CA2104119A1 - Spiral implant for organ pathways - Google Patents
Spiral implant for organ pathwaysInfo
- Publication number
- CA2104119A1 CA2104119A1 CA002104119A CA2104119A CA2104119A1 CA 2104119 A1 CA2104119 A1 CA 2104119A1 CA 002104119 A CA002104119 A CA 002104119A CA 2104119 A CA2104119 A CA 2104119A CA 2104119 A1 CA2104119 A1 CA 2104119A1
- Authority
- CA
- Canada
- Prior art keywords
- implant
- primary
- spiral
- guide wire
- wire
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Abandoned
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/12—Surgical instruments, devices or methods, e.g. tourniquets for ligaturing or otherwise compressing tubular parts of the body, e.g. blood vessels, umbilical cord
- A61B17/12022—Occluding by internal devices, e.g. balloons or releasable wires
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/12—Surgical instruments, devices or methods, e.g. tourniquets for ligaturing or otherwise compressing tubular parts of the body, e.g. blood vessels, umbilical cord
- A61B17/12022—Occluding by internal devices, e.g. balloons or releasable wires
- A61B17/12099—Occluding by internal devices, e.g. balloons or releasable wires characterised by the location of the occluder
- A61B17/12109—Occluding by internal devices, e.g. balloons or releasable wires characterised by the location of the occluder in a blood vessel
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/12—Surgical instruments, devices or methods, e.g. tourniquets for ligaturing or otherwise compressing tubular parts of the body, e.g. blood vessels, umbilical cord
- A61B17/12022—Occluding by internal devices, e.g. balloons or releasable wires
- A61B17/12131—Occluding by internal devices, e.g. balloons or releasable wires characterised by the type of occluding device
- A61B17/1214—Coils or wires
- A61B17/12145—Coils or wires having a pre-set deployed three-dimensional shape
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/12—Surgical instruments, devices or methods, e.g. tourniquets for ligaturing or otherwise compressing tubular parts of the body, e.g. blood vessels, umbilical cord
- A61B17/12022—Occluding by internal devices, e.g. balloons or releasable wires
- A61B17/12131—Occluding by internal devices, e.g. balloons or releasable wires characterised by the type of occluding device
- A61B17/12168—Occluding by internal devices, e.g. balloons or releasable wires characterised by the type of occluding device having a mesh structure
- A61B17/12172—Occluding by internal devices, e.g. balloons or releasable wires characterised by the type of occluding device having a mesh structure having a pre-set deployed three-dimensional shape
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/0004—Closure means for urethra or rectum, i.e. anti-incontinence devices or support slings against pelvic prolapse
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2250/00—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2250/0014—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis
- A61F2250/0039—Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis differing in diameter
Abstract
Abstract Spiral implant for organ pathways, in particular for blood vessels, which is formed from a primary spiral made of metal or a primary tube made of an elastic synthetic material whose anterior end is closed and whose cross-section at a distance of 0.5 to 2 mm from the other end of the primary spiral or primary tube is modified for a distance of 0.01 to 10 mm in order to make it possible to reposition the implant. The force required to displace the primary shape on the guide wire serving as an inser-tion aid amounts to 0.5 N to 10 N. The invention des-cribes an implant (1) which can be used in vascular surgery or vascular radiology in order to achieve selec-tive blood vessel occlusion. Insertion of the implant (1) into a blood vessel is brought about by means of an insertion catheter (16), with the implant being held in a rectilinear shape by a guide wire (14) slid therein.
After the implant has reached the correct position in the organ pathway (18) it assumes a pre-formed spiral shape on the withdrawal of the insertion wire from inside it, thereby ensuring fixation of the implant in the organ pathway.
After the implant has reached the correct position in the organ pathway (18) it assumes a pre-formed spiral shape on the withdrawal of the insertion wire from inside it, thereby ensuring fixation of the implant in the organ pathway.
Description
NO 92J14408 - 1 ~ PC~/EP~/00294 Spiral implant for organ pathway~
The invention relate~ to implant~ for organ pathway~, preferably for blood ve~sel~, whose secondary shape i~ fo~med either from a primary wire ~piral made of metal or a prLmary tube made of synthetic material by twistin~ or winding, the secondary shapP bei~g extended for in~roduction and being reformad in as~ociation with placemen~ in the organ;
In interventional radiology, metal spLrals fbr vessel occlusion have, for more than 10 year~, been Lmplanted ~lsing catheters. Spirals of this type are described repeatedly i~ tha literature. In Radiology 136;230-231 ~July 1980), N. Ca~taneda-Z~niga et al.
describ~ an L~proved form of the so-called Gianturco spiral~r which can be introduced u~ing cath~ter~ mad~ of polyurethane or polyethylene. The primary spiral is formed by appropria~e techniques in~o a ball or ~ secon-dary spiral. In order to be able to implant the spiral in its secondary shapa, the latter i3 extended by drawing up the primary spiral onto a guide wire. When Lmplanting by means of a catheter on the guide wire, a further dis-placeable spiral is arranged on the guide wire, which spiral serves to push ~he implant, i.e. the prLmary spiral, out of the catheter and to push it off from the guide wire, so that the ~econdary shape is re~rmed and the secondary spiral or the ball re~ain~ in the vessel which is to be oc~luded.
In Am. J. Roentgenol. 129: 795-798 ~November 1977) J. Andersonf S. Walace and C. Gianturco describe the advantages of being able ~o replace the ~piral before finally ca~ting it o~f. Howaver, their helical cork~crew connection has the di~ad~antage that there is the danger of the vessel being per~orated by the sharp e~d of the spiral. In a~dition, the spiral can be di~placed by ro~ation while disconnecting. This is also suggeqted by the numerous complications in the animal experiments.
In Radiology 138; 37-46 (Ja~a~y 1981), M.J.
M~zer and coworkers describe the disad~antages of the ' ' ' r ~ 7 i~ 4 ~ ~ ~
rela~i~ely high degree~ of deformat~on, in~o a helical spring body, such that the spring body, on the application of an external force, can be el~s~ically reformed into a straight wira ~piral and, on partial ce~sat~on of thi~ ~orca, assume~ a knot-~haped con~iguration.
It is the ob~ect of the pre~ent in~ention to improve the constructional configura~ion of the i~plant~
and of the insertion wire in such a way that the pos-sibility exi~ts, be~ore finally detaching the implant5fr~m the auxiliary mean~ employed for the in er~ion, of, ~E:P~I~T SH13 - 7 ~ ; ` `: - : :
.
- : ., : ` . . : :: :
known technique and refer to failur~ arising from incorrect choice o~ the si2e of the secondary ~piral and to the ri~ks o~ using unsuitable stripping devices.
A device for occluding arterie~ is described in ~D-A-223 065, which de~ice comprises a cardiac or angio-graphic cathe~er, with a prepared point, a pu~hing element (pusher), an occluding body and a core wire, on the front end of which wire the occluding body i~ slid on and is detachably secursd. The core wire run~ movably in th~ intarior of the pu~hing ~lement and can ba i~ro duced, together with the slid-on oc~luding body and the pushing element, beyond the opening of the cathetsr further into the ar~ery in such a way that ths occluding body remains on the core wire and i~ also con~eyed by 15 ~hi~ wire outside of the catheter. By keeping a firm hold on the core wire and by further pushing of the pushing element, the occluding bo~y can be stripped off the core wire. This can take place by retracting the core wire into the pushing elQment. ~he occluding body i provided with a textile fibre material over its whole length and over i~ whole periphery. It possesses a sleeve-shaped part at its po~terior end into which the core wire can be introduced in such a way tha~ the occluding body can be detached eficiently from th~ core wire usin~ the pushing element.
An occluding body suitable for the intra-arterial and intravenou~ occlu~ion of blood ves~els, is kno~n from DD-A-158 084, in which occluding ~ody a wire spiral is formed, with the use of relatively high degrees of defor-mation, into a helical spring body, such that the spring bod~, on the application of an external force, can be eLastically re~ormed into a straight wire spiral and, on partial cessation of this force, assumes a knot-~haped configuration.
It is the ob~ect of the present invention to Lmprove the constructional configuration of the Lmplants in such a way tha~ the possibili~y exists~ be~ore finally detaching the implant~ from the auxiliary mean~ empioyed ' ~
`
;
.
The invention relate~ to implant~ for organ pathway~, preferably for blood ve~sel~, whose secondary shape i~ fo~med either from a primary wire ~piral made of metal or a prLmary tube made of synthetic material by twistin~ or winding, the secondary shapP bei~g extended for in~roduction and being reformad in as~ociation with placemen~ in the organ;
In interventional radiology, metal spLrals fbr vessel occlusion have, for more than 10 year~, been Lmplanted ~lsing catheters. Spirals of this type are described repeatedly i~ tha literature. In Radiology 136;230-231 ~July 1980), N. Ca~taneda-Z~niga et al.
describ~ an L~proved form of the so-called Gianturco spiral~r which can be introduced u~ing cath~ter~ mad~ of polyurethane or polyethylene. The primary spiral is formed by appropria~e techniques in~o a ball or ~ secon-dary spiral. In order to be able to implant the spiral in its secondary shapa, the latter i3 extended by drawing up the primary spiral onto a guide wire. When Lmplanting by means of a catheter on the guide wire, a further dis-placeable spiral is arranged on the guide wire, which spiral serves to push ~he implant, i.e. the prLmary spiral, out of the catheter and to push it off from the guide wire, so that the ~econdary shape is re~rmed and the secondary spiral or the ball re~ain~ in the vessel which is to be oc~luded.
In Am. J. Roentgenol. 129: 795-798 ~November 1977) J. Andersonf S. Walace and C. Gianturco describe the advantages of being able ~o replace the ~piral before finally ca~ting it o~f. Howaver, their helical cork~crew connection has the di~ad~antage that there is the danger of the vessel being per~orated by the sharp e~d of the spiral. In a~dition, the spiral can be di~placed by ro~ation while disconnecting. This is also suggeqted by the numerous complications in the animal experiments.
In Radiology 138; 37-46 (Ja~a~y 1981), M.J.
M~zer and coworkers describe the disad~antages of the ' ' ' r ~ 7 i~ 4 ~ ~ ~
rela~i~ely high degree~ of deformat~on, in~o a helical spring body, such that the spring body, on the application of an external force, can be el~s~ically reformed into a straight wira ~piral and, on partial ce~sat~on of thi~ ~orca, assume~ a knot-~haped con~iguration.
It is the ob~ect of the pre~ent in~ention to improve the constructional configura~ion of the i~plant~
and of the insertion wire in such a way that the pos-sibility exi~ts, be~ore finally detaching the implant5fr~m the auxiliary mean~ employed for the in er~ion, of, ~E:P~I~T SH13 - 7 ~ ; ` `: - : :
.
- : ., : ` . . : :: :
known technique and refer to failur~ arising from incorrect choice o~ the si2e of the secondary ~piral and to the ri~ks o~ using unsuitable stripping devices.
A device for occluding arterie~ is described in ~D-A-223 065, which de~ice comprises a cardiac or angio-graphic cathe~er, with a prepared point, a pu~hing element (pusher), an occluding body and a core wire, on the front end of which wire the occluding body i~ slid on and is detachably secursd. The core wire run~ movably in th~ intarior of the pu~hing ~lement and can ba i~ro duced, together with the slid-on oc~luding body and the pushing element, beyond the opening of the cathetsr further into the ar~ery in such a way that ths occluding body remains on the core wire and i~ also con~eyed by 15 ~hi~ wire outside of the catheter. By keeping a firm hold on the core wire and by further pushing of the pushing element, the occluding bo~y can be stripped off the core wire. This can take place by retracting the core wire into the pushing elQment. ~he occluding body i provided with a textile fibre material over its whole length and over i~ whole periphery. It possesses a sleeve-shaped part at its po~terior end into which the core wire can be introduced in such a way tha~ the occluding body can be detached eficiently from th~ core wire usin~ the pushing element.
An occluding body suitable for the intra-arterial and intravenou~ occlu~ion of blood ves~els, is kno~n from DD-A-158 084, in which occluding ~ody a wire spiral is formed, with the use of relatively high degrees of defor-mation, into a helical spring body, such that the spring bod~, on the application of an external force, can be eLastically re~ormed into a straight wire spiral and, on partial cessation of this force, assumes a knot-~haped configuration.
It is the ob~ect of the present invention to Lmprove the constructional configuration of the Lmplants in such a way tha~ the possibili~y exists~ be~ore finally detaching the implant~ from the auxiliary mean~ empioyed ' ~
`
;
.
2 ~ 9 - where appropriate, recovering these implan~s once again or elss altering their po~ition in the organ pathwa~.
This object is achieved by an imp}ant for org~n.
pathway~ which i~ formed from a primary spiral made o~
metal or a primary tube made of elaatic ~ynth~tic material, in which the anterior end o~ the pri~ary ~piral or of the primary tube i5 closed and the pos~erior region is ~orm~d a3 a clamping ~ea~ for a guide wire, and ~h~
L~plant pos~e~se~ a secondary shape of increa~ed external.
diametQr, which shape can be ex~ended by sliding- th~
primary spiral or primary tube on~o the guide wire hnd reform~ on pulling out the guide wire or o~ pushing off from the guide wire by rastitutory forces present in.the material, characterize~ i~ that, at a distance of 0.5.mm to 2 mm from the posterior end o the primary ~piral or of tha primary tube, it~ cro~s-~ectio~ is modified for a distance of 0~01 mm to 10 mm by diminution o the inter-nal diame~er in at leas~ one radial direction. ::
In addition, the in~ention includes a device for inserting these implant-~ into an organ pathway, having an insertion catheter, a stripping element and a guide wire for the Lmplant, where the force required to displace ~he primary spiral or the primary tube and to overcome the clamping force with the guide wire ~er~ing as an in~er-tion aid is 0~5 N to 10 N, preferably 1.5 N to 3 N.
REPL~E~E~T S~E~T
...,, . ' ' , . , ~. . ., : ., ~ , ..
~ 7 `~ 9 wo 92/14408 - 3 - ~ PCT~P92/00294 for tha in~ertion, of, where appropriate, recovering these implants once again or else al~ering their po~ition in the organ pathway.
Thi~ object is achieved by an implant for organ pathways which is formed from a primary spiral made o~
metal or a prLmary tube made of ela~tic synthetic material, in which the anterior end of the prL~ary ~piral or of the primAry tube i~ clo~ed and the po~terior region i~ formed as a clamping seat for a guide wire, ch~rac-terized in tha~, at a dis~ance of 0.5 mm ~o 2 mm from theposterior end of the primary spiral or of the primary tube, its cross-section is modified for a distance o~
O.01 mm to 10 mm by diminution of the internal diameter in at lea3t one radlal direction, 50 ~ha~ the force required to displace the primary spiral or the primary tube a~d to overcome the clamping force with the guide wire ~er~ing a~ an insertion aid i~ 005 N to 10 N, the implant has a secondary shape of increased external diameter, which ~hape can ~e extended by ~he primary spiral or the primary tube being slid onto the guide wire and reforms on pulling o~t th~ guids wire or on pu~hing of~ from the guide wire as a result of restitutory orces presen~ in the material. Force3 between 1.5 N and 3N are preferred.
The primary 3pirals having diameters of 0.2 mm to 3 mm, preferably 0.4 mm to 1.5 mm, are wound from metal wire having diam0ters of 0.Q6 mm to 0.6 mm, preferably O.1 mm to 0.4 mm, and the secondary shape is formed subseguent}y. ~owever, the shape can al~o be for~ed at the same time as the primary spiral i5 being wound.
Suitable materials for the implants having a primary spiral made of metal are surgical steel wire with spring propertieq, corrosivQ or non-corro~ive ~pring steel wire and steel wire made of non-precious metals, which is coated with corrosion-resistant metals such as tantalum, titanium, platinum or gold, or ceramic material3. The wire can have a round, oval or rectangular cro~s ~ection.
. - . . . ~ ~ , . ..
.
-.. . ~ ~. . . .
~O 9~/14408 ~ 4 ~ ~ PCTfEP92/00294 ~ he pr~ary tube3 for implantc~ are prepared from medically compatible elastic thennopLa3tic polymers, such as polyurethane homopolymers or copolym~r~, polyolefin copolymer~ or silicone elastomer~. Re~orbable polymer~, S such a~ aliphatic polye~ter~, e.g. polydio~anone, ars also suitable, and the secondary spiral shape is formed subsequently. The wall thickness of the prLmary tube~ can ba 0.08 mm to 0.8 mm, and the diameter of the primary tubes 0.3 mm to 3 ~m. The constriction of the cros~-section for achieving a clamping seat, in the ca~e ofprLmary ~ubes, can also take place by parallel elongated slo~s being cut in o~er the circumference of the t~be, and longi~udinal strip~ of the polymer material being per}llanently deformed inward~ b~ being pre~-4ed in. The ad~antage of this configuration of the cro~s-sectional con~triction for producing a clamping seat on the guid~
wire is that the 1OAg1tUdina11Y extending ~ection~ which ha~e been formed exhibit an enlarged contact surface on the guide wire.
~h0 length o~ the primary shape_, i.e. o~ the primary ~pirals or primiary tube3, can be 10 to 500 mm, pre~erably 10 mm to 200 mm.
It is a characteristic of th~ implants according to the invention that the ~econdary qpiral shape can be rever~ibly extended by sliding the prima~y spiral or the primary tube onto a guide wire, who3e internal diameter i~ omewhat smaller than ~he internal dia~ter of th~
prLmary spiral or ~he prima~y tub~ in the non-modified part~, and that the s~condary ~hape is reformed on pulling out the guide wire or on pushing off from the guide wire a~ a result o~ restitutory force~ present in the material. An elastic spring behaviour of this nature, and the restitutory forces re~ulting from it, are ba~ed on ~he properties of the selected materials. The spring action can, for example, be achiaved by heating the material, which has been con~igured in~o the desired shape, and 3ubsequently cooling (quenching) it rapidly.
The spxing action of thermoplastic polymer~ frequently . . .- . . .
- . ..
. . ~ . .. ...
. . . ..
-21~4119 ~0 92J14408 - 5 PC~/EP92/0029 depends on the formation o~ par~icular cry~talline structures, or on the freazing in of ~tre~es in the material during shaping. The mea~ures for e~tabli~hi~g the modulus of ela~ticity of the material nace~sary for th~ r~versible extension, and the selection of the materials which are suitable for this, are known to the perqon skilled in the art and do not pre~ent him with any difficulties.
By means of the part formed with a modified cross-section in the vicinity of th2 rear end of the primary shape of the implants, a clamping seat is achieved of the pr~mary shape, tha~ i~ approximately the extended ~econdary shape on the guide wire, in as~oci-ation with which, however, ~he clamping force is not so great that displacement of the primary shape on the guide wire and complete withdrawal of the guide wire, or ~tripping from the guide wire by means of a stripping elemen~ no longer possible.
The placement of the implant is effected using a de~ice having an inser~ion catheter, a stripping element and a guide wire for the Lmplan~, the guide wire being provided with a conical point and posse~sing, immediately after the point, either an an~ular groove or a circum-farential beading, i~ order to achieve a particularly high cl2mping effQCt between the pocterior region of the implant, with reduced internal diameter, and the anterior regio~ of the guide wire.
Fsr insertion into an organ path~ay, the guide wire, with the stripping element slid onto it and the primary shape of the extended implant ~lid on in fron~ of the element, ic placed inside a oathQter. ~ith a solid cross section, the diame~er of the guide wire3 can be 0,07 to 0.7 mm. The ability to reposition the implant is given by the sta~ic friction of the part wi~h the modi-fied, preferably reduced, cro~q-section on the guide wire being 2 to 5 times, pre~erably 2 to 3 times, greater than the force which is necessary in ordex to stretch once again the secondary shape, which to a large ex~ent has : "
,, : . :
- - . . , ~,: . . . :
2 ~
WO 92J1440E~ - 6 - PCT~E:P92~00:~94 been complet~ly formed in the organ pathway as the re3ult of partial ~tripping from the guide wira, by retracti~g it into the insertion cathe~er. The s~lected uppor limit of the clamping force en~ures that, in the event of unwanted catching ~f the implant in the wall of the organ pathway, damage to the lat~er by too great a withdrawal force i~ avoided. ~he clamping seat of the primary shape of the implant on the` guide wire is achieved ~y the cros~-section of at least one to several turnæ of the primary spiral being modified by constriction of th~
di~mater of the prLmary spixal, or by formation o~ an oval cross-section whose smaller diameter is ~maller than the ex~ernal diameter of the guide wire. The desired dif-ferenca between withdrawal force into the insertion catheter a~d the force for overcoming the clamping seat of the primary shape on the guida wire can, with the given modified cro~s-section of the prima~y ~hape, alRo be brought about by using a guide wire with a friction-increasing ~urface con~iguration, for example a roughened surface, in the anterior region, with a circumferential beading, or by mean~ of an annular groove in the guide wire in which the modified, preferably constricted, cross-section at least partially engages.
The device described above pe~mits reliable placement of ~he Lmplant according to the in~ent~on in an organ pathway, going through ~he following step~:
a) advancement of the catheter, in who~e inner lumen the implant is located in extended condition on the insertion wire, in~ide tha organ pathway into the vicinity of the site where the implant is to be located, b) di~placement of the insertion wire, with the implant located on it in extended hape, to the intended sit~ for the location, c) formation of the secondary shape of the implant by withdrawing the guide wire or by pushing forward the stripping elemen~, ~ . ,: . .
':' ;' ' '~'.. ': ' ' ' ' ,: : ..
: .
2 l a ~
~o 92~14~08 _ 7 _ ~ Pc~/~Pg2/Oe294 d) further withdrawaL of tha catheter and of the guide wire, or pu~hing ~orward of the ~tripping el~ment, until only the anterior point of the guide wirs i3 heLd in the clamping seat in the po~erior region of the primary spiral or the primary tube, e) correction of the position of the Lmplant, or, i~
neca~3ary, withdrawal o~ the implant into the catheter, f) stripping-off o~ the implant from the guide wire a~
~he sita intcnded for it in the organ pathway u~ing the stripping element.
Th~ ~econdary shape~ of the lmplant~ according to the invention can exhibit varying ~OrmB, in each ca~e accordLng ~o the ~pecial i~tended ef~ect i~ the organ pathway.
As a prosthe~i~ for an organ pathway, a cylindrical form is preerred i~ wh~ch the external diameter of the cylinder must be at lea~t a~ large as the inte~nal diam~er of the organ pathway to be supported, in order to guarantee Yecure plac~ment. In order to re~uce the ri~k o~ throm~osi~, it is preferred, in this mode of applicatio~, to heparinise the ~urface o~ the implant. In ~he case of implants made of polymer~, the chemical bondi~g of heparin to t ~ polym~r presents no problem3y and is known to the per~on skilled in the art.
I~ the ca~e of Lmplants mad2 of m~tal, th~ b~nding of the hsparin can necessitate the application of a thin adhe4ive layer of a medically compatible polymer which i~
capa~le of chemical bonding. Sinc~ the suitable polymers, such as, for example, polyvinyl alcohol, silicones, or copolymer~ with heparin binding groups based on poly-urethane~ or polyolefins, possess film-forming properties, the polymsrs can be applied either from a disper~io~, emulsion or solu~ion in organio olvents, and the film can be formed by evaporatin~ of~ the liquid medium.
In order to configure the open in~er cross-section of prostheses o~ this type to be a~ large a~
: -. ~ . , . . :. ,. . - . : -, ~ , , ,. . , - , . . ~ . , , 2~0~9 ~O 92/14408 - a Pc~Pq2/002s4 pos~ible, the primary spiral or the prLmary tube of the --Lmplant can ha~e an oval cros~-~ection, and the cylindrical secondary shape can be ~o formed that the surface~ with the larger radius of curvature of th~
primary shape~ are arranged alongside each other in the secondary shape, and form the outer surfaee of the secondary shape.
~ owever~ a contrary effect of the implant3 i~
frequently de~ired; organ pathway~ are to be constricted or occluded by the implant. In order to achieve this with a cylindrical secondary ~hape, either the diamater can be formed to be correspondingly small, or ~ cylindrical ~piral can be wound in which turn~ of ~arying diameter alterna~P so that ~he internal diameter o~ the ~econdary shape is variably formed in the lengthwi3e axi~ of the spiral, with individual turn~ or several turn of the minimum possible radiu~ of curvature. A con~triction of an organ pathwa~ can also be achieved ~y means of a cone or a double cone with the larger diameter at the ends o~
the secondary shape. In thi~ way, flow~ in ves~el~ (via cathetery) can be throttled. In this context, the minLmum in~ernal diameter ~hould not be less than 4 mm, if the vessel must remain open. (One possible application i9 pul~onary banding in children with left-right shu~t).
For an o~clu3ion, a shape which i~ here desig-na~ed a helix is par~i~ularly suitable. In thi~ case, th~
primary shap2 i~ wound helically, with the primary shape being bent of~ in the cen~re at right angle~ to the halix and, at a distance from the fir3t helix, a ~econd helix being formed parallel to it, which second helix can, where neces~ary, also have a ~maller or larger diameter.
The primary shape between the two helical elements can al~o be wound a~ a ~piral, in order to provide the ~econdary shape with greater stability in the direction of the lengthwi~e axis. When being u~e~ for occlusion in as30ciation with a cardiac septum defect, this secondary ~hape can yield ela~tically ~o the alteration~ in wall thickness at each heartbea~.
' `~ -. . ,. . . : ., ; .. :
~O 92~14408 - 9 - PCT/~P92/00294 In order to increase ~he rigidity of the external turn~ of the helix or of the double-cone sha~e, the WirQ
used ~o prepare the primary spiral or primary shape can al~o, ins~ead of a relatively large round cro3s-section, have an oval o~ rectangular cro~ ection.
Since, particularly in perinatal u~e, the extar-nal diameter of the in~ertion catheter should be a~ small a~ pos~ibler and consequently the spiral diameter of the secondary 3hape mu~t necessarily al~o remain 3mall, thi~
can lead, in the ca~e of larger organ pathways to b0 occluded, to problems of s~a~ility in as~ociation wi~h arrangement and locs~ion, with the danger of incompleta occlusion or o~ di~location. In such a case, it i~
particularly preferred to locate double cones a~ implant~
in the organ pathway in a tand~m arrange~en~. For carry ing out the location, ~wo ~condary shape , in each ca~e ~ormed as a double cone, are arranged behind one another in extended form on the guid~ wire. Th~ first double cone with a per~anent inner lumen i~ implanted, and ~ubse-quently the second im~lant, in extended form, i~ pu~hedso far forward that the a~terior end pro~ects beyond the first double cone to be L~planted, and par~ially unroll~.
By furthar withdrawal of the guide wire, while the stripping element is sta~ionary, a cen~ral part of the doublQ cone i~ deposited i~ the inside of the first double cone in more or 10~s axtended ~orm~ and the end of ~h~ ~eoond double cone out~ide the firs~ double con~
unroll~. The elastic ~orce of the second implant, which i5 ~ill extended in tha inner lumen o~ the first double cone, pulls the fir3t implant as tightly together as pos3ible and anlarge~ ths external diameter of the ends of the dou~le cone, and incxea~es tho contact pres~ure on the organ wall. At tha same time, the inner lumen i~
additionally closed. The minLmum external diameter i~
association with catheter occlusion i~ only 1.3 to 2.3 mm (4 F to 7 F) in thi~ technique, ~o that this implantation technique can also be employed with neonate or premature babies. ~f the smalle~t im~lant is ~upplied in a normal ~,,. . . ~ .
'-: ' ' . . , '' . ' :~' . : : ', .. : ' - ' 21~119 WO 92/14408 - 10 - Pc~JEp92/oo294 cannula, the ~mallest external diametex then amount~ to only 1 mm, and thu3 permit~ use in a relati~ely ri~k-free manner even at the prenatal tage, e.g. for aneuris~al occlusion .
Since a thrombotic e~fect i~ de3ired in associa-~ion wi~h ~he occlusion of an organ pathway, the surface o the~e Lmplant~ i9 not heparinised but, on th~ con-trary, is given a coa~ulation-promoti~g configuration.
This can take plac~ by coating ~he ~urface with metal 0 particl8s I Rilicones~ polytetrafluoroethylene~, m~dically compatible rubber la~ice~, or wi~h medically compatibla polymers which promota b~ood coagulation. ?
For plugging cavities and ve~sels, a secondary shape of the Lmplan~ i~ i~ partieular suitable which 15 pos3e~es several loops lyi~g behind each other in tha form of horiæo~tal figures of eight.
The in~ention is described below in still more detail with reference to the illus~ration.
Figuro 1 3hows diagrammatically a cylindrical secondary shap~ of the implant which, with a ~mall spiral diameter, can be used to occlude a narrow organ pathwa~
or, with a larger diameter, can be used a3 a prosthe3is for keeping an organ pathway open.
Figure 2 show~ diagrammatically in longitudinal sec~ion a par~ of the po3terior end of the prLmary shape of the implant spiral from Figure 1.
Figure 3 show~ diagrammatically a cylindrical secondary shape o~ the Lmplant spiral whose primary ~hape differ~ from the primary ~hape in Figure 1 in it~ cro-qs-30 sectional shape. ;~
Figure 4 show~ diagrammatically a cylindrical ~ :
secondary shape of the implant with spiral ~wists of varying diameter.
Figure 5 shows diagrammatically a conical shape : -of the implant.
Figure 6 .~0W8 diagrammatically an implant in the form of a d~uble cone. ~.
. ~
2 ~ 9 In Fig~re 2, the pos~erior end of the primasy shape of th~ implant from Figure 1 is reprodsced in enlarged form. Th~ i~terna} diameter of the p~imary spiral 2, which i~ wound out o~ me~al wire ha~ing spring properties, i9 constricted at a short distance from the pos~erior end 5 by mean~ of turns 6 which have a smalIer diameter. If the primary spiral 2 is sli~ on~o an inser-tion wire whose external dlame~er is ~omewhat larger than the modlied internal d~axe~er 7 of tha primary ~piral 2, the clamping seat of the extend~d secondary shape on th~ ins~rtion wire, which seat i~ d~ired for the re-positionability, is formed.
The cylindrical spiral 1 reprecented in Figure 3 i~ ~ormed from ~ primary shape 2 whose cross-section 3 is R~PhaCE~ENT 5HEET
: . . . .,. : . . .. . - .
~a 92~1440~ PcT/~ps2/oa2s4 Figures 7, 7a and 7b show the L~plant shape of the so-calle~ double helix and double ro~ette from th~
side and from behind.
Figure 8 show~ diagrammatically a preferred embodiment of the anterior end of an insertion wire ~sr implanting the spiral~ accbrding to the in~ention.
Figure ~ shows the anterior end of an in~ertion catheter in longitudinal ~ectio~.
Figure 10 show3 in cro~ ection the end of a~
1~ insertivn cathe~er which wa~ repres~nted in Figure 9.
Figure 11 show~ diagrzmmatically, in ~equence a to e, the individual ~teps invoLved in locating a~
implant according to the invention in an organ pathway.
The Lmplant ~hown in Figura 1 ha~ the ~econdary shape 1 of a cylindrical helix or ~piral, the helix 1 it~elf being composed of a wire ~piral 2 (primary shape) made of spring metal. The modification of the cross-~ection 3 of the primary ~piral 2 at the po~terior end i~
not ~how~ in ~hi~ figure. The anterior end 4 o the primary ~piral 2 i~ clo~ed in order ~o ensure that~ on extending the ~econdary ~hape on the in~ertion wire, the primary spiral 2 cannot be drawn 40 far up the insertion wire that the latter pro~sct~ bayond the end of the primary spiral 2.
In Figure 2, the po~t~rior end of tha primary shape oi ~he i~plant from Pigure 1 is reproduced in enla~ged iorm. The internal diameter of the primary ~piral 2, which is wound out of me~al wire having spring propertie~ constrictad at a short dis~ance from the po~terior end 5 by means of turn~ 6 which have a smaller diameter. If the pri~ary spiral 2 ~9 slid on~o an inser-tion wire whose external diameter i~ somewhat larger than the modi ied internal diameter ~ of the primary spiral 2, ~he clamping seat o~ th~ extended secondary shape on the insertion catheter, which seat is desired for the re-positionability, is formed.
The cylindrical spiral 1 represen~ed in ~igure 3 is formed from a primary sh~pe 2 whose cross-~ection 3 i5 . ,., ~ . ..... . . . . .
. " - .
'~ : - ' ', . , , :
`: : ' : ` .
:: " `
oval. The anterior end 4 o the p~imary spiral 2 i~
closed. $his shape is particularly ~uitable a~ a pro~-thosis for organ pa~hways because, a~ compared with the shap~ shown in Figure 1, a ~omewhat larger free internal volum~ of the prosthesi3 remains.
Figure 4 ~hows a cyiindrical shape of the secon-dary ~hape 1, which was formed from a primary spiral 2.
The anterior end 4 of the primary spiral 2 is closed. In order ~o form the i~plant to be particularly ~uitable for occluding organ pathway~, the secondary shape 1 posse~e~
turns ~, 10, o different diametPr, which alternate with each other. Tha turns o the implant ha~ing the larger diameter 9 serve to support the ~mplant again~t the wall of ~he organ pathway and the t~rns 10 ha~ing the small~r ~5 diameter redu~e the free in~ernal vol~me of the Lmplant and ~hereby promote occlu~ion through thrombo~is.
Figure S shows the configuration of a conical secondaxy shape 1 from a primary ~piral 2. In order to simplify the positioningr and retraction into the inser-tion catheter, of a REPha~EME~T S~æ~T ~ :
. :
;
', ,:
~' :- ':,.
2 1 0 ~
WO 92~14408 - 12 - PC~EP92/00294 oval. The anterior and 4 o the primary spiral 2 i~ -.
clo~ed. Thi~ ~hape i~ particularly ~ui~able as a pro~-the~i~ for organ pathways becau~e, a~ comp æ ed with the shape shown in Figure 1, a somewhat la~g~r free inte~nal 5 volume of the pro~the~is remains. :~
Figure 4 shows a cylindrical shape of the secon-dary shape 1, which wa~ formed from a primary spiral 2.
The anterior end 4 of ~he primary spiral 2 i~ closed. I~
order to form the Lmplant to be particularly ~uitable for occluding organ p~thway~, the secondaxy shape 1 po~e~e5 turns 9, 10, of different diameter, which alternate with each other. The turns of the Lmplant ha~ing the larger diameter 9 serve ~o ~upport ~he implant agai~st the wall of ths organ pathway and the turns 10 having the ~maller diameter reduce the ~ree internal ~olume of the implant and th~reby promote occlusion through thrombosis.
Figure 5 shows the configuration of a conical secondary shape 1 from a primary spiral 2. In order to simplify the positioning, and retraction in~o the in~er-20 tion catheter, of a spiral which ha~ been partiaLly paLd .;
out but which ha~ still not been completely stripped from the guide wire, the cross-sectional modification, in ~he conical con~iguration, i~ preferably arranged at a distance from ~he end of the secondary spiral 1 which has the smaller dia~eter. However, the modification of the oro~s-section can al~o be arranged at the end of the spiral having the larger diæmeter.
Figure 6 i3 a particularly preferred embodiment of the helical Lmplant according to the invention in the form of a double cone, the turn~ of the secondary shape 1 being arranged with a smaller diameter in the cen~ral region, and the ands possessing a larger turn diameter.
In the figure, the external ~iameter o~ the secondary shape 1 is identical at both ends. In principle, however, it is al~o possible to form the double cone in such a way that the secondary shape has a different diameter at each of the two ends.
:
, .
; ;
"
:
. ~ :, ' , . :
2 ~
W~ 92tl440B - 13 - PCT/EP9~/002~4 Figure 7 shows the shape of the impla~ according to the inven~ion which is de~igna~ed here as a double helix. The secondary shape 1 i8 compo~ed of two parallel elemen~s 11 and 13 which are spaced apart fr~m each o~her, wound helically and connected to each other by means of a cylindrically wound intermediat~ piece 12, which runs in ths direc~ion of the lengthwis~ axi~ of the double piece~, the elements 11 and 13 extending at right angles to the lengthwise axis. In principle, howe~er, it is also possible for the double helix to be form~d in such a way that it has different diameter~ at each of the two ends.
Figure 7a show~ one of the helically rolled-up elements 11 with a diagrE~matically indicated primary lS shape whose diameter i modiied, i.e. formed to b~
cons~ricted, in the ~ection 7 a~ a ~hort distance from the posterior end 5.
It is evident from Figure 7b that the helically rolled-up elements 11 can also be configured as a rosette in order to form a double rosette instead of a double helix.
Naturally, all the secondary shapes which are preferred according to the in~ention and which are formed from spirals (primary ~hape) can al50 be formed from elastic tube3 made of synthetic material.
In order to suppor~ the clamping ~eat of the implan~s according to the inYention on the insertion wire in a particular position shortly before the final releasa, a guide wire can be used whose anterior end i~
rapresented diagrammatically in Figu~e 8. In order to ~implify the sliding-on of the primary shape o~ the lmplant onto the insertion wire 14, the anterior end of the latter is preferably rounded off conically, and an annular groova lS i formed at a di~tance from the anterior point, into which groove the section wi~h the modified cro~s-sc~tion of the primary shape of the implant according to the inven~ion engage3, so that the clamping seat is particul~rly pronounced at thi~ point, ..
:: : : . :
. . .
" : .
:. : : ... .. . .
~la~lls ~.
~o 92/1~08 - 14 - PC~/~P92~00294 and the maxLmum force for overcoming the clamping seat while stripping off the implan~ from ~he guid~ wire i~
determined by the force for releasing the engagem~nt o~
the modified turns of the primary spiral or o~ the S modified cross-section of a primary t~be with tha annular groove 15.
Figure 9 shows, in longitudinal section, tha anterior end of a cathet~r 16 which i~ ~uitable for inserting the implant~ according to the in~ntion into organ pathways, into the tip of which catheter preferably a liner 17 made of metal or of a h~rd, par~icularly low-friction, pol~mer material is firmly in~erted. In order to ~implify tha retraction, for the purpose of repositioning, of secondary spirals which have already been partially formed into th~ catheter, the front end of the lines directed toward the exterior is rounded o~f inward~. This strengthening liner extend3 that part of the implant which has already been pushed off the quide wire to such an extent that, after pulling into the catheter, it can be removed once again from the organ pathway together with the catheter in order to make po~sible a repositioning during a new insertion cycle.
This can prove to be necessary in particular when it emerges, in association wi~h the partial formation of the secondary shape in the organ pa~hway, that an un~uitable implant shap~ has bee~ selacted, or el~e that th~
formation o~ the secondary shape has not taken place in the correct position in the organ pathway.
Figure 10 show~ the preferably strengthened catheter tip i~ cros~-~ection.
Figure lOa shows a round cathe~er 16 with an inserted cylindrical liner 17.
In Figure lOb, an oval catheter 16 is represen~ed with a rectangular liner 17, and in Figure lOc an oval catheter 16 with a rec~angular liner 17 into which an implant 1 has been retracted.
This xectan~ular shape of a liner 17 is par-ticularly pre~erred when the primary shape of the implan~
. ' ' . ::
2 ~
wo 32~14408 _ 15 - PC~/EP92/00294 1 po~se3~e~ an oval rather than a round cro~ ection.
Figurs 11 shows diagrammatically the po~itio~ing of the implant 1 in an organ pathway 18, for example a blood vessel. A catheter 16 is pu~hed i~Yide the organ pathway 1~ into the ~icinity of the site at which the Lmplant 1 is to be positioned. The implant 1 is located, in an extendad condition in the so-called primary shape, in the inner lumen of the catheter and on the insertion wire 14. Starting rom the di~tal end of the ca~heter, which end is locatQd out~ide the bod~, the guide wire 14, with the implant 1 loca~ed on it in extended form, i~
pushed forward into the organ pathway 18 to the site for positioning. In ~tep ~, the secondary shape of the implant i~ formed, from tha prLmary shape of the Lmplant 1 and as a re~ult of the spring ac~ion, in the organ pathway 18 by withdrawing the guide wire 14 or by pu~hing forward the stripping element 19. In step C, tha secondary ~hape of the ~mplant 1 i~ developed further by withdrawing the insertion catheter 16 and by further withdrawal o~ the guide wixe 14, or by pu~hing forward the stripping element 19, and in step D the position is reached in which the guide wire 14 i8 contained in ~he la~t section of the prima~y shape of the implant 1 and the clamping sea~, due to the modified cross-section 7 of the prLmary ~hape of the Lmpla~ 1, is still present o~
the guide wire 1~. In the emhodiment o~ the guide wire represented in s~ep D, the wire pos esses an annular grcove 15 in which the wall o~ the modified cross-section of the primary shape, for exa~ple one or more spirals of a wire 6 ha~ing a smaller cro~s-section, o~ at least a cross-sectian which is reduced in one direction, engages.
In thi~ position there is, a~ter checking for the correct positioning of the implant 1 in the organ pathway 18, a final chance to withdraw the unrolled ~econdary shap~ of the Lmplant 1 into the catheter 16 by pulling bac~ the guide wire. The fact that the force req~ired to overcome the clamping seat amounts to several time3 that required to reextend ~he ~ormed secondary shape of the Lmplan~ 1 ,,,, .. . ' . ~
. . ~ .
.
2 1 ~
W0 9~/144~8 - 16 - PCT/EP92toO2g4 and draw it back into the ca~heter 16 en~ure~ that it i5 --possible to repo3ition the Lmplants according to the invention in the case of an incorrect arrangement or an unsuitable choice of shape. A stripping element lg is arranged on the guide wire 14 in an axial direction behind the prLmary shape of the Lmplant 1, the posterior end of which element reache~ to the distal end of the catheter. ~he stripping element can be a tube or el~e, for reasons of elasticity, a spiral, who3e e~ternal diameter coinrides wi~h the external diam~ter of the primary shape of the Lmplant at its postPrior end. By pushing forward the stripping element 19 in tha catheter 16 or.pulling back the guide wire 14 while keeping th~
~tripping elemen~ 19 stationary/ the clamping ~at o~ the implan~ 1 on the guide wire 14 is released, and the end of the guide wire is pulled out of the shape, or the prLmary shape is stripped off from the end of the guide wire. The Lmplant 1 then assumes the predetermined shape in the organ pathway 18. Catheter 16 and st~ipping element 19 are withdrawn from the organ pathway.
In the case of a tandem arrang~ment of implants, two primary shapes, preferably implant~ having the double-cone shape, are extended in a tandem arrangement on a guide wire. The first implant i~ initially 2S positioned in the organ pathway, and then the second Lmplant is unroll~d and positioned in the inner lumen of this impla~t. In the case of double-coned implants, it i8 possible to arrange them so that at least a part of the central section of the second implant remains in extended form and thu~ exerts a traction effect on the ends of the double-coned first implant.
The particular advantage of the configuration of spiral Lmplants according to the invention i~ that the implant can still be manipulated even in the implanted state a3 long as it has still not been completely uncoupled from the guide wire. The repositionability which this pr~ides represents the crucial i~provement as co~pared with con~entional technoloyy. Following . , .
:, ' . ' ~:
. . . .
.
2 ~ 9 NO 92Jl4~08 - 17 - PCT~P92~00294 thrombo~ the region o the implant, a lasting occlusion of ~he organ pathway, for example o~ blood vessels, is provided. If resorbable implant material~
having a spring action are u~ed, no undesirable ~ide-effects are ~o be expected, even over a long period oftime. The exact positioning can be monitored radio-logically or by means of ultrasonic , : . .. . . .
- . . . , , ~ . , : . ~
This object is achieved by an imp}ant for org~n.
pathway~ which i~ formed from a primary spiral made o~
metal or a primary tube made of elaatic ~ynth~tic material, in which the anterior end o~ the pri~ary ~piral or of the primary tube i5 closed and the pos~erior region is ~orm~d a3 a clamping ~ea~ for a guide wire, and ~h~
L~plant pos~e~se~ a secondary shape of increa~ed external.
diametQr, which shape can be ex~ended by sliding- th~
primary spiral or primary tube on~o the guide wire hnd reform~ on pulling out the guide wire or o~ pushing off from the guide wire by rastitutory forces present in.the material, characterize~ i~ that, at a distance of 0.5.mm to 2 mm from the posterior end o the primary ~piral or of tha primary tube, it~ cro~s-~ectio~ is modified for a distance of 0~01 mm to 10 mm by diminution o the inter-nal diame~er in at leas~ one radial direction. ::
In addition, the in~ention includes a device for inserting these implant-~ into an organ pathway, having an insertion catheter, a stripping element and a guide wire for the Lmplant, where the force required to displace ~he primary spiral or the primary tube and to overcome the clamping force with the guide wire ~er~ing as an in~er-tion aid is 0~5 N to 10 N, preferably 1.5 N to 3 N.
REPL~E~E~T S~E~T
...,, . ' ' , . , ~. . ., : ., ~ , ..
~ 7 `~ 9 wo 92/14408 - 3 - ~ PCT~P92/00294 for tha in~ertion, of, where appropriate, recovering these implants once again or else al~ering their po~ition in the organ pathway.
Thi~ object is achieved by an implant for organ pathways which is formed from a primary spiral made o~
metal or a prLmary tube made of ela~tic synthetic material, in which the anterior end of the prL~ary ~piral or of the primAry tube i~ clo~ed and the po~terior region i~ formed as a clamping seat for a guide wire, ch~rac-terized in tha~, at a dis~ance of 0.5 mm ~o 2 mm from theposterior end of the primary spiral or of the primary tube, its cross-section is modified for a distance o~
O.01 mm to 10 mm by diminution of the internal diameter in at lea3t one radlal direction, 50 ~ha~ the force required to displace the primary spiral or the primary tube a~d to overcome the clamping force with the guide wire ~er~ing a~ an insertion aid i~ 005 N to 10 N, the implant has a secondary shape of increased external diameter, which ~hape can ~e extended by ~he primary spiral or the primary tube being slid onto the guide wire and reforms on pulling o~t th~ guids wire or on pu~hing of~ from the guide wire as a result of restitutory orces presen~ in the material. Force3 between 1.5 N and 3N are preferred.
The primary 3pirals having diameters of 0.2 mm to 3 mm, preferably 0.4 mm to 1.5 mm, are wound from metal wire having diam0ters of 0.Q6 mm to 0.6 mm, preferably O.1 mm to 0.4 mm, and the secondary shape is formed subseguent}y. ~owever, the shape can al~o be for~ed at the same time as the primary spiral i5 being wound.
Suitable materials for the implants having a primary spiral made of metal are surgical steel wire with spring propertieq, corrosivQ or non-corro~ive ~pring steel wire and steel wire made of non-precious metals, which is coated with corrosion-resistant metals such as tantalum, titanium, platinum or gold, or ceramic material3. The wire can have a round, oval or rectangular cro~s ~ection.
. - . . . ~ ~ , . ..
.
-.. . ~ ~. . . .
~O 9~/14408 ~ 4 ~ ~ PCTfEP92/00294 ~ he pr~ary tube3 for implantc~ are prepared from medically compatible elastic thennopLa3tic polymers, such as polyurethane homopolymers or copolym~r~, polyolefin copolymer~ or silicone elastomer~. Re~orbable polymer~, S such a~ aliphatic polye~ter~, e.g. polydio~anone, ars also suitable, and the secondary spiral shape is formed subsequently. The wall thickness of the prLmary tube~ can ba 0.08 mm to 0.8 mm, and the diameter of the primary tubes 0.3 mm to 3 ~m. The constriction of the cros~-section for achieving a clamping seat, in the ca~e ofprLmary ~ubes, can also take place by parallel elongated slo~s being cut in o~er the circumference of the t~be, and longi~udinal strip~ of the polymer material being per}llanently deformed inward~ b~ being pre~-4ed in. The ad~antage of this configuration of the cro~s-sectional con~triction for producing a clamping seat on the guid~
wire is that the 1OAg1tUdina11Y extending ~ection~ which ha~e been formed exhibit an enlarged contact surface on the guide wire.
~h0 length o~ the primary shape_, i.e. o~ the primary ~pirals or primiary tube3, can be 10 to 500 mm, pre~erably 10 mm to 200 mm.
It is a characteristic of th~ implants according to the invention that the ~econdary qpiral shape can be rever~ibly extended by sliding the prima~y spiral or the primary tube onto a guide wire, who3e internal diameter i~ omewhat smaller than ~he internal dia~ter of th~
prLmary spiral or ~he prima~y tub~ in the non-modified part~, and that the s~condary ~hape is reformed on pulling out the guide wire or on pushing off from the guide wire a~ a result o~ restitutory force~ present in the material. An elastic spring behaviour of this nature, and the restitutory forces re~ulting from it, are ba~ed on ~he properties of the selected materials. The spring action can, for example, be achiaved by heating the material, which has been con~igured in~o the desired shape, and 3ubsequently cooling (quenching) it rapidly.
The spxing action of thermoplastic polymer~ frequently . . .- . . .
- . ..
. . ~ . .. ...
. . . ..
-21~4119 ~0 92J14408 - 5 PC~/EP92/0029 depends on the formation o~ par~icular cry~talline structures, or on the freazing in of ~tre~es in the material during shaping. The mea~ures for e~tabli~hi~g the modulus of ela~ticity of the material nace~sary for th~ r~versible extension, and the selection of the materials which are suitable for this, are known to the perqon skilled in the art and do not pre~ent him with any difficulties.
By means of the part formed with a modified cross-section in the vicinity of th2 rear end of the primary shape of the implants, a clamping seat is achieved of the pr~mary shape, tha~ i~ approximately the extended ~econdary shape on the guide wire, in as~oci-ation with which, however, ~he clamping force is not so great that displacement of the primary shape on the guide wire and complete withdrawal of the guide wire, or ~tripping from the guide wire by means of a stripping elemen~ no longer possible.
The placement of the implant is effected using a de~ice having an inser~ion catheter, a stripping element and a guide wire for the Lmplan~, the guide wire being provided with a conical point and posse~sing, immediately after the point, either an an~ular groove or a circum-farential beading, i~ order to achieve a particularly high cl2mping effQCt between the pocterior region of the implant, with reduced internal diameter, and the anterior regio~ of the guide wire.
Fsr insertion into an organ path~ay, the guide wire, with the stripping element slid onto it and the primary shape of the extended implant ~lid on in fron~ of the element, ic placed inside a oathQter. ~ith a solid cross section, the diame~er of the guide wire3 can be 0,07 to 0.7 mm. The ability to reposition the implant is given by the sta~ic friction of the part wi~h the modi-fied, preferably reduced, cro~q-section on the guide wire being 2 to 5 times, pre~erably 2 to 3 times, greater than the force which is necessary in ordex to stretch once again the secondary shape, which to a large ex~ent has : "
,, : . :
- - . . , ~,: . . . :
2 ~
WO 92J1440E~ - 6 - PCT~E:P92~00:~94 been complet~ly formed in the organ pathway as the re3ult of partial ~tripping from the guide wira, by retracti~g it into the insertion cathe~er. The s~lected uppor limit of the clamping force en~ures that, in the event of unwanted catching ~f the implant in the wall of the organ pathway, damage to the lat~er by too great a withdrawal force i~ avoided. ~he clamping seat of the primary shape of the implant on the` guide wire is achieved ~y the cros~-section of at least one to several turnæ of the primary spiral being modified by constriction of th~
di~mater of the prLmary spixal, or by formation o~ an oval cross-section whose smaller diameter is ~maller than the ex~ernal diameter of the guide wire. The desired dif-ferenca between withdrawal force into the insertion catheter a~d the force for overcoming the clamping seat of the primary shape on the guida wire can, with the given modified cro~s-section of the prima~y ~hape, alRo be brought about by using a guide wire with a friction-increasing ~urface con~iguration, for example a roughened surface, in the anterior region, with a circumferential beading, or by mean~ of an annular groove in the guide wire in which the modified, preferably constricted, cross-section at least partially engages.
The device described above pe~mits reliable placement of ~he Lmplant according to the in~ent~on in an organ pathway, going through ~he following step~:
a) advancement of the catheter, in who~e inner lumen the implant is located in extended condition on the insertion wire, in~ide tha organ pathway into the vicinity of the site where the implant is to be located, b) di~placement of the insertion wire, with the implant located on it in extended hape, to the intended sit~ for the location, c) formation of the secondary shape of the implant by withdrawing the guide wire or by pushing forward the stripping elemen~, ~ . ,: . .
':' ;' ' '~'.. ': ' ' ' ' ,: : ..
: .
2 l a ~
~o 92~14~08 _ 7 _ ~ Pc~/~Pg2/Oe294 d) further withdrawaL of tha catheter and of the guide wire, or pu~hing ~orward of the ~tripping el~ment, until only the anterior point of the guide wirs i3 heLd in the clamping seat in the po~erior region of the primary spiral or the primary tube, e) correction of the position of the Lmplant, or, i~
neca~3ary, withdrawal o~ the implant into the catheter, f) stripping-off o~ the implant from the guide wire a~
~he sita intcnded for it in the organ pathway u~ing the stripping element.
Th~ ~econdary shape~ of the lmplant~ according to the invention can exhibit varying ~OrmB, in each ca~e accordLng ~o the ~pecial i~tended ef~ect i~ the organ pathway.
As a prosthe~i~ for an organ pathway, a cylindrical form is preerred i~ wh~ch the external diameter of the cylinder must be at lea~t a~ large as the inte~nal diam~er of the organ pathway to be supported, in order to guarantee Yecure plac~ment. In order to re~uce the ri~k o~ throm~osi~, it is preferred, in this mode of applicatio~, to heparinise the ~urface o~ the implant. In ~he case of implants made of polymer~, the chemical bondi~g of heparin to t ~ polym~r presents no problem3y and is known to the per~on skilled in the art.
I~ the ca~e of Lmplants mad2 of m~tal, th~ b~nding of the hsparin can necessitate the application of a thin adhe4ive layer of a medically compatible polymer which i~
capa~le of chemical bonding. Sinc~ the suitable polymers, such as, for example, polyvinyl alcohol, silicones, or copolymer~ with heparin binding groups based on poly-urethane~ or polyolefins, possess film-forming properties, the polymsrs can be applied either from a disper~io~, emulsion or solu~ion in organio olvents, and the film can be formed by evaporatin~ of~ the liquid medium.
In order to configure the open in~er cross-section of prostheses o~ this type to be a~ large a~
: -. ~ . , . . :. ,. . - . : -, ~ , , ,. . , - , . . ~ . , , 2~0~9 ~O 92/14408 - a Pc~Pq2/002s4 pos~ible, the primary spiral or the prLmary tube of the --Lmplant can ha~e an oval cros~-~ection, and the cylindrical secondary shape can be ~o formed that the surface~ with the larger radius of curvature of th~
primary shape~ are arranged alongside each other in the secondary shape, and form the outer surfaee of the secondary shape.
~ owever~ a contrary effect of the implant3 i~
frequently de~ired; organ pathway~ are to be constricted or occluded by the implant. In order to achieve this with a cylindrical secondary ~hape, either the diamater can be formed to be correspondingly small, or ~ cylindrical ~piral can be wound in which turn~ of ~arying diameter alterna~P so that ~he internal diameter o~ the ~econdary shape is variably formed in the lengthwi3e axi~ of the spiral, with individual turn~ or several turn of the minimum possible radiu~ of curvature. A con~triction of an organ pathwa~ can also be achieved ~y means of a cone or a double cone with the larger diameter at the ends o~
the secondary shape. In thi~ way, flow~ in ves~el~ (via cathetery) can be throttled. In this context, the minLmum in~ernal diameter ~hould not be less than 4 mm, if the vessel must remain open. (One possible application i9 pul~onary banding in children with left-right shu~t).
For an o~clu3ion, a shape which i~ here desig-na~ed a helix is par~i~ularly suitable. In thi~ case, th~
primary shap2 i~ wound helically, with the primary shape being bent of~ in the cen~re at right angle~ to the halix and, at a distance from the fir3t helix, a ~econd helix being formed parallel to it, which second helix can, where neces~ary, also have a ~maller or larger diameter.
The primary shape between the two helical elements can al~o be wound a~ a ~piral, in order to provide the ~econdary shape with greater stability in the direction of the lengthwi~e axis. When being u~e~ for occlusion in as30ciation with a cardiac septum defect, this secondary ~hape can yield ela~tically ~o the alteration~ in wall thickness at each heartbea~.
' `~ -. . ,. . . : ., ; .. :
~O 92~14408 - 9 - PCT/~P92/00294 In order to increase ~he rigidity of the external turn~ of the helix or of the double-cone sha~e, the WirQ
used ~o prepare the primary spiral or primary shape can al~o, ins~ead of a relatively large round cro3s-section, have an oval o~ rectangular cro~ ection.
Since, particularly in perinatal u~e, the extar-nal diameter of the in~ertion catheter should be a~ small a~ pos~ibler and consequently the spiral diameter of the secondary 3hape mu~t necessarily al~o remain 3mall, thi~
can lead, in the ca~e of larger organ pathways to b0 occluded, to problems of s~a~ility in as~ociation wi~h arrangement and locs~ion, with the danger of incompleta occlusion or o~ di~location. In such a case, it i~
particularly preferred to locate double cones a~ implant~
in the organ pathway in a tand~m arrange~en~. For carry ing out the location, ~wo ~condary shape , in each ca~e ~ormed as a double cone, are arranged behind one another in extended form on the guid~ wire. Th~ first double cone with a per~anent inner lumen i~ implanted, and ~ubse-quently the second im~lant, in extended form, i~ pu~hedso far forward that the a~terior end pro~ects beyond the first double cone to be L~planted, and par~ially unroll~.
By furthar withdrawal of the guide wire, while the stripping element is sta~ionary, a cen~ral part of the doublQ cone i~ deposited i~ the inside of the first double cone in more or 10~s axtended ~orm~ and the end of ~h~ ~eoond double cone out~ide the firs~ double con~
unroll~. The elastic ~orce of the second implant, which i5 ~ill extended in tha inner lumen o~ the first double cone, pulls the fir3t implant as tightly together as pos3ible and anlarge~ ths external diameter of the ends of the dou~le cone, and incxea~es tho contact pres~ure on the organ wall. At tha same time, the inner lumen i~
additionally closed. The minLmum external diameter i~
association with catheter occlusion i~ only 1.3 to 2.3 mm (4 F to 7 F) in thi~ technique, ~o that this implantation technique can also be employed with neonate or premature babies. ~f the smalle~t im~lant is ~upplied in a normal ~,,. . . ~ .
'-: ' ' . . , '' . ' :~' . : : ', .. : ' - ' 21~119 WO 92/14408 - 10 - Pc~JEp92/oo294 cannula, the ~mallest external diametex then amount~ to only 1 mm, and thu3 permit~ use in a relati~ely ri~k-free manner even at the prenatal tage, e.g. for aneuris~al occlusion .
Since a thrombotic e~fect i~ de3ired in associa-~ion wi~h ~he occlusion of an organ pathway, the surface o the~e Lmplant~ i9 not heparinised but, on th~ con-trary, is given a coa~ulation-promoti~g configuration.
This can take plac~ by coating ~he ~urface with metal 0 particl8s I Rilicones~ polytetrafluoroethylene~, m~dically compatible rubber la~ice~, or wi~h medically compatibla polymers which promota b~ood coagulation. ?
For plugging cavities and ve~sels, a secondary shape of the Lmplan~ i~ i~ partieular suitable which 15 pos3e~es several loops lyi~g behind each other in tha form of horiæo~tal figures of eight.
The in~ention is described below in still more detail with reference to the illus~ration.
Figuro 1 3hows diagrammatically a cylindrical secondary shap~ of the implant which, with a ~mall spiral diameter, can be used to occlude a narrow organ pathwa~
or, with a larger diameter, can be used a3 a prosthe3is for keeping an organ pathway open.
Figure 2 show~ diagrammatically in longitudinal sec~ion a par~ of the po3terior end of the prLmary shape of the implant spiral from Figure 1.
Figure 3 show~ diagrammatically a cylindrical secondary shape o~ the Lmplant spiral whose primary ~hape differ~ from the primary ~hape in Figure 1 in it~ cro-qs-30 sectional shape. ;~
Figure 4 show~ diagrammatically a cylindrical ~ :
secondary shape of the implant with spiral ~wists of varying diameter.
Figure 5 shows diagrammatically a conical shape : -of the implant.
Figure 6 .~0W8 diagrammatically an implant in the form of a d~uble cone. ~.
. ~
2 ~ 9 In Fig~re 2, the pos~erior end of the primasy shape of th~ implant from Figure 1 is reprodsced in enlarged form. Th~ i~terna} diameter of the p~imary spiral 2, which i~ wound out o~ me~al wire ha~ing spring properties, i9 constricted at a short distance from the pos~erior end 5 by mean~ of turns 6 which have a smalIer diameter. If the primary spiral 2 is sli~ on~o an inser-tion wire whose external dlame~er is ~omewhat larger than the modlied internal d~axe~er 7 of tha primary ~piral 2, the clamping seat of the extend~d secondary shape on th~ ins~rtion wire, which seat i~ d~ired for the re-positionability, is formed.
The cylindrical spiral 1 reprecented in Figure 3 i~ ~ormed from ~ primary shape 2 whose cross-section 3 is R~PhaCE~ENT 5HEET
: . . . .,. : . . .. . - .
~a 92~1440~ PcT/~ps2/oa2s4 Figures 7, 7a and 7b show the L~plant shape of the so-calle~ double helix and double ro~ette from th~
side and from behind.
Figure 8 show~ diagrammatically a preferred embodiment of the anterior end of an insertion wire ~sr implanting the spiral~ accbrding to the in~ention.
Figure ~ shows the anterior end of an in~ertion catheter in longitudinal ~ectio~.
Figure 10 show3 in cro~ ection the end of a~
1~ insertivn cathe~er which wa~ repres~nted in Figure 9.
Figure 11 show~ diagrzmmatically, in ~equence a to e, the individual ~teps invoLved in locating a~
implant according to the invention in an organ pathway.
The Lmplant ~hown in Figura 1 ha~ the ~econdary shape 1 of a cylindrical helix or ~piral, the helix 1 it~elf being composed of a wire ~piral 2 (primary shape) made of spring metal. The modification of the cross-~ection 3 of the primary ~piral 2 at the po~terior end i~
not ~how~ in ~hi~ figure. The anterior end 4 o the primary ~piral 2 i~ clo~ed in order ~o ensure that~ on extending the ~econdary ~hape on the in~ertion wire, the primary spiral 2 cannot be drawn 40 far up the insertion wire that the latter pro~sct~ bayond the end of the primary spiral 2.
In Figure 2, the po~t~rior end of tha primary shape oi ~he i~plant from Pigure 1 is reproduced in enla~ged iorm. The internal diameter of the primary ~piral 2, which is wound out of me~al wire having spring propertie~ constrictad at a short dis~ance from the po~terior end 5 by means of turn~ 6 which have a smaller diameter. If the pri~ary spiral 2 ~9 slid on~o an inser-tion wire whose external diameter i~ somewhat larger than the modi ied internal diameter ~ of the primary spiral 2, ~he clamping seat o~ th~ extended secondary shape on the insertion catheter, which seat is desired for the re-positionability, is formed.
The cylindrical spiral 1 represen~ed in ~igure 3 is formed from a primary sh~pe 2 whose cross-~ection 3 i5 . ,., ~ . ..... . . . . .
. " - .
'~ : - ' ', . , , :
`: : ' : ` .
:: " `
oval. The anterior end 4 o the p~imary spiral 2 i~
closed. $his shape is particularly ~uitable a~ a pro~-thosis for organ pa~hways because, a~ compared with the shap~ shown in Figure 1, a ~omewhat larger free internal volum~ of the prosthesi3 remains.
Figure 4 ~hows a cyiindrical shape of the secon-dary ~hape 1, which was formed from a primary spiral 2.
The anterior end 4 of the primary spiral 2 is closed. In order ~o form the i~plant to be particularly ~uitable for occluding organ pathway~, the secondary shape 1 posse~e~
turns ~, 10, o different diametPr, which alternate with each other. Tha turns o the implant ha~ing the larger diameter 9 serve to support the ~mplant again~t the wall of ~he organ pathway and the t~rns 10 ha~ing the small~r ~5 diameter redu~e the free in~ernal vol~me of the Lmplant and ~hereby promote occlu~ion through thrombo~is.
Figure S shows the configuration of a conical secondaxy shape 1 from a primary ~piral 2. In order to simplify the positioningr and retraction into the inser-tion catheter, of a REPha~EME~T S~æ~T ~ :
. :
;
', ,:
~' :- ':,.
2 1 0 ~
WO 92~14408 - 12 - PC~EP92/00294 oval. The anterior and 4 o the primary spiral 2 i~ -.
clo~ed. Thi~ ~hape i~ particularly ~ui~able as a pro~-the~i~ for organ pathways becau~e, a~ comp æ ed with the shape shown in Figure 1, a somewhat la~g~r free inte~nal 5 volume of the pro~the~is remains. :~
Figure 4 shows a cylindrical shape of the secon-dary shape 1, which wa~ formed from a primary spiral 2.
The anterior end 4 of ~he primary spiral 2 i~ closed. I~
order to form the Lmplant to be particularly ~uitable for occluding organ p~thway~, the secondaxy shape 1 po~e~e5 turns 9, 10, of different diameter, which alternate with each other. The turns of the Lmplant ha~ing the larger diameter 9 serve ~o ~upport ~he implant agai~st the wall of ths organ pathway and the turns 10 having the ~maller diameter reduce the ~ree internal ~olume of the implant and th~reby promote occlusion through thrombosis.
Figure 5 shows the configuration of a conical secondary shape 1 from a primary spiral 2. In order to simplify the positioning, and retraction in~o the in~er-20 tion catheter, of a spiral which ha~ been partiaLly paLd .;
out but which ha~ still not been completely stripped from the guide wire, the cross-sectional modification, in ~he conical con~iguration, i~ preferably arranged at a distance from ~he end of the secondary spiral 1 which has the smaller dia~eter. However, the modification of the oro~s-section can al~o be arranged at the end of the spiral having the larger diæmeter.
Figure 6 i3 a particularly preferred embodiment of the helical Lmplant according to the invention in the form of a double cone, the turn~ of the secondary shape 1 being arranged with a smaller diameter in the cen~ral region, and the ands possessing a larger turn diameter.
In the figure, the external ~iameter o~ the secondary shape 1 is identical at both ends. In principle, however, it is al~o possible to form the double cone in such a way that the secondary shape has a different diameter at each of the two ends.
:
, .
; ;
"
:
. ~ :, ' , . :
2 ~
W~ 92tl440B - 13 - PCT/EP9~/002~4 Figure 7 shows the shape of the impla~ according to the inven~ion which is de~igna~ed here as a double helix. The secondary shape 1 i8 compo~ed of two parallel elemen~s 11 and 13 which are spaced apart fr~m each o~her, wound helically and connected to each other by means of a cylindrically wound intermediat~ piece 12, which runs in ths direc~ion of the lengthwis~ axi~ of the double piece~, the elements 11 and 13 extending at right angles to the lengthwise axis. In principle, howe~er, it is also possible for the double helix to be form~d in such a way that it has different diameter~ at each of the two ends.
Figure 7a show~ one of the helically rolled-up elements 11 with a diagrE~matically indicated primary lS shape whose diameter i modiied, i.e. formed to b~
cons~ricted, in the ~ection 7 a~ a ~hort distance from the posterior end 5.
It is evident from Figure 7b that the helically rolled-up elements 11 can also be configured as a rosette in order to form a double rosette instead of a double helix.
Naturally, all the secondary shapes which are preferred according to the in~ention and which are formed from spirals (primary ~hape) can al50 be formed from elastic tube3 made of synthetic material.
In order to suppor~ the clamping ~eat of the implan~s according to the inYention on the insertion wire in a particular position shortly before the final releasa, a guide wire can be used whose anterior end i~
rapresented diagrammatically in Figu~e 8. In order to ~implify the sliding-on of the primary shape o~ the lmplant onto the insertion wire 14, the anterior end of the latter is preferably rounded off conically, and an annular groova lS i formed at a di~tance from the anterior point, into which groove the section wi~h the modified cro~s-sc~tion of the primary shape of the implant according to the inven~ion engage3, so that the clamping seat is particul~rly pronounced at thi~ point, ..
:: : : . :
. . .
" : .
:. : : ... .. . .
~la~lls ~.
~o 92/1~08 - 14 - PC~/~P92~00294 and the maxLmum force for overcoming the clamping seat while stripping off the implan~ from ~he guid~ wire i~
determined by the force for releasing the engagem~nt o~
the modified turns of the primary spiral or o~ the S modified cross-section of a primary t~be with tha annular groove 15.
Figure 9 shows, in longitudinal section, tha anterior end of a cathet~r 16 which i~ ~uitable for inserting the implant~ according to the in~ntion into organ pathways, into the tip of which catheter preferably a liner 17 made of metal or of a h~rd, par~icularly low-friction, pol~mer material is firmly in~erted. In order to ~implify tha retraction, for the purpose of repositioning, of secondary spirals which have already been partially formed into th~ catheter, the front end of the lines directed toward the exterior is rounded o~f inward~. This strengthening liner extend3 that part of the implant which has already been pushed off the quide wire to such an extent that, after pulling into the catheter, it can be removed once again from the organ pathway together with the catheter in order to make po~sible a repositioning during a new insertion cycle.
This can prove to be necessary in particular when it emerges, in association wi~h the partial formation of the secondary shape in the organ pa~hway, that an un~uitable implant shap~ has bee~ selacted, or el~e that th~
formation o~ the secondary shape has not taken place in the correct position in the organ pathway.
Figure 10 show~ the preferably strengthened catheter tip i~ cros~-~ection.
Figure lOa shows a round cathe~er 16 with an inserted cylindrical liner 17.
In Figure lOb, an oval catheter 16 is represen~ed with a rectangular liner 17, and in Figure lOc an oval catheter 16 with a rec~angular liner 17 into which an implant 1 has been retracted.
This xectan~ular shape of a liner 17 is par-ticularly pre~erred when the primary shape of the implan~
. ' ' . ::
2 ~
wo 32~14408 _ 15 - PC~/EP92/00294 1 po~se3~e~ an oval rather than a round cro~ ection.
Figurs 11 shows diagrammatically the po~itio~ing of the implant 1 in an organ pathway 18, for example a blood vessel. A catheter 16 is pu~hed i~Yide the organ pathway 1~ into the ~icinity of the site at which the Lmplant 1 is to be positioned. The implant 1 is located, in an extendad condition in the so-called primary shape, in the inner lumen of the catheter and on the insertion wire 14. Starting rom the di~tal end of the ca~heter, which end is locatQd out~ide the bod~, the guide wire 14, with the implant 1 loca~ed on it in extended form, i~
pushed forward into the organ pathway 18 to the site for positioning. In ~tep ~, the secondary shape of the implant i~ formed, from tha prLmary shape of the Lmplant 1 and as a re~ult of the spring ac~ion, in the organ pathway 18 by withdrawing the guide wire 14 or by pu~hing forward the stripping element 19. In step C, tha secondary ~hape of the ~mplant 1 i~ developed further by withdrawing the insertion catheter 16 and by further withdrawal o~ the guide wixe 14, or by pu~hing forward the stripping element 19, and in step D the position is reached in which the guide wire 14 i8 contained in ~he la~t section of the prima~y shape of the implant 1 and the clamping sea~, due to the modified cross-section 7 of the prLmary ~hape of the Lmpla~ 1, is still present o~
the guide wire 1~. In the emhodiment o~ the guide wire represented in s~ep D, the wire pos esses an annular grcove 15 in which the wall o~ the modified cross-section of the primary shape, for exa~ple one or more spirals of a wire 6 ha~ing a smaller cro~s-section, o~ at least a cross-sectian which is reduced in one direction, engages.
In thi~ position there is, a~ter checking for the correct positioning of the implant 1 in the organ pathway 18, a final chance to withdraw the unrolled ~econdary shap~ of the Lmplant 1 into the catheter 16 by pulling bac~ the guide wire. The fact that the force req~ired to overcome the clamping seat amounts to several time3 that required to reextend ~he ~ormed secondary shape of the Lmplan~ 1 ,,,, .. . ' . ~
. . ~ .
.
2 1 ~
W0 9~/144~8 - 16 - PCT/EP92toO2g4 and draw it back into the ca~heter 16 en~ure~ that it i5 --possible to repo3ition the Lmplants according to the invention in the case of an incorrect arrangement or an unsuitable choice of shape. A stripping element lg is arranged on the guide wire 14 in an axial direction behind the prLmary shape of the Lmplant 1, the posterior end of which element reache~ to the distal end of the catheter. ~he stripping element can be a tube or el~e, for reasons of elasticity, a spiral, who3e e~ternal diameter coinrides wi~h the external diam~ter of the primary shape of the Lmplant at its postPrior end. By pushing forward the stripping element 19 in tha catheter 16 or.pulling back the guide wire 14 while keeping th~
~tripping elemen~ 19 stationary/ the clamping ~at o~ the implan~ 1 on the guide wire 14 is released, and the end of the guide wire is pulled out of the shape, or the prLmary shape is stripped off from the end of the guide wire. The Lmplant 1 then assumes the predetermined shape in the organ pathway 18. Catheter 16 and st~ipping element 19 are withdrawn from the organ pathway.
In the case of a tandem arrang~ment of implants, two primary shapes, preferably implant~ having the double-cone shape, are extended in a tandem arrangement on a guide wire. The first implant i~ initially 2S positioned in the organ pathway, and then the second Lmplant is unroll~d and positioned in the inner lumen of this impla~t. In the case of double-coned implants, it i8 possible to arrange them so that at least a part of the central section of the second implant remains in extended form and thu~ exerts a traction effect on the ends of the double-coned first implant.
The particular advantage of the configuration of spiral Lmplants according to the invention i~ that the implant can still be manipulated even in the implanted state a3 long as it has still not been completely uncoupled from the guide wire. The repositionability which this pr~ides represents the crucial i~provement as co~pared with con~entional technoloyy. Following . , .
:, ' . ' ~:
. . . .
.
2 ~ 9 NO 92Jl4~08 - 17 - PCT~P92~00294 thrombo~ the region o the implant, a lasting occlusion of ~he organ pathway, for example o~ blood vessels, is provided. If resorbable implant material~
having a spring action are u~ed, no undesirable ~ide-effects are ~o be expected, even over a long period oftime. The exact positioning can be monitored radio-logically or by means of ultrasonic , : . .. . . .
- . . . , , ~ . , : . ~
Claims (12)
1. Implant for organ pathways, which is formed from a primary spiral (2) made of metal or a primary tube (2) made of elastic synthetic material, where the anterior end (4) of the primary spiral (2) or of the primary tube (2) is closed and the posterior region is formed as a clamping seat for a guide wire, and the implant has a secondary shape (1) of increased external diameter, which shape can be extended by sliding the primary spiral (2) or the primary tube (2) onto the guide wire (14) and reforms on pulling out the guide wire (14) or on pushing off from the guide wire (14) as a result of restitutory forces present in the material, characterized in that, at a distance of 0.5 mm to 2 mm from the posterior end of the primary spiral (2) or of the primary tube (2) its cross-section (7) is modified for a distance of 0.01 mm to 10 mm by constriction of the internal diameter in at least one radial direction.
2. Implant according to claim 1, characterized in that the wire diameter of the primary spiral (2) is 0.06 to 0.6 mm and the diameter of the primary spiral (2) is from 0.2 to 3 mm.
3. Implant according to claim 1, characterized in that the wall thickness of the primary tube (2) made of synthetic material is from 0.08 mm to 0.8 mm and the diameter is from 0.3 to 3mm.
4. Implant according to claim 1 or 2, characterized in that the cross-section of at least one to several turns (6) of the primary spiral (2) is modified by constricting the diameter of the primary spiral (2) or by forming an oval cross-section having a reduced diameter of the primary spiral (2) as compared with the oval diameter.
5. Implant according to claim 1 or 2, characterized in that the cross-section of the primary tube (2) is modified by constricting the diameter, or by forming an oval cross-section having a reduced diameter in one direction as compared with the normal diameter.
6. Implant according to claim 1, characterized in that the primary spiral (2) or the primary tube (2) is 10 to 500 mm long.
7. Implant according to claim 1, characterized in that the secondary shape (1), by twisting a primary spiral (2) or primary tube (2), has the form of a cylinder, a cone, a double cone with larger diameters at the ends, a cylinder in which turns (9, 10) of the secondary shape (1) having different diameters alternate, a double helix (11, 13) which is connected by a cylin-drical section (12), a double rosette, or the form of several horizontal figures of eight.
8. Implant according to claim 1, characterized in that the primary spiral (2) is wound from a wire having a round, oval or rectangular cross-section.
9. Implant according to claim 7, characterized in that the inner turns of the double cone or of the double helix or of the double rosette are composed of a primary spiral (2) having a round wire cross-section, and the outer turns are composed of a primary spiral (2) having an enlarged round, oval or rectangular wire cross-section.
10. Device for inserting an implant according to one of claims 1 to 9 into an organ pathway, having an insertion catheter (16), a stripping element (19) and a guide wire (14) for the implant, characterized in that the force required to displace the primary spiral (2) or the primary tube (2) and to overcome the clamping force with the guide wire (14) serving as an insertion aid is 0.5 N to 10 N.
11. Device according to claim 13, characterized in that the guide wire (14) is provided, at the anterior end or in the vicinity of this end, either with an annular groove (15) or with a circumferential beading.
12. Process for positioning the implant according to one of claims 1 to 9 in an organ pathway (18) by means of the steps:
a) advancement of the catheter (16), in whose inner lumen the implant is located in extended condition on the insertion wire (14), inside the organ pathway (18) into the vicinity of the site where the implant is to be located, b) displacement of the insertion wire (14), with the implant located on it in extended shape, to the intended site for the location, c) formation of the secondary shape (1) of the implant by withdrawing the guide wire (14) or by pushing forward the stripping element (19), d) further withdrawal of the catheter (16) and of the guide wire (14), or pushing forward of the stripping element (19), until only the anterior point of the guide wire (14) is held in clamping seating in the posterior region of the primary spiral (2) or the primary tube (2), e) correction of the position of the implant, or, if necessary, withdrawal of the implant into the catheter, f) stripping-off of the implant from the guide wire (14) at the site intended for it in the organ pathway (18) using the stripping element (19).
a) advancement of the catheter (16), in whose inner lumen the implant is located in extended condition on the insertion wire (14), inside the organ pathway (18) into the vicinity of the site where the implant is to be located, b) displacement of the insertion wire (14), with the implant located on it in extended shape, to the intended site for the location, c) formation of the secondary shape (1) of the implant by withdrawing the guide wire (14) or by pushing forward the stripping element (19), d) further withdrawal of the catheter (16) and of the guide wire (14), or pushing forward of the stripping element (19), until only the anterior point of the guide wire (14) is held in clamping seating in the posterior region of the primary spiral (2) or the primary tube (2), e) correction of the position of the implant, or, if necessary, withdrawal of the implant into the catheter, f) stripping-off of the implant from the guide wire (14) at the site intended for it in the organ pathway (18) using the stripping element (19).
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| DE4104702A DE4104702C2 (en) | 1991-02-15 | 1991-02-15 | Implants for organ pathways in spiral form |
| DEP4104702.8 | 1991-02-15 |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA2104119A1 true CA2104119A1 (en) | 1992-08-16 |
Family
ID=6425135
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002104119A Abandoned CA2104119A1 (en) | 1991-02-15 | 1992-02-12 | Spiral implant for organ pathways |
Country Status (8)
| Country | Link |
|---|---|
| US (1) | US5536274A (en) |
| EP (1) | EP0571422B1 (en) |
| JP (1) | JPH06504931A (en) |
| AT (1) | ATE110551T1 (en) |
| CA (1) | CA2104119A1 (en) |
| DE (2) | DE4104702C2 (en) |
| DK (1) | DK0571422T3 (en) |
| WO (1) | WO1992014408A1 (en) |
Families Citing this family (229)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US6083220A (en) | 1990-03-13 | 2000-07-04 | The Regents Of The University Of California | Endovascular electrolytically detachable wire and tip for the formation of thrombus in arteries, veins, aneurysms, vascular malformations and arteriovenous fistulas |
| USRE41029E1 (en) | 1990-03-13 | 2009-12-01 | The Regents Of The University Of California | Endovascular electrolytically detachable wire and tip for the formation of thrombus in arteries, veins, aneurysms, vascular malformations and arteriovenous fistulas |
| USRE42625E1 (en) | 1990-03-13 | 2011-08-16 | The Regents Of The University Of California | Endovascular electrolytically detachable wire and tip for the formation of thrombus in arteries, veins, aneurysms, vascular malformations and arteriovenous fistulas |
| US5413601A (en) * | 1990-03-26 | 1995-05-09 | Keshelava; Viktor V. | Tubular organ prosthesis |
| US5562725A (en) | 1992-09-14 | 1996-10-08 | Meadox Medicals Inc. | Radially self-expanding implantable intraluminal device |
| USRE37117E1 (en) | 1992-09-22 | 2001-03-27 | Target Therapeutics, Inc. | Detachable embolic coil assembly using interlocking clasps and method of use |
| IL106946A0 (en) * | 1992-09-22 | 1993-12-28 | Target Therapeutics Inc | Detachable embolic coil assembly |
| FR2696636A1 (en) * | 1992-10-13 | 1994-04-15 | Balt Sa | Temporary wire-based blocking system for blood vessel etc. - uses coiled tubular tungsten@ wire to promote localised clotting, with hollow catheter for introduction of wire to required location |
| US5690666A (en) * | 1992-11-18 | 1997-11-25 | Target Therapeutics, Inc. | Ultrasoft embolism coils and process for using them |
| US5716410A (en) * | 1993-04-30 | 1998-02-10 | Scimed Life Systems, Inc. | Temporary stent and method of use |
| FR2706764B1 (en) * | 1993-06-24 | 1995-08-04 | Synthelabo | |
| DE4339265A1 (en) * | 1993-11-18 | 1995-05-24 | Angiomed Ag | Vena cava filter |
| US5725546A (en) * | 1994-06-24 | 1998-03-10 | Target Therapeutics, Inc. | Detachable microcoil delivery catheter |
| DE9413645U1 (en) * | 1994-08-24 | 1994-10-27 | Schneidt Bernhard Ing Grad | Device for closing a duct, in particular the ductus arteriosus |
| US5879366A (en) * | 1996-12-20 | 1999-03-09 | W.L. Gore & Associates, Inc. | Self-expanding defect closure device and method of making and using |
| US6171329B1 (en) | 1994-12-19 | 2001-01-09 | Gore Enterprise Holdings, Inc. | Self-expanding defect closure device and method of making and using |
| US5814062A (en) * | 1994-12-22 | 1998-09-29 | Target Therapeutics, Inc. | Implant delivery assembly with expandable coupling/decoupling mechanism |
| US6638291B1 (en) * | 1995-04-20 | 2003-10-28 | Micrus Corporation | Three dimensional, low friction vasoocclusive coil, and method of manufacture |
| US6171326B1 (en) | 1998-08-27 | 2001-01-09 | Micrus Corporation | Three dimensional, low friction vasoocclusive coil, and method of manufacture |
| US8790363B2 (en) * | 1995-04-20 | 2014-07-29 | DePuy Synthes Products, LLC | Three dimensional, low friction vasoocclusive coil, and method of manufacture |
| US5645558A (en) * | 1995-04-20 | 1997-07-08 | Medical University Of South Carolina | Anatomically shaped vasoocclusive device and method of making the same |
| US5639277A (en) * | 1995-04-28 | 1997-06-17 | Target Therapeutics, Inc. | Embolic coils with offset helical and twisted helical shapes |
| US5624461A (en) | 1995-06-06 | 1997-04-29 | Target Therapeutics, Inc. | Three dimensional in-filling vaso-occlusive coils |
| US5766160A (en) * | 1995-06-06 | 1998-06-16 | Target Therapeutics, Inc. | Variable stiffness coils |
| US5707389A (en) * | 1995-06-07 | 1998-01-13 | Baxter International Inc. | Side branch occlusion catheter device having integrated endoscope for performing endoscopically visualized occlusion of the side branches of an anatomical passageway |
| DE19531659C2 (en) * | 1995-08-29 | 1998-07-02 | Ernst Peter Prof Dr M Strecker | Stent |
| FR2742650B1 (en) * | 1995-12-20 | 1998-03-13 | Braun Celsa Sa | CATHETER FILTER HAVING A SERPENTINE TERMINAL |
| DE19604817C2 (en) * | 1996-02-09 | 2003-06-12 | Pfm Prod Fuer Die Med Ag | Device for closing defect openings in the human or animal body |
| US5871537A (en) | 1996-02-13 | 1999-02-16 | Scimed Life Systems, Inc. | Endovascular apparatus |
| US5649949A (en) * | 1996-03-14 | 1997-07-22 | Target Therapeutics, Inc. | Variable cross-section conical vasoocclusive coils |
| FR2747301B1 (en) * | 1996-04-10 | 1998-09-18 | Nycomed Lab Sa | IMPLANTABLE DEVICE FOR MAINTAINING OR RE-ESTABLISHING THE NORMAL PASSAGE SECTION OF A BODY DUCT, AS WELL AS A SYSTEM FOR ITS PLACEMENT |
| EP0902651B1 (en) * | 1996-05-14 | 2002-07-17 | PFM Produkte für die Medizin Aktiengesellschaft | Strengthened implant for bodily ducts |
| DE19704269A1 (en) * | 1996-05-14 | 1997-11-20 | Pfm Prod Fuer Die Med Ag | Reinforced implant for organ pathways |
| US6190402B1 (en) * | 1996-06-21 | 2001-02-20 | Musc Foundation For Research Development | Insitu formable and self-forming intravascular flow modifier (IFM) and IFM assembly for deployment of same |
| US5709702A (en) * | 1996-10-15 | 1998-01-20 | Cogita; Giuseppe | Surgical device for repairing aneurysms |
| US6984240B1 (en) * | 1996-10-25 | 2006-01-10 | Target Therapeutics, Inc. | Detachable multidiameter vasoocclusive coil |
| US7959664B2 (en) | 1996-12-26 | 2011-06-14 | Medinol, Ltd. | Flat process of drug coating for stents |
| US5906759A (en) | 1996-12-26 | 1999-05-25 | Medinol Ltd. | Stent forming apparatus with stent deforming blades |
| US5733329A (en) * | 1996-12-30 | 1998-03-31 | Target Therapeutics, Inc. | Vaso-occlusive coil with conical end |
| US5858556A (en) * | 1997-01-21 | 1999-01-12 | Uti Corporation | Multilayer composite tubular structure and method of making |
| ATE275888T1 (en) * | 1997-01-29 | 2004-10-15 | Endovascular Tech Inc | MODULAR STENT FABRIC WITH BELL-SHAPED EXTENDED END |
| NL1005197C2 (en) * | 1997-02-06 | 1998-08-07 | Cordis Europ | Filter for inserting in main artery |
| US5911717A (en) * | 1997-03-17 | 1999-06-15 | Precision Vascular Systems, Inc. | Catheter deliverable thrombogenic apparatus and method |
| US5800454A (en) * | 1997-03-17 | 1998-09-01 | Sarcos, Inc. | Catheter deliverable coiled wire thromboginic apparatus and method |
| US5836966A (en) | 1997-05-22 | 1998-11-17 | Scimed Life Systems, Inc. | Variable expansion force stent |
| US6860893B2 (en) | 1997-08-29 | 2005-03-01 | Boston Scientific Scimed, Inc. | Stable coil designs |
| US6322576B1 (en) | 1997-08-29 | 2001-11-27 | Target Therapeutics, Inc. | Stable coil designs |
| WO1999012484A1 (en) | 1997-09-05 | 1999-03-18 | Neurovasx, Inc. | Vessel occlusion device |
| US6159165A (en) * | 1997-12-05 | 2000-12-12 | Micrus Corporation | Three dimensional spherical micro-coils manufactured from radiopaque nickel-titanium microstrand |
| US6168570B1 (en) | 1997-12-05 | 2001-01-02 | Micrus Corporation | Micro-strand cable with enhanced radiopacity |
| US5954737A (en) * | 1997-12-19 | 1999-09-21 | Neurovasx, Inc. | Thrombus macerator catheter |
| US6395019B2 (en) | 1998-02-09 | 2002-05-28 | Trivascular, Inc. | Endovascular graft |
| EP1082072B8 (en) | 1998-06-04 | 2014-03-05 | New York University | Endovascular thin film devices for treating and preventing stroke |
| US20020087184A1 (en) * | 1998-06-18 | 2002-07-04 | Eder Joseph C. | Water-soluble coating for bioactive devices |
| US5980550A (en) | 1998-06-18 | 1999-11-09 | Target Therapeutics, Inc. | Water-soluble coating for bioactive vasoocclusive devices |
| NL1009551C2 (en) * | 1998-07-03 | 2000-01-07 | Cordis Europ | Vena cava filter with improvements for controlled ejection. |
| US6478773B1 (en) | 1998-12-21 | 2002-11-12 | Micrus Corporation | Apparatus for deployment of micro-coil using a catheter |
| US6224610B1 (en) | 1998-08-31 | 2001-05-01 | Micrus Corporation | Shape memory polymer intravascular delivery system with heat transfer medium |
| EP1600125A3 (en) * | 1998-09-29 | 2006-08-30 | C.R.Bard, Inc. | Coiled stent for drug delivery |
| US6358276B1 (en) | 1998-09-30 | 2002-03-19 | Impra, Inc. | Fluid containing endoluminal stent |
| US6042597A (en) | 1998-10-23 | 2000-03-28 | Scimed Life Systems, Inc. | Helical stent design |
| US6475234B1 (en) * | 1998-10-26 | 2002-11-05 | Medinol, Ltd. | Balloon expandable covered stents |
| US6187024B1 (en) | 1998-11-10 | 2001-02-13 | Target Therapeutics, Inc. | Bioactive coating for vaso-occlusive devices |
| US6723112B2 (en) | 1998-11-10 | 2004-04-20 | Scimed Life Systems, Inc. | Bioactive three loop coil |
| US8016852B2 (en) * | 1998-11-10 | 2011-09-13 | Stryker Corporation | Bioactive components for incorporation with vaso-occlusive members |
| US6569179B2 (en) | 1998-11-10 | 2003-05-27 | Scimed Life Systems, Inc. | Bioactive three loop coil |
| US6383204B1 (en) | 1998-12-15 | 2002-05-07 | Micrus Corporation | Variable stiffness coil for vasoocclusive devices |
| US6835185B2 (en) | 1998-12-21 | 2004-12-28 | Micrus Corporation | Intravascular device deployment mechanism incorporating mechanical detachment |
| US7018401B1 (en) | 1999-02-01 | 2006-03-28 | Board Of Regents, The University Of Texas System | Woven intravascular devices and methods for making the same and apparatus for delivery of the same |
| US6986784B1 (en) * | 1999-05-14 | 2006-01-17 | C. R. Bard, Inc. | Implant anchor systems |
| AU5179900A (en) * | 1999-06-02 | 2000-12-18 | Sethel Interventional, Inc. | Intracorporeal occlusive device |
| US6280457B1 (en) | 1999-06-04 | 2001-08-28 | Scimed Life Systems, Inc. | Polymer covered vaso-occlusive devices and methods of producing such devices |
| AU6058000A (en) * | 1999-07-12 | 2001-01-30 | Scimed Life Systems, Inc. | Liquid based vaso-occlusive compositions |
| US6602261B2 (en) | 1999-10-04 | 2003-08-05 | Microvention, Inc. | Filamentous embolic device with expansile elements |
| US6616591B1 (en) | 1999-12-08 | 2003-09-09 | Scimed Life Systems, Inc. | Radioactive compositions and methods of use thereof |
| DE10000137A1 (en) | 2000-01-04 | 2001-07-12 | Pfm Prod Fuer Die Med Ag | Implantate for closing defect apertures in human or animal bodies, bearing structure of which can be reversed from secondary to primary form by elastic force |
| US7867186B2 (en) * | 2002-04-08 | 2011-01-11 | Glaukos Corporation | Devices and methods for treatment of ocular disorders |
| US20020128701A1 (en) * | 2000-04-28 | 2002-09-12 | Winters R. Edward | Low profile expandable hoop support device for flexible tubes |
| US6334864B1 (en) * | 2000-05-17 | 2002-01-01 | Aga Medical Corp. | Alignment member for delivering a non-symmetric device with a predefined orientation |
| US6605101B1 (en) * | 2000-09-26 | 2003-08-12 | Microvention, Inc. | Microcoil vaso-occlusive device with multi-axis secondary configuration |
| US7029486B2 (en) | 2000-09-26 | 2006-04-18 | Microvention, Inc. | Microcoil vaso-occlusive device with multi-axis secondary configuration |
| US7033374B2 (en) * | 2000-09-26 | 2006-04-25 | Microvention, Inc. | Microcoil vaso-occlusive device with multi-axis secondary configuration |
| US6635069B1 (en) | 2000-10-18 | 2003-10-21 | Scimed Life Systems, Inc. | Non-overlapping spherical three-dimensional coil |
| US7344539B2 (en) | 2001-03-30 | 2008-03-18 | Depuy Acromed, Inc. | Intervertebral connection system |
| US6602269B2 (en) | 2001-03-30 | 2003-08-05 | Scimed Life Systems | Embolic devices capable of in-situ reinforcement |
| US7144413B2 (en) | 2001-04-20 | 2006-12-05 | Synthes (U.S.A.) | Graft fixation system and method |
| US20030004568A1 (en) * | 2001-05-04 | 2003-01-02 | Concentric Medical | Coated combination vaso-occlusive device |
| EP1392182A1 (en) * | 2001-05-04 | 2004-03-03 | Concentric Medical | Hydrogel vaso-occlusive device |
| US20020193813A1 (en) * | 2001-05-04 | 2002-12-19 | Concentric Medical | Hydrogel filament vaso-occlusive device |
| US6585754B2 (en) | 2001-05-29 | 2003-07-01 | Scimed Life Systems, Inc. | Absorbable implantable vaso-occlusive member |
| JP4383746B2 (en) * | 2001-05-29 | 2009-12-16 | マイクロベンション インコーポレイテッド | Method for producing inflatable thread-like embolic device |
| US8715312B2 (en) | 2001-07-20 | 2014-05-06 | Microvention, Inc. | Aneurysm treatment device and method of use |
| US8252040B2 (en) | 2001-07-20 | 2012-08-28 | Microvention, Inc. | Aneurysm treatment device and method of use |
| US7572288B2 (en) * | 2001-07-20 | 2009-08-11 | Microvention, Inc. | Aneurysm treatment device and method of use |
| WO2003037191A1 (en) * | 2001-10-26 | 2003-05-08 | Concentric Medical | Device for vaso-occlusion |
| US7147661B2 (en) | 2001-12-20 | 2006-12-12 | Boston Scientific Santa Rosa Corp. | Radially expandable stent |
| WO2003053288A1 (en) | 2001-12-20 | 2003-07-03 | Trivascular, Inc. | Advanced endovascular graft |
| US7037288B2 (en) * | 2002-01-14 | 2006-05-02 | Codman & Shurtleff, Inc. | Anti-block catheter |
| US20030191492A1 (en) * | 2002-04-05 | 2003-10-09 | Scimed Life Systems, Inc. | Radial coil expandable medical wire |
| US7122048B2 (en) * | 2002-05-03 | 2006-10-17 | Scimed Life Systems, Inc. | Hypotube endoluminal device |
| CA2494287C (en) | 2002-07-31 | 2010-11-09 | Microvention, Inc. | Three element coaxial vaso-occlusive device |
| US20050171572A1 (en) | 2002-07-31 | 2005-08-04 | Microvention, Inc. | Multi-layer coaxial vaso-occlusive device |
| US7682392B2 (en) | 2002-10-30 | 2010-03-23 | Depuy Spine, Inc. | Regenerative implants for stabilizing the spine and devices for attachment of said implants |
| US20040115164A1 (en) * | 2002-12-17 | 2004-06-17 | Pierce Ryan K. | Soft filament occlusive device delivery system |
| DE10362223B4 (en) * | 2003-01-21 | 2010-02-04 | pfm Produkte für die Medizin AG | Basic coil shape |
| US20050043783A1 (en) * | 2003-06-09 | 2005-02-24 | Amis James Peter | Helical endoluminal stent and related methods |
| US7803178B2 (en) | 2004-01-30 | 2010-09-28 | Trivascular, Inc. | Inflatable porous implants and methods for drug delivery |
| US8444668B2 (en) * | 2004-09-17 | 2013-05-21 | DePuy Synthes Products, LLC | Expandable vascular occlusion device |
| DE502004010411D1 (en) | 2004-09-22 | 2009-12-31 | Dendron Gmbh | DEVICE FOR IMPLANTING MICROWAVES |
| ES2321300T3 (en) * | 2004-09-22 | 2009-06-04 | Dendron Gmbh | MEDICAL IMPLANT |
| US20060074409A1 (en) * | 2004-10-05 | 2006-04-06 | Scimed Life Systems, Inc. | Detachable shaft medical retrieval device and related methods of use |
| US8535345B2 (en) * | 2004-10-07 | 2013-09-17 | DePuy Synthes Products, LLC | Vasoocclusive coil with biplex windings to improve mechanical properties |
| EP1827251B8 (en) * | 2004-11-09 | 2013-12-11 | Stryker Corporation | Vaso-occlusive devices comprising complex-shape proximal portion and smaller diameter distal portion |
| US9974680B2 (en) | 2004-12-27 | 2018-05-22 | Spatz Fgia, Inc. | System and methods for internalization of external components of adjustable intragastric balloon |
| US8403952B2 (en) * | 2004-12-27 | 2013-03-26 | Spatz-Fgia, Inc. | Floating gastrointestinal anchor |
| WO2014082044A1 (en) | 2012-11-26 | 2014-05-30 | Spatz Fgia, Inc. | System and methods for internalization of components of an adjustable intragastric balloon |
| US20060155324A1 (en) * | 2005-01-12 | 2006-07-13 | Porter Stephen C | Vaso-occlusive devices with attached polymer structures |
| US7967747B2 (en) * | 2005-05-10 | 2011-06-28 | Boston Scientific Scimed, Inc. | Filtering apparatus and methods of use |
| AU2006330786B2 (en) | 2005-11-17 | 2012-02-02 | Microvention, Inc. | Three-dimensional complex coil |
| US8152839B2 (en) | 2005-12-19 | 2012-04-10 | Boston Scientific Scimed, Inc. | Embolic coils |
| ATE521289T1 (en) | 2005-12-19 | 2011-09-15 | Boston Scient Ltd | SPIRALS MADE FROM A FLAT RIBBON FOR EMBOLIZATION |
| US8101197B2 (en) * | 2005-12-19 | 2012-01-24 | Stryker Corporation | Forming coils |
| US8828077B2 (en) | 2006-03-15 | 2014-09-09 | Medinol Ltd. | Flat process of preparing drug eluting stents |
| US20070225799A1 (en) * | 2006-03-24 | 2007-09-27 | Medtronic Vascular, Inc. | Stent, intraluminal stent delivery system, and method of treating a vascular condition |
| ES2592316T3 (en) * | 2006-03-28 | 2016-11-29 | Spatz-Fgia Inc | Floating gastrointestinal anchor |
| WO2007121405A2 (en) | 2006-04-17 | 2007-10-25 | Micro Therapeutics, Inc. | System and method for mechanically positioning intravascular implants |
| US8777979B2 (en) | 2006-04-17 | 2014-07-15 | Covidien Lp | System and method for mechanically positioning intravascular implants |
| KR101443926B1 (en) | 2006-06-15 | 2014-10-02 | 마이크로벤션, 인코포레이티드 | Embolization device constructed from expansible polymer |
| CN103767810B (en) | 2006-10-22 | 2016-06-15 | Idev科技公司 | From the manufacturing process of extendable bracket |
| KR101659197B1 (en) | 2006-10-22 | 2016-09-22 | 이데브 테크놀로지스, 아이엔씨. | Devices and methods for stent advancement |
| WO2008112435A2 (en) | 2007-03-13 | 2008-09-18 | Micro Therapeutics, Inc. | An implant including a coil and a stretch-resistant member |
| KR20100015521A (en) | 2007-03-13 | 2010-02-12 | 마이크로 테라퓨틱스 인코포레이티드 | An implant, a mandrel, and a method of forming an implant |
| JP5734650B2 (en) | 2007-06-25 | 2015-06-17 | マイクロベンション インコーポレイテッド | Self-expanding prosthesis |
| EP2173289A4 (en) | 2007-07-17 | 2010-11-24 | Transcend Medical Inc | Ocular implant with hydrogel expansion capabilities |
| WO2009026253A2 (en) | 2007-08-17 | 2009-02-26 | Micrus Endovascular Corporation | A twisted primary coil for vascular therapy |
| US8226701B2 (en) | 2007-09-26 | 2012-07-24 | Trivascular, Inc. | Stent and delivery system for deployment thereof |
| US8066755B2 (en) | 2007-09-26 | 2011-11-29 | Trivascular, Inc. | System and method of pivoted stent deployment |
| US8663309B2 (en) | 2007-09-26 | 2014-03-04 | Trivascular, Inc. | Asymmetric stent apparatus and method |
| AU2008308474B2 (en) | 2007-10-04 | 2014-07-24 | Trivascular, Inc. | Modular vascular graft for low profile percutaneous delivery |
| US8083789B2 (en) | 2007-11-16 | 2011-12-27 | Trivascular, Inc. | Securement assembly and method for expandable endovascular device |
| US8328861B2 (en) | 2007-11-16 | 2012-12-11 | Trivascular, Inc. | Delivery system and method for bifurcated graft |
| NZ586186A (en) * | 2007-12-17 | 2012-08-31 | Mallinckrodt Llc | Processes for the preparation of normorphinan salts |
| JP5366974B2 (en) | 2007-12-21 | 2013-12-11 | マイクロベンション インコーポレイテッド | System and method for determining the position of a separation zone of a separable implant |
| EP2266639B1 (en) | 2007-12-21 | 2016-10-05 | MicroVention, Inc. | Methods for preparing hydrogel filaments for biomedical use |
| WO2009086214A1 (en) | 2007-12-21 | 2009-07-09 | Microvention, Inc. | A system and method of detecting implant detachment |
| US8956378B2 (en) * | 2008-02-29 | 2015-02-17 | Cook Biotech Incorporated | Coated embolization device |
| US9833149B2 (en) | 2008-03-18 | 2017-12-05 | Circa Scientific, Llc | Methods, apparatus and systems for facilitating introduction of shaped medical instruments into the body of a subject |
| JP2011517417A (en) * | 2008-03-18 | 2011-06-09 | サーカ・サイエンティフィック，エルエルシー | Large surface area temperature sensing device |
| US20100010520A1 (en) | 2008-07-11 | 2010-01-14 | Olympus Medical Systems Corp. | Tissue fastener |
| US8162958B2 (en) * | 2008-07-11 | 2012-04-24 | Olympus Medical Systems Corp. | Tissue fastening tool and applicator for indwelling the same within body, and tissue fastening method through natural orifice |
| US20100010514A1 (en) | 2008-07-11 | 2010-01-14 | Olympus Medical Systems Corp. | Tissue fastening tool |
| US20110282426A1 (en) * | 2009-01-23 | 2011-11-17 | Ashish Sudhir Mitra | Endovascular devices and associated systems and methods |
| DE102009009003A1 (en) * | 2009-02-16 | 2010-08-26 | Justus-Liebig-Universität Giessen | implant |
| US20110066175A1 (en) * | 2009-05-07 | 2011-03-17 | Rainbow Medical Ltd. | Gastric anchor |
| US8414559B2 (en) | 2009-05-07 | 2013-04-09 | Rainbow Medical Ltd. | Gastroretentive duodenal pill |
| US9283305B2 (en) | 2009-07-09 | 2016-03-15 | Medtronic Vascular, Inc. | Hollow tubular drug eluting medical devices |
| US8425586B2 (en) * | 2009-09-02 | 2013-04-23 | Novostent Corporation | Vascular prosthesis with stress relief slots |
| US8381774B2 (en) * | 2009-09-20 | 2013-02-26 | Medtronic Vascular, Inc. | Methods for loading a drug eluting medical device |
| US20110070358A1 (en) * | 2009-09-20 | 2011-03-24 | Medtronic Vascular, Inc. | Method of forming hollow tubular drug eluting medical devices |
| US8678046B2 (en) | 2009-09-20 | 2014-03-25 | Medtronic Vascular, Inc. | Apparatus and methods for loading a drug eluting medical device |
| US8828474B2 (en) | 2009-09-20 | 2014-09-09 | Medtronic Vascular, Inc. | Apparatus and methods for loading a drug eluting medical device |
| CN102665606A (en) * | 2009-09-24 | 2012-09-12 | 微排放器公司 | Injectable hydrogel filaments for biomedical uses |
| US20110092998A1 (en) * | 2009-10-13 | 2011-04-21 | Spatz Fgia, Inc. | Balloon hydraulic and gaseous expansion system |
| JP5722333B2 (en) * | 2009-10-26 | 2015-05-20 | マイクロベンション インコーポレイテッド | Embolization device composed of expandable polymer |
| US8529492B2 (en) | 2009-12-23 | 2013-09-10 | Trascend Medical, Inc. | Drug delivery devices and methods |
| US9561125B2 (en) | 2010-04-14 | 2017-02-07 | Microvention, Inc. | Implant delivery device |
| US9744339B2 (en) | 2010-05-12 | 2017-08-29 | Circa Scientific, Llc | Apparatus for manually manipulating hollow organs |
| US9023095B2 (en) | 2010-05-27 | 2015-05-05 | Idev Technologies, Inc. | Stent delivery system with pusher assembly |
| US8545430B2 (en) | 2010-06-09 | 2013-10-01 | Transcend Medical, Inc. | Expandable ocular devices |
| US9526648B2 (en) | 2010-06-13 | 2016-12-27 | Synerz Medical, Inc. | Intragastric device for treating obesity |
| US8628554B2 (en) | 2010-06-13 | 2014-01-14 | Virender K. Sharma | Intragastric device for treating obesity |
| US10010439B2 (en) | 2010-06-13 | 2018-07-03 | Synerz Medical, Inc. | Intragastric device for treating obesity |
| US10420665B2 (en) | 2010-06-13 | 2019-09-24 | W. L. Gore & Associates, Inc. | Intragastric device for treating obesity |
| WO2012002944A1 (en) | 2010-06-29 | 2012-01-05 | Artventive Medical Group, Inc. | Reducing flow through a tubular structure |
| US9247942B2 (en) | 2010-06-29 | 2016-02-02 | Artventive Medical Group, Inc. | Reversible tubal contraceptive device |
| US8632846B2 (en) | 2010-09-17 | 2014-01-21 | Medtronic Vascular, Inc. | Apparatus and methods for loading a drug eluting medical device |
| US8333801B2 (en) | 2010-09-17 | 2012-12-18 | Medtronic Vascular, Inc. | Method of Forming a Drug-Eluting Medical Device |
| US8616040B2 (en) | 2010-09-17 | 2013-12-31 | Medtronic Vascular, Inc. | Method of forming a drug-eluting medical device |
| US9149277B2 (en) | 2010-10-18 | 2015-10-06 | Artventive Medical Group, Inc. | Expandable device delivery |
| US8489649B2 (en) | 2010-12-13 | 2013-07-16 | Oracle International Corporation | Extensible RDF databases |
| WO2015134768A1 (en) | 2011-01-11 | 2015-09-11 | Amsel Medical Corporation | Method and apparatus for occluding a blood vessel and/or other tubular structures |
| WO2012145431A2 (en) | 2011-04-18 | 2012-10-26 | Microvention, Inc. | Embolic devices |
| CA2835427A1 (en) | 2011-05-11 | 2012-11-15 | Microvention, Inc. | Device for occluding a lumen |
| EP2755574A1 (en) * | 2011-09-13 | 2014-07-23 | Stryker Corporation | Vaso-occlusive device |
| KR20140098794A (en) * | 2011-11-23 | 2014-08-08 | 마이크로벤션, 인코포레이티드 | Embolic device with shaped wire |
| US9579104B2 (en) | 2011-11-30 | 2017-02-28 | Covidien Lp | Positioning and detaching implants |
| US9011480B2 (en) | 2012-01-20 | 2015-04-21 | Covidien Lp | Aneurysm treatment coils |
| WO2013119332A2 (en) | 2012-02-09 | 2013-08-15 | Stout Medical Group, L.P. | Embolic device and methods of use |
| US9687245B2 (en) | 2012-03-23 | 2017-06-27 | Covidien Lp | Occlusive devices and methods of use |
| US8992595B2 (en) | 2012-04-04 | 2015-03-31 | Trivascular, Inc. | Durable stent graft with tapered struts and stable delivery methods and devices |
| US9498363B2 (en) | 2012-04-06 | 2016-11-22 | Trivascular, Inc. | Delivery catheter for endovascular device |
| US9011884B2 (en) | 2012-04-18 | 2015-04-21 | Microvention, Inc. | Embolic devices |
| WO2014058043A1 (en) * | 2012-10-12 | 2014-04-17 | 日本発條株式会社 | Member for implanting in living organism, stent, embolization member, blood vessel expansion kit, and aneurysm embolization kit |
| US9095344B2 (en) | 2013-02-05 | 2015-08-04 | Artventive Medical Group, Inc. | Methods and apparatuses for blood vessel occlusion |
| US8984733B2 (en) | 2013-02-05 | 2015-03-24 | Artventive Medical Group, Inc. | Bodily lumen occlusion |
| BR112015022327A2 (en) * | 2013-03-12 | 2017-07-18 | Pfm Medical Inc | vascular occlusion device configured for children |
| EP2967938B1 (en) | 2013-03-14 | 2017-03-01 | Medtronic Vascular Inc. | Method for manufacturing a stent and stent manufactured thereby |
| CN110101422A (en) | 2013-05-07 | 2019-08-09 | 阿姆泽尔医药公司 | For occluding vascular and/or the method and apparatus that two objects are fixed together |
| US9636116B2 (en) | 2013-06-14 | 2017-05-02 | Artventive Medical Group, Inc. | Implantable luminal devices |
| US9737308B2 (en) | 2013-06-14 | 2017-08-22 | Artventive Medical Group, Inc. | Catheter-assisted tumor treatment |
| US10149968B2 (en) | 2013-06-14 | 2018-12-11 | Artventive Medical Group, Inc. | Catheter-assisted tumor treatment |
| US9737306B2 (en) | 2013-06-14 | 2017-08-22 | Artventive Medical Group, Inc. | Implantable luminal devices |
| US20160066921A1 (en) * | 2014-02-21 | 2016-03-10 | Neuravi Limited | DEVICE AND METHOD FOR ENDOVASCULAR TREATMENT OF ANEURYSMS USING EMBOLIC ePTFE |
| US10124090B2 (en) | 2014-04-03 | 2018-11-13 | Terumo Corporation | Embolic devices |
| US9713475B2 (en) | 2014-04-18 | 2017-07-25 | Covidien Lp | Embolic medical devices |
| WO2015167752A1 (en) | 2014-04-29 | 2015-11-05 | Microvention, Inc. | Polymers including active agents |
| WO2015167751A1 (en) | 2014-04-29 | 2015-11-05 | Microvention, Inc. | Polymers |
| US10363043B2 (en) | 2014-05-01 | 2019-07-30 | Artventive Medical Group, Inc. | Treatment of incompetent vessels |
| US9060777B1 (en) | 2014-05-28 | 2015-06-23 | Tw Medical Technologies, Llc | Vaso-occlusive devices and methods of use |
| CN106604696A (en) | 2014-05-28 | 2017-04-26 | 斯瑞克欧洲控股有限责任公司 | Vaso-occlusive devices and methods of use |
| US10111670B2 (en) | 2015-05-01 | 2018-10-30 | DePuy Synthes Products, Inc. | Expandable vascular occlusion device with lead framing coil |
| WO2016182949A1 (en) | 2015-05-08 | 2016-11-17 | Stryker European Holdings I, Llc | Vaso-occlusive devices |
| WO2016201250A1 (en) | 2015-06-11 | 2016-12-15 | Microvention, Inc. | Expansile device for implantation |
| US10512713B2 (en) | 2015-07-20 | 2019-12-24 | Strataca Systems Limited | Method of removing excess fluid from a patient with hemodilution |
| US11541205B2 (en) | 2015-07-20 | 2023-01-03 | Roivios Limited | Coated urinary catheter or ureteral stent and method |
| US10918827B2 (en) | 2015-07-20 | 2021-02-16 | Strataca Systems Limited | Catheter device and method for inducing negative pressure in a patient's bladder |
| AU2016296866B2 (en) | 2015-07-20 | 2018-07-19 | Roivios Limited | Ureteral and bladder catheters and methods for inducing negative pressure to increase renal perfusion |
| US11229771B2 (en) | 2015-07-20 | 2022-01-25 | Roivios Limited | Percutaneous ureteral catheter |
| US10493232B2 (en) | 2015-07-20 | 2019-12-03 | Strataca Systems Limited | Ureteral catheters, bladder catheters, systems, kits and methods for inducing negative pressure to increase renal function |
| US10765834B2 (en) | 2015-07-20 | 2020-09-08 | Strataca Systems Limited | Ureteral and bladder catheters and methods of inducing negative pressure to increase renal perfusion |
| US10926062B2 (en) | 2015-07-20 | 2021-02-23 | Strataca Systems Limited | Ureteral and bladder catheters and methods of inducing negative pressure to increase renal perfusion |
| US11040180B2 (en) | 2015-07-20 | 2021-06-22 | Strataca Systems Limited | Systems, kits and methods for inducing negative pressure to increase renal function |
| US11040172B2 (en) | 2015-07-20 | 2021-06-22 | Strataca Systems Limited | Ureteral and bladder catheters and methods of inducing negative pressure to increase renal perfusion |
| US10307168B2 (en) | 2015-08-07 | 2019-06-04 | Terumo Corporation | Complex coil and manufacturing techniques |
| US10813644B2 (en) | 2016-04-01 | 2020-10-27 | Artventive Medical Group, Inc. | Occlusive implant and delivery system |
| US10779980B2 (en) | 2016-04-27 | 2020-09-22 | Synerz Medical, Inc. | Intragastric device for treating obesity |
| WO2018146547A1 (en) | 2017-02-09 | 2018-08-16 | Spatz FGIA Ltd | Check valve with docking station for gastrointestinal balloon |
| IT201800010311A1 (en) | 2018-11-14 | 2020-05-14 | Pfm Medical Ag | SYSTEM FOR THE CONNECTION OF A MEDICAL IMPLANT TO AN INSERTION AID |
| US11399840B2 (en) | 2019-08-13 | 2022-08-02 | Covidien Lp | Implantable embolization device |
Family Cites Families (14)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US3868956A (en) * | 1972-06-05 | 1975-03-04 | Ralph J Alfidi | Vessel implantable appliance and method of implanting it |
| DD158084A1 (en) * | 1981-05-08 | 1982-12-29 | Joachim Heinke | CLOSURE BODY AND METHOD FOR ITS MANUFACTURE |
| US4512338A (en) * | 1983-01-25 | 1985-04-23 | Balko Alexander B | Process for restoring patency to body vessels |
| DD223065A1 (en) * | 1983-12-21 | 1985-06-05 | Univ Berlin Humboldt | DEVICE WITH A LOCK BUTTER FOR CLOSING ADERN |
| DE3816906A1 (en) * | 1988-05-18 | 1989-11-30 | Drews Kurt Uromed Gmbh | Ureteral stent with releasably connected advance tube |
| US5019090A (en) * | 1988-09-01 | 1991-05-28 | Corvita Corporation | Radially expandable endoprosthesis and the like |
| EP0408245B1 (en) * | 1989-07-13 | 1994-03-02 | American Medical Systems, Inc. | Stent placement instrument |
| US5354295A (en) * | 1990-03-13 | 1994-10-11 | Target Therapeutics, Inc. | In an endovascular electrolytically detachable wire and tip for the formation of thrombus in arteries, veins, aneurysms, vascular malformations and arteriovenous fistulas |
| DE4038227C2 (en) * | 1990-11-30 | 2003-06-18 | Bosch Gmbh Robert | Electronic engine power control for a motor vehicle |
| US5256146A (en) * | 1991-10-11 | 1993-10-26 | W. D. Ensminger | Vascular catheterization system with catheter anchoring feature |
| US5372600A (en) * | 1991-10-31 | 1994-12-13 | Instent Inc. | Stent delivery systems |
| US5234437A (en) * | 1991-12-12 | 1993-08-10 | Target Therapeutics, Inc. | Detachable pusher-vasoocclusion coil assembly with threaded coupling |
| US5306294A (en) * | 1992-08-05 | 1994-04-26 | Ultrasonic Sensing And Monitoring Systems, Inc. | Stent construction of rolled configuration |
| US5312415A (en) * | 1992-09-22 | 1994-05-17 | Target Therapeutics, Inc. | Assembly for placement of embolic coils using frictional placement |
-
1991
- 1991-02-15 DE DE4104702A patent/DE4104702C2/en not_active Expired - Fee Related
-
1992
- 1992-02-12 AT AT92903988T patent/ATE110551T1/en not_active IP Right Cessation
- 1992-02-12 DK DK92903988.1T patent/DK0571422T3/en active
- 1992-02-12 CA CA002104119A patent/CA2104119A1/en not_active Abandoned
- 1992-02-12 EP EP92903988A patent/EP0571422B1/en not_active Expired - Lifetime
- 1992-02-12 JP JP4503971A patent/JPH06504931A/en active Pending
- 1992-02-12 DE DE59200446T patent/DE59200446D1/en not_active Expired - Fee Related
- 1992-02-12 WO PCT/EP1992/000294 patent/WO1992014408A1/en active IP Right Grant
- 1992-02-12 US US08/098,303 patent/US5536274A/en not_active Expired - Lifetime
Also Published As
| Publication number | Publication date |
|---|---|
| DK0571422T3 (en) | 1994-10-03 |
| DE4104702A1 (en) | 1992-08-20 |
| US5536274A (en) | 1996-07-16 |
| WO1992014408A1 (en) | 1992-09-03 |
| EP0571422A1 (en) | 1993-12-01 |
| EP0571422B1 (en) | 1994-08-31 |
| JPH06504931A (en) | 1994-06-09 |
| ATE110551T1 (en) | 1994-09-15 |
| DE4104702C2 (en) | 1996-01-18 |
| DE59200446D1 (en) | 1994-10-06 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CA2104119A1 (en) | Spiral implant for organ pathways | |
| US5256146A (en) | Vascular catheterization system with catheter anchoring feature | |
| US4922905A (en) | Dilatation catheter | |
| US5378239A (en) | Radially expandable fixation member constructed of recovery metal | |
| EP0466518B1 (en) | Endovascular grafting apparatus and system | |
| US5071407A (en) | Radially expandable fixation member | |
| EP2756821B1 (en) | Vascular implant | |
| US5984957A (en) | Radially expanded prostheses with axial diameter control | |
| CN103989499B (en) | For the occlusive implant of anatomical structure of hollow, induction system and correlation technique | |
| US20160242896A1 (en) | Methods for fluid flow through body passages | |
| US20040193209A1 (en) | Retrievable filter | |
| US20060241737A1 (en) | Fixation device for coronary venous lead | |
| JP2008521501A (en) | Method and apparatus for improving mitral valve function | |
| JPH06210004A (en) | Device to plant naturally expanding type intracorporeal protease in blood vessel | |
| CA2599413A1 (en) | Apparatus and method for sensor deployment and fixation | |
| US9108025B2 (en) | Apparatus and method for anchoring an elongated object in body lumens | |
| EP1078647B1 (en) | Balloon catheter | |
| KR20090073036A (en) | Percutaneous catheter directed intravascular occlusion devices | |
| JP2006528036A (en) | Method and apparatus for improving mitral valve function | |
| JP2010511428A (en) | Push-in sheath and placement device | |
| CN101553175A (en) | Anchoring and fixing implant and surgical assembly for its implantation | |
| US20080249602A1 (en) | Artificial Blood Vessel Stent | |
| US20230210533A1 (en) | Implant detachment systems with a modified pull wire | |
| CN215839711U (en) | Conveying sheath pipe with adjustable distal end angle | |
| US20230210535A1 (en) | Medical device delivery systems with twisting loop wires |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| FZDE | Discontinued |