CA1153264A - Medical vascular guide wire and self-guiding type catheter - Google Patents
Medical vascular guide wire and self-guiding type catheterInfo
- Publication number
- CA1153264A CA1153264A CA000344317A CA344317A CA1153264A CA 1153264 A CA1153264 A CA 1153264A CA 000344317 A CA000344317 A CA 000344317A CA 344317 A CA344317 A CA 344317A CA 1153264 A CA1153264 A CA 1153264A
- Authority
- CA
- Canada
- Prior art keywords
- hollow
- monofilament
- guide wire
- manipulating
- self
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired
Links
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/01—Introducing, guiding, advancing, emplacing or holding catheters
- A61M25/0105—Steering means as part of the catheter or advancing means; Markers for positioning
- A61M25/0125—Catheters carried by the bloodstream, e.g. with parachutes; Balloon catheters specially designed for this purpose
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/01—Introducing, guiding, advancing, emplacing or holding catheters
- A61M25/0105—Steering means as part of the catheter or advancing means; Markers for positioning
- A61M25/0108—Steering means as part of the catheter or advancing means; Markers for positioning using radio-opaque or ultrasound markers
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/01—Introducing, guiding, advancing, emplacing or holding catheters
- A61M25/09—Guide wires
- A61M25/09016—Guide wires with mandrils
- A61M25/09033—Guide wires with mandrils with fixed mandrils, e.g. mandrils fixed to tip; Tensionable wires
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/01—Introducing, guiding, advancing, emplacing or holding catheters
- A61M25/09—Guide wires
- A61M2025/09058—Basic structures of guide wires
- A61M2025/09066—Basic structures of guide wires having a coil without a core possibly combined with a sheath
Abstract
MEDICAL VASCULAR GUIDE WIRE AND SELF-GUIDING TYPE CATHETER ABSTRACT OF THE DISCLOSURE Disclosed is a medical vascular guide wire made of a synthetic resin hollow monofilament. The guide wire is comprised of a tip part, a flexible part having a smaller diameter than the other parts, a tapering part and a manipulating part, these four parts continuously forming in line, in that order, along the monofilament axis. At least the tip part and the manipulating part have X-ray impermeable material inserted in the respective hollows thereof. A self-guiding type catheter made of a synthetic resin, multi-hollow monofilament is also provided. The catheter is comprised of a tip part, a flexible part having a smaller diameter than the other parts, a tapering part and a manipulating part, these four parts continuously formed in line, in that order, along the monofilament axis: The catheter has at least two hollows extending at least from one end of the manipulating part to the tapering part or to the other end of the manipulating part or to a point in close proximity to said other end of the manipulating part. At least one of the hollows has an X-ray impermeable material inserted at least within the hollow in the manipulating part, and the other hollow or at least one of the other hollows form a lumen for permitting a liquid and/or a gas to pass therethrough.
Description
~1~i3Z6~
MEDICAL VASCULAR G~IDE WIRE AND SELF-GUIDING
TYPE CATHETER
BACKGROUND OF THE INVENTION
(1) Field of the Invention This invention relates to a medical vascular guide wire for aiding the insertion of a catheter into, particularly, blood vessels of the living body for withdrawal of blood and other specimens from the affected parts, or for infusion of a drug solution to the affected parts. It also relates to a self-guiding type catheter, namely, a catheter capable of guiding its tip to the peripheral blood vessels in the affected parts.
MEDICAL VASCULAR G~IDE WIRE AND SELF-GUIDING
TYPE CATHETER
BACKGROUND OF THE INVENTION
(1) Field of the Invention This invention relates to a medical vascular guide wire for aiding the insertion of a catheter into, particularly, blood vessels of the living body for withdrawal of blood and other specimens from the affected parts, or for infusion of a drug solution to the affected parts. It also relates to a self-guiding type catheter, namely, a catheter capable of guiding its tip to the peripheral blood vessels in the affected parts.
(2) Description of the Prior Art Most conventional guide wires are coil-form metal wires supplied by, for example, COOK Inc., Universal Medical Instrument Corp. and USCI, a division of C. R. Bard, Inc. These coiled metal wires have some disadvantages.
Namely, first, the coiled metal wires possess an uneven surface, and hence, thrombi are liable to be deposited ~ thereon. Secondly, the metal wires are too rigid to permit ; their tips to reach the blood vessels in the affected parts without causing undue strain or pain to the patient, or taking a great deal of time. Thirdly, the coiled metal wires are not easy to manipulate so that their tips will ~ ~ reach the affected parts. Fourthly, there is a danger that ;~ the coiled metal wires may injure the intimae of blood vessels.
; Most conventional catheters are made of synthetic resin tubes and supplied by, for example, niversal Medical Instrument Corp., Electro-Catheter Corp.
~ and USCI, a division of C.R.Bard, Inc. These catheters are -~ 30 used in combination with the aforesaid ~etal guide wires.
These catheters also have some disadvantages. That is first, the catheters are larger in diameter than the guide wires, and, therefore, it is difficult for the catheter tip ~:
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':
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to reach the intended location, particularly in peripheral blood vessels, where the guide wire has reached.
'Furthermore, it is generally difficult to accomplish the catheterization without causing undue strain or pain to the ~patient. Secondly, in the process of catheterization, many kinds of catheters and guide wires must be used in combination. Thus, the procedure requires a substantially long period of time.
SUMMARY OF THE INVENTION
Therefore, an object of the present invention is to provide a medical vascular guide wire, which has a smooth surface on which thrombi are deposited only to a slight extent, which is sufficiently flexible for permitting it to reach peripheral blood vessels in the affected parts without undue strain to the patient or taking a great deal of time, which is capable of being easily manipulated and which does not injure the intimae of blood vessels.
Another object of the present invention is to provide a self-guiding type catheter, namely, a catheter capable of guiding its tip to the peripheral blood vessels, which catheter possesses advantageous characteristics - similar to those mentioned above in the object directed to the guide wire.
Other objects and advantages of the present invention will be apparent from the following description.
In one aspect of the present invention, there is provided a medical vascular guide wire comprising a wire body made of a synthetic resin hollow monofilament and comprised o a tip part, a relatively flexible part having a smaller diameter than the other parts, a tapering part and a manipulating part, these four parts continuously forming in line, in that order, along the monofilament axis, and; at least the tip part and the manipulating part having X-ray impermeable material inserted in the 35 respective hollows thereof.
In another aspect of the present invention, there is provided a self-guiding type catheter comprising a ";
~1~3Z64 continuously extending body made of a synthetic resin multi-hollow monofilament and comprised of a tip part, a relatively flexible part having a smaller diameter than the other parts, a tapering part and a manipulating part, these four parts continuously formed in line, in that order, along the monofilament axis;
said body having at least two hollows extending at least from one end of the manipulating part to the tapering part or to the other end of the manipulating part or to a point in close proximity to said other end of the manipulating part, at least one of said hollows having an X-ray impermeable material inserted at least within the hollow in the manipulating part, and the other hollow or at least one of the other hollows forming a lumen for permitting a liquid andtor a gas to pass therethrough, which lumen is opened to the outside of the body through an inlet opening at the distal end of the lumen and through an outlet opening bored in the tapering part or in the adjacent portion thereto of the manipulating part and;
said body further having at least two hollows in the tip part, at least one of said hollows having an X-ray impermeable material inserted therein.
BRI EF DE S CRI PT ION OF THE DR AWI NGS
FIG. lA is an enlarged longitudinal sectional view illustrating one example of the guide wire of the invention;
FIG. lB is an enlarged transverse sectional view taken along the line A-A in FIG. l;
FIGs. 2 through 5 are diagrammatical views illustrating the state of the guide wire inserted in various blood vessels;
FIG. 6 is an enlarged longitudinal sectional view :~ illustrating another example of the guide wire of the invention;
: 35 FIG. 7A is an enlarged longitudinal sectional view illustrating one example of the self-guiding type catheter of the invention;
..
.
., ~3;26'1 FIG. 7B is an enlarged cross-sectional view taken along the line B-B in FIG. 7A;
FIG. 7C is an enlarged cross-sectional view illustrating a self-guiding type catheter similar to that illustrated in FIGs. 7A and 7B, but with three hollows;
FIG. 8A is an enlarged longitudinal sectional view illustrating another example of the self-guiding type catheter of the invention; and, FIG. 8B is an enlarged transverse sectiona view taken along the line C-C in FIG. 8A.
DESCRIPTION OF THE PREFERRED EMBODIMENTS
Referring to FIGs. lA and lB, the guide wire l is comprised of a tip part 6, a relatively flexible part 2 (which is hereinafter referred to as "flexible part" for brevity), a tapering part 3 and a manipulating part 4~
These four parts continously form in line, in that order, along the monofilament axis. The tip part 6 is of a hollow structure and has X-ray impermeable material 5 inserted therein. The shape of the tip part 6 is not particularly limited but may preferably be spherical, oval spherical or end-rounded cylindrical. The size of the tip part 6 is preferably about 0.5-3 mm, more preferably about 0.7-2 mm, in maximum diameter, and preferably about 0.5-5 mm, more preferably about 0.7-4 mm, in length.
The flexible part 2 may be either hollow or solid and possesses a substantially uniform diameter over its entixe length. The size of the flexible part 2 is preferably about 0.1-0.5 mm, more preferably about 0.15-0.4 mm, in diameter, and preerably about 10-100 mm, 30 more preferably about 20-70 mm, in length. The flexible part 2 possesses a smaller diameter, and is more flexible and pliable than the other parts, and furthermore, is sufficiently strong to prevent the guide wire fram being broken between the tip part 6 and the 1exible part 2.
The tapering part 3 tapers from its end adjacent to the manipulating part 4 toward the flexible part 2. The size of the tapering part 3 is preferably about 10-100 mm, ., 326~
more preferably about 20-70 mm, in length. ~lthough there may be no clear demarcation between the tapering part 3 and the flexible part 2, the total length of these two parts should preferably be not larger than 200 mm. The tapering part 3 may be either hollow or solid. It is, however, preferable that the tapering part 3 be hollow and have X-ray impermeable material inserted therein.
The manipulating part 4 is of a hollow monofilament structure. Its diameter is preferably about 0.5-3 mm, more preferably about 0.7-2 mm. Its length should be at least about 200 mm, preferably 50-200 cm and more preferably 70-150 cm. The manipulating part 4 has X-ray impermeable material 5 in the form of a wire of about 0.2-0.4 mm in diameter, inserted in the hollow thereof. The manipulating part 4 should preferably possess a high toughness and suitable degree of rigidity.
The above-mentioned numerical values for the size of the guide wire are mere exemplifications and it should be understood that the size of the guide wire is not particularly limited to such values.
The respective parts of the guide wire of the invention have the following functions. The tip part 6 is capable of freely moving in blood vessels and does not intrude into the walls of blood vessels. That is, the tip part 6 floats in the blood stream and reaches the intended parts without even a slight strain being caused on the patient, and therefore, there is no risk of injuring the intimae of blood vessels. This is in a striking contrast to conventional metal guide wires, which must be forced
Namely, first, the coiled metal wires possess an uneven surface, and hence, thrombi are liable to be deposited ~ thereon. Secondly, the metal wires are too rigid to permit ; their tips to reach the blood vessels in the affected parts without causing undue strain or pain to the patient, or taking a great deal of time. Thirdly, the coiled metal wires are not easy to manipulate so that their tips will ~ ~ reach the affected parts. Fourthly, there is a danger that ;~ the coiled metal wires may injure the intimae of blood vessels.
; Most conventional catheters are made of synthetic resin tubes and supplied by, for example, niversal Medical Instrument Corp., Electro-Catheter Corp.
~ and USCI, a division of C.R.Bard, Inc. These catheters are -~ 30 used in combination with the aforesaid ~etal guide wires.
These catheters also have some disadvantages. That is first, the catheters are larger in diameter than the guide wires, and, therefore, it is difficult for the catheter tip ~:
:~
~ ~: , . ~ . : , .
':
' ' ' ' ' ~53Z6~
to reach the intended location, particularly in peripheral blood vessels, where the guide wire has reached.
'Furthermore, it is generally difficult to accomplish the catheterization without causing undue strain or pain to the ~patient. Secondly, in the process of catheterization, many kinds of catheters and guide wires must be used in combination. Thus, the procedure requires a substantially long period of time.
SUMMARY OF THE INVENTION
Therefore, an object of the present invention is to provide a medical vascular guide wire, which has a smooth surface on which thrombi are deposited only to a slight extent, which is sufficiently flexible for permitting it to reach peripheral blood vessels in the affected parts without undue strain to the patient or taking a great deal of time, which is capable of being easily manipulated and which does not injure the intimae of blood vessels.
Another object of the present invention is to provide a self-guiding type catheter, namely, a catheter capable of guiding its tip to the peripheral blood vessels, which catheter possesses advantageous characteristics - similar to those mentioned above in the object directed to the guide wire.
Other objects and advantages of the present invention will be apparent from the following description.
In one aspect of the present invention, there is provided a medical vascular guide wire comprising a wire body made of a synthetic resin hollow monofilament and comprised o a tip part, a relatively flexible part having a smaller diameter than the other parts, a tapering part and a manipulating part, these four parts continuously forming in line, in that order, along the monofilament axis, and; at least the tip part and the manipulating part having X-ray impermeable material inserted in the 35 respective hollows thereof.
In another aspect of the present invention, there is provided a self-guiding type catheter comprising a ";
~1~3Z64 continuously extending body made of a synthetic resin multi-hollow monofilament and comprised of a tip part, a relatively flexible part having a smaller diameter than the other parts, a tapering part and a manipulating part, these four parts continuously formed in line, in that order, along the monofilament axis;
said body having at least two hollows extending at least from one end of the manipulating part to the tapering part or to the other end of the manipulating part or to a point in close proximity to said other end of the manipulating part, at least one of said hollows having an X-ray impermeable material inserted at least within the hollow in the manipulating part, and the other hollow or at least one of the other hollows forming a lumen for permitting a liquid andtor a gas to pass therethrough, which lumen is opened to the outside of the body through an inlet opening at the distal end of the lumen and through an outlet opening bored in the tapering part or in the adjacent portion thereto of the manipulating part and;
said body further having at least two hollows in the tip part, at least one of said hollows having an X-ray impermeable material inserted therein.
BRI EF DE S CRI PT ION OF THE DR AWI NGS
FIG. lA is an enlarged longitudinal sectional view illustrating one example of the guide wire of the invention;
FIG. lB is an enlarged transverse sectional view taken along the line A-A in FIG. l;
FIGs. 2 through 5 are diagrammatical views illustrating the state of the guide wire inserted in various blood vessels;
FIG. 6 is an enlarged longitudinal sectional view :~ illustrating another example of the guide wire of the invention;
: 35 FIG. 7A is an enlarged longitudinal sectional view illustrating one example of the self-guiding type catheter of the invention;
..
.
., ~3;26'1 FIG. 7B is an enlarged cross-sectional view taken along the line B-B in FIG. 7A;
FIG. 7C is an enlarged cross-sectional view illustrating a self-guiding type catheter similar to that illustrated in FIGs. 7A and 7B, but with three hollows;
FIG. 8A is an enlarged longitudinal sectional view illustrating another example of the self-guiding type catheter of the invention; and, FIG. 8B is an enlarged transverse sectiona view taken along the line C-C in FIG. 8A.
DESCRIPTION OF THE PREFERRED EMBODIMENTS
Referring to FIGs. lA and lB, the guide wire l is comprised of a tip part 6, a relatively flexible part 2 (which is hereinafter referred to as "flexible part" for brevity), a tapering part 3 and a manipulating part 4~
These four parts continously form in line, in that order, along the monofilament axis. The tip part 6 is of a hollow structure and has X-ray impermeable material 5 inserted therein. The shape of the tip part 6 is not particularly limited but may preferably be spherical, oval spherical or end-rounded cylindrical. The size of the tip part 6 is preferably about 0.5-3 mm, more preferably about 0.7-2 mm, in maximum diameter, and preferably about 0.5-5 mm, more preferably about 0.7-4 mm, in length.
The flexible part 2 may be either hollow or solid and possesses a substantially uniform diameter over its entixe length. The size of the flexible part 2 is preferably about 0.1-0.5 mm, more preferably about 0.15-0.4 mm, in diameter, and preerably about 10-100 mm, 30 more preferably about 20-70 mm, in length. The flexible part 2 possesses a smaller diameter, and is more flexible and pliable than the other parts, and furthermore, is sufficiently strong to prevent the guide wire fram being broken between the tip part 6 and the 1exible part 2.
The tapering part 3 tapers from its end adjacent to the manipulating part 4 toward the flexible part 2. The size of the tapering part 3 is preferably about 10-100 mm, ., 326~
more preferably about 20-70 mm, in length. ~lthough there may be no clear demarcation between the tapering part 3 and the flexible part 2, the total length of these two parts should preferably be not larger than 200 mm. The tapering part 3 may be either hollow or solid. It is, however, preferable that the tapering part 3 be hollow and have X-ray impermeable material inserted therein.
The manipulating part 4 is of a hollow monofilament structure. Its diameter is preferably about 0.5-3 mm, more preferably about 0.7-2 mm. Its length should be at least about 200 mm, preferably 50-200 cm and more preferably 70-150 cm. The manipulating part 4 has X-ray impermeable material 5 in the form of a wire of about 0.2-0.4 mm in diameter, inserted in the hollow thereof. The manipulating part 4 should preferably possess a high toughness and suitable degree of rigidity.
The above-mentioned numerical values for the size of the guide wire are mere exemplifications and it should be understood that the size of the guide wire is not particularly limited to such values.
The respective parts of the guide wire of the invention have the following functions. The tip part 6 is capable of freely moving in blood vessels and does not intrude into the walls of blood vessels. That is, the tip part 6 floats in the blood stream and reaches the intended parts without even a slight strain being caused on the patient, and therefore, there is no risk of injuring the intimae of blood vessels. This is in a striking contrast to conventional metal guide wires, which must be forced
3~ into blood vessels. The flexible part 2 permits the free movement of the tip part 6 in blood vessels. The tapering part 3 between the flexible part 2 and the manipulating part 4, ensures the unrestricted manipulation of the guide wire. Namely, a highly skilled and delicate manipulation of the guide wire can be easily effected, which manipulation is required for advancing the guide wire into the intended blood vessel branch at a turning point.
.
3;~6'~t Furthermore, the synthetic resin monofilament has a smooth surface and therefore, thrombi are deposited thereon only to a slight extent.
The guide wire of the invention may be made of any melt-extrudable thermoplastic synthetic resins. The thermoplastic synthetic resins used include, for example, polyesters, such as polyethylene terephthalate and polybutylene terephthalate; polyamides, such as nylon-6, nylon-66, nylon-610, nylon-ll, nylon-12 and nylon-6/66;
polyolefins, such as polyethylene and polypropylene; and, fluorine-containing resins, such as copolymer of tetrafluoroethylene with hexafluoropropylene. These thermoplastic synthetic resins may be used either alone or in combination.
The most preferable thermoplastic synthetic resins are a polyblend comprised of, based on the total weight of the polyblend, (i) 70 to 99% by weight of at least one melt-extrudable thermoplastic synthetic resin selected from the above-mentioned polyesters, polyamides and p~lyolefins, and (ii) 1 to 30% by weight of a fluorine-containing thermoplastic resin, such as polytetrafluoroethylene and polyvinylidene fluoride. me optimum amount of the fluorine-containing thermoplastic resin in the polyblend is from 3 to 15% by weight. The guide wire made of the above-mentioned polyblend exhibits an enhanced self-lubricating property. Therefore, the undesirable deposition of thrombi can be substantially avoided and, in addition, the manipulation of the guide wire is very easy.
The guide wire made only o~ a melt-extrudable 30 fluorine-containing thermoplastic synthetic resin also exhibits an enhanced self-lubricating property.
The X-ray impermeable (or radio-opaque) material is inserted at least in the tip part and the manipulating part of the guide wire, so that the guide wire can be monitored 35 from the outside of the patient body during the introduction of the guide wire into blood vessels. The X-ray impermeable material used includes, for example metal .
~1~3Z64 wires, such as a tungsten wire, and liquid contrast media, such as "CONRAY" ttrade mark, 6n w/v%
methylglucamine iothalamete, supplied by, Mallinkrodt Inc.) and "UROGRAFIN" ~trade mark, methyl~lucamine and sodium diatrigoate, supplied by Schering A.G.). These X-ray impermeable materials may be used either alone or in combination. Of these, tungsten is preferable because of its high radio-opacity.
The X-ray impermeable mat~rial to be inscrtod in the hollow of the tip part 6 may be of any shape or form, such as a finely divided powder, a rod and a sphere. Its size may be, for example, about 0.2 mm in diàmeter for the spherical or powdered material, and about 0.2 mm in diameter and about 0.4-0.6 mm in length for the rod-shaped material. The X-ray impermeable material to be inserted in the hollow of the manipulating part 4 may preferably be continuously extending wire, such as a tungsten wire, for imparting proper toughness and rigidity to the manipulating part. This metal wire is usually inserted over the entire length of the manipulating part, and its diameter is preferably about 0.2-0.4 mm.
The medical vascular guide wire illustrated in FIG. 6 is similar to that of FIGs. lA and lB, but with an X-ray impermeable metal wire 5, one end portion 5' of which is tapered toward the flexible part 2. The metal wire 5 is inserted in the hollow of the tip part 6 and the hollow extending fran one end of the manipulating part 4 to a midway point of the tapering part 3. The tapered metal wire S exhibits an enhanced flexibility, as compared with the non-tapered metal wire illustrated in FIG. lA, and thus, the guide wire can be more unrestrictedly moved in blood vessels and more easily manipulated.
The hollow monofilament body of the guide wire of the invention can be surface-treated in order to enhance its self-lubricating property and, thus, to ccmpletely avoid the risk of thrombus deposition and to make the .~
. . .
.
3Z~4 manipulation of the gui~e wire easy. The surface treatment employed includes (i) a silicone treatment, (ii) a fluorine-containing resin coating treatment or (iii) a plasma spark discharge treatment. These surface treatments can be effected as follows.
(i) Silicon coating treatment A hollow monofilament body is passed several times through a bath of a solution of a medical silicone disolved in, for example, isoprop~nol, and then, the ~o coated monofilament body is dried under reduced pressure, thereby removing the solvent therefrom. Prior to the silicone coating treatment, the monofilament body may be surface-treated with sandpaper in order to facilitate the silicone coating treatment.
(ii) Fluorine-containing resin coating treatment A hollow monofilament body is treated with a solution of a fluorine-containing resin, such as "Te~lon 30 J" (trade mark, an aqucous suspension containing about 60 weight % of finely divided polytetrafluoroethylene having a particle size of about 0.3 micron, supplied by Mitsui Fluorochemical Co.) and "Teflon D-l" (trade mark, an aqueous suspension of finely divided polytetra-fluoroethylene, supplied by Daikin Kogyo K.K.). The treating procedure may be similar to that explained above with regard to the silicone coating treatment.
(iii) Plasma spark discharge treatment A hollow monofilament body is placed in a chamber which is maintained at a reduced pressure of below about 1 mmHg and into which a small amount of a gaseous oxganic fluorocompound is introduced. Then, a plasma spark discharge is effected, thereby introducing fluorine substituents into the polymer forming the surface of the monofilament.
The medical vascular guide wire of the invention may be manufactured as follows. A thermoplastic synthetic resin is melt-extruded through an annular orifice of a spinneret provided in an extruder, to obtain an undrawn or ' .
~3Z6~
g slightly drawn continuous hollow monofilament. The continuous hollow monofilament is cut into predetermined lengths. A portion of the entire length of each hollow monofilament, which portion is adjacent to one end portion thereof, is drawn several times its original length, whereby a relatively flexible part and a tapering part are simultaneously formed. X-ray impermeable material is inserted into the hollow of the undrawn or slightly drawn end portion thereof and, then, its open end is heat-sealed to form the tip part. X-ray impermeable material is also inserted into the continuously extending hollow of the manipulating part from the end thereof opposite to the tip part and, then, the open end is heat-sealed. When the guide wire illustrated in FIG. 6 is manufactured, an X-ray impermeable metal wire, one end portion of which is tapered, is inserted so that the tapered end reaches a midway point of the tapering part.
The guide wire of the invention can be inserted into peripheral blood vessels so that its tip part is advanced to the affected parts, by a conventional manipulation procedure. Then, a catheter may be inserted in the blood vessels so that the catheter advances along the inserted guide wire.
The self-guiding type catheter will now be illustrated with reference to FIGs. 7A through 8B.
Referring to FIGs. 7~ and 7B, the self-guiding type catheter l' is made of a multi-hollow monofilament body having two continuously extending hollows and comprised of a tip part 6, a relatively flexible part 2, a tapering part 3 and a manipulating part 4. X-ray impermeable material 5 is inserted in one of the continuously extending hollows at least in the tip part 6 and in the manipulating part 4, and both ends of the X-ray impermeable material inserted hollow are closed. The other continuously extending hollow 9 forms a lumen for permitting liquid and/or gas, such as a drug solution, to pass therethrough, which lumen is opened to the outside of the monofilament body through an . ' ' , " ` .
~32~4 inlet opening $ at one end of the lumen 9 and through an outlet opening 7 bored in the tapering part 3. The outlet opening 7 may be bored not in the tapering part 3 but in a portion of the manipulating part 4, adjacent to the tapering part 3. The structure and function of the tip part 6, the flexible part 2 and the tapering part 3 are similar to those of the guide wire explained with reference to FIGs. lA and 6. The outlet opening 7 bored in the tapering part 3 or in a portion, adjacent thereto, of the manipulating part 4 preferably has a sectional shape, shown in FIG. 7A, such that the section becomes broader toward the outside of the monofilament body so as to avoid the undesirable retentivity of a drug solution. The inlet opening 8 may be capped when the catheter is not used.
Furthermore, the end portion of the monofilament body, having the inlet opening 8, may preferably be of a structure such that a connector or an injector can be connected thereto.
The self-guiding type catheter having the structure mentioned above with reference to FIGs. 7A and 7B is characterized as being very pliable and easy to manipulate.
Thus, it is easy to manipulate the catheter, inserted by degrees in blood vessels, so that the tip part of the catheter reaches the intended parts through large diameter curved blood vessels and small peripheral blood vessels. A
drug solution may be introduced into the catheter through the inlet opening thereof after the tip part thereof reaches the intended parts and, as a result, the drug solution can be selectively administered to the intended parts. Thus, a medical treatment can be accomplished without taking a great deal of time, i.e., without repeated insertion and withdrawal of guide wires and catheters. In stead of the infusion of a drug solution, the self-guiding type catheter may be used for, for example, the withdrawal of blood and other specimens and the monitering of heart functions.
It is preferable that the multi-hollow monofilament .
;~ :
3Z6~
body of the catheter have an exactly circular cross-section, at least over the entire length of the menipulating part, in order to make the insertion of the catheter into blood vessels and the manipulation thereof easy, and furthermore, to minimize the leakage of blood.
In this regard, the multi-hollow monofilament body should preferably have at least three continuously extending hollows, instead of two continuously extending hollows as illustrated in FIGs. 7A and 7B. It is easy to prepare a multi-hollow monofilament possessing an exactly circular cross-section in the case where the monofilament has three continuously extending hollows as illustrated in FlG. 7C, one hollow has X-ray impermeable material 5 inserted therein and another hollow forms a lumen 9 for infusion of a drug solution. The remaining hollow 10 is closed, i.e., heat-sealed, at both ends. Alternatively, this remaining hollow 10 may have X-ray impermeable material inserted therein or form a lumen for infusion of a drug solution.
It is also possible to provide four or more contimuously extending hollows in the multi-hollow monofilament body.
One modification of the self-guiding type catheter of FIGs. 7A and 7B, is illustrated in FIGs. 8A and 8B. The catheter 1' illustrated in FIGs. 8A and 8B is composed of a multi-hollow monofilament body having a substantially uniform diameter over the entire length thereof and two continuously extending hollows, one of the hollows having X-ray impermeable material inserted therein and the other forming a lumen 9 for infusion of a drug solution. This type catheter is poor in flexibility as compared with the 30 catheter illustrated in FIGs. 7A and 7B, and therefore, may be used in the case where the affected parts can be reached only through blood vessels having a large diameter and ` having no tortuous portions.
The thermoplastic synthetic resin used for the 35 preparation of the multi-hollow monofilament body of the catheter and the X-ray impermeable material to be inserted in the hollow of the monofilament body may be similar to :,.' .. . .
.
,~ :
326~
those mentioned hereinbefore with regard to the guide wire.
The size of the multi-lumene monofilament body of the catheter of the invention may also be similar to that of the guide wire mentioned hereinbefore, but is preferably somewhat larger than the guide wire. More specifically, the tip part preferably has a maximum diameter o~ ahout 0.5 - 3 mm, more preferably about 0.7 - 2 mm, and a length of about 0.5 - 5 mm, more preferably 0.7 - 4 mm. The flexible part preferably has a diameter of about 0.1 -0.5 mm, more preferably about 0.15 - 0.4 mm, and a length of about 10 - 100 mm, more preferably about 20 - 70 mm.
The tapering part preferably has a length of about 10 - 100 mm, morepreferably about 20 - 70 mm. The manipulating part preferably has a diameter of about 0.5 - 3 mm, more preferably 0.7 - 2 mm, and a length of at least about 20 cm, more preferably about 50 - 200 cm.
These sizes may be suitably varied depending upon, for example, the age and the physical condition of the pateient or the state of the parts for which a treatment is intended. It is preferable that the continuously extending hollows in the monofilament body have a large diameter.
The self-guiding type catheter of the invention may be manufactured as follows. A thermoplastic synthetic resin is melt-extruded through an annular orifice of a multi-hollow type spinneret equipped in an extruder to obtain an undrawn or slightly drawn continuous multi-hollow monofilament. The multi-hollow monofilament is cut into predetermined lengths. ~ portion o the entire length of each multi-hollow monofilament, which poirtion is adjacent to one end portion thereof, is drawn several times its original length, whereby a flexible part and a tapering part are simultaneously formed. X-ray impermeable material is inserted into at least one of the hollows in the undrawn or slightly drawn end portion of the monofilament, and then, its open end is heat-sealed to form the tip part.
X-ray impermeable material is also inserted into the hollow of the manipulating part from the end thereof opposite to .
., ~153Z6~
the tip part, and then, the open end is heat-sealed. In the case where a tungsten wire is used as the X-ray impermeable material, it is preferable that one end portion of the tungsten wire be tapered and inserted in the hollow of the manipulating part so that its tapered tip end is directed to the tip part of the catheter. Then, an outlet opening 7 (refer to FIG. 7A) is drilled through the wall of the tapering part by using a fine drill. The end portion of the monofilament body, which has an inlet opening 8 (FIG. 7A), may be provided with a cap or an adaptor to connect the catheter with an infusion pump. The multi-hollow monofilament body of the catheter may be surface-treated in manners similar to those herei~efore described with regard to the guide wire. Such a surface treatment enhances the self-lubricating property of the catheter, and thus, enables the minimization of thrombus deposition and makes the manipulation very easy.
The invention will now be illustrated by the following examples.
Example 1 Polyethylene terephthalate was melt-extruded in a conventional manner, by using an extruder provided with a spinneret having an annular orifice to obtain an undrawn hollow monofilament having an overall diameter of 0.7 mm and a hollow diameter of 0.35 mm. A tungsten piece of wire, 0.25 mm in diameter and 0.6 mm in length, was inserted in one end portion of the hollow monofilament, which portion had a length of 0.7 mm. Then, the open end was heat-sealed to form a tip part of a guide wire.
Thereafter, the portion adjacent to the tip part was drawn to form a flexible part 0.3 mm in diameter and 3 cm in length and a tapering part 0.3 - 0.7 mm in diameter and
.
3;~6'~t Furthermore, the synthetic resin monofilament has a smooth surface and therefore, thrombi are deposited thereon only to a slight extent.
The guide wire of the invention may be made of any melt-extrudable thermoplastic synthetic resins. The thermoplastic synthetic resins used include, for example, polyesters, such as polyethylene terephthalate and polybutylene terephthalate; polyamides, such as nylon-6, nylon-66, nylon-610, nylon-ll, nylon-12 and nylon-6/66;
polyolefins, such as polyethylene and polypropylene; and, fluorine-containing resins, such as copolymer of tetrafluoroethylene with hexafluoropropylene. These thermoplastic synthetic resins may be used either alone or in combination.
The most preferable thermoplastic synthetic resins are a polyblend comprised of, based on the total weight of the polyblend, (i) 70 to 99% by weight of at least one melt-extrudable thermoplastic synthetic resin selected from the above-mentioned polyesters, polyamides and p~lyolefins, and (ii) 1 to 30% by weight of a fluorine-containing thermoplastic resin, such as polytetrafluoroethylene and polyvinylidene fluoride. me optimum amount of the fluorine-containing thermoplastic resin in the polyblend is from 3 to 15% by weight. The guide wire made of the above-mentioned polyblend exhibits an enhanced self-lubricating property. Therefore, the undesirable deposition of thrombi can be substantially avoided and, in addition, the manipulation of the guide wire is very easy.
The guide wire made only o~ a melt-extrudable 30 fluorine-containing thermoplastic synthetic resin also exhibits an enhanced self-lubricating property.
The X-ray impermeable (or radio-opaque) material is inserted at least in the tip part and the manipulating part of the guide wire, so that the guide wire can be monitored 35 from the outside of the patient body during the introduction of the guide wire into blood vessels. The X-ray impermeable material used includes, for example metal .
~1~3Z64 wires, such as a tungsten wire, and liquid contrast media, such as "CONRAY" ttrade mark, 6n w/v%
methylglucamine iothalamete, supplied by, Mallinkrodt Inc.) and "UROGRAFIN" ~trade mark, methyl~lucamine and sodium diatrigoate, supplied by Schering A.G.). These X-ray impermeable materials may be used either alone or in combination. Of these, tungsten is preferable because of its high radio-opacity.
The X-ray impermeable mat~rial to be inscrtod in the hollow of the tip part 6 may be of any shape or form, such as a finely divided powder, a rod and a sphere. Its size may be, for example, about 0.2 mm in diàmeter for the spherical or powdered material, and about 0.2 mm in diameter and about 0.4-0.6 mm in length for the rod-shaped material. The X-ray impermeable material to be inserted in the hollow of the manipulating part 4 may preferably be continuously extending wire, such as a tungsten wire, for imparting proper toughness and rigidity to the manipulating part. This metal wire is usually inserted over the entire length of the manipulating part, and its diameter is preferably about 0.2-0.4 mm.
The medical vascular guide wire illustrated in FIG. 6 is similar to that of FIGs. lA and lB, but with an X-ray impermeable metal wire 5, one end portion 5' of which is tapered toward the flexible part 2. The metal wire 5 is inserted in the hollow of the tip part 6 and the hollow extending fran one end of the manipulating part 4 to a midway point of the tapering part 3. The tapered metal wire S exhibits an enhanced flexibility, as compared with the non-tapered metal wire illustrated in FIG. lA, and thus, the guide wire can be more unrestrictedly moved in blood vessels and more easily manipulated.
The hollow monofilament body of the guide wire of the invention can be surface-treated in order to enhance its self-lubricating property and, thus, to ccmpletely avoid the risk of thrombus deposition and to make the .~
. . .
.
3Z~4 manipulation of the gui~e wire easy. The surface treatment employed includes (i) a silicone treatment, (ii) a fluorine-containing resin coating treatment or (iii) a plasma spark discharge treatment. These surface treatments can be effected as follows.
(i) Silicon coating treatment A hollow monofilament body is passed several times through a bath of a solution of a medical silicone disolved in, for example, isoprop~nol, and then, the ~o coated monofilament body is dried under reduced pressure, thereby removing the solvent therefrom. Prior to the silicone coating treatment, the monofilament body may be surface-treated with sandpaper in order to facilitate the silicone coating treatment.
(ii) Fluorine-containing resin coating treatment A hollow monofilament body is treated with a solution of a fluorine-containing resin, such as "Te~lon 30 J" (trade mark, an aqucous suspension containing about 60 weight % of finely divided polytetrafluoroethylene having a particle size of about 0.3 micron, supplied by Mitsui Fluorochemical Co.) and "Teflon D-l" (trade mark, an aqueous suspension of finely divided polytetra-fluoroethylene, supplied by Daikin Kogyo K.K.). The treating procedure may be similar to that explained above with regard to the silicone coating treatment.
(iii) Plasma spark discharge treatment A hollow monofilament body is placed in a chamber which is maintained at a reduced pressure of below about 1 mmHg and into which a small amount of a gaseous oxganic fluorocompound is introduced. Then, a plasma spark discharge is effected, thereby introducing fluorine substituents into the polymer forming the surface of the monofilament.
The medical vascular guide wire of the invention may be manufactured as follows. A thermoplastic synthetic resin is melt-extruded through an annular orifice of a spinneret provided in an extruder, to obtain an undrawn or ' .
~3Z6~
g slightly drawn continuous hollow monofilament. The continuous hollow monofilament is cut into predetermined lengths. A portion of the entire length of each hollow monofilament, which portion is adjacent to one end portion thereof, is drawn several times its original length, whereby a relatively flexible part and a tapering part are simultaneously formed. X-ray impermeable material is inserted into the hollow of the undrawn or slightly drawn end portion thereof and, then, its open end is heat-sealed to form the tip part. X-ray impermeable material is also inserted into the continuously extending hollow of the manipulating part from the end thereof opposite to the tip part and, then, the open end is heat-sealed. When the guide wire illustrated in FIG. 6 is manufactured, an X-ray impermeable metal wire, one end portion of which is tapered, is inserted so that the tapered end reaches a midway point of the tapering part.
The guide wire of the invention can be inserted into peripheral blood vessels so that its tip part is advanced to the affected parts, by a conventional manipulation procedure. Then, a catheter may be inserted in the blood vessels so that the catheter advances along the inserted guide wire.
The self-guiding type catheter will now be illustrated with reference to FIGs. 7A through 8B.
Referring to FIGs. 7~ and 7B, the self-guiding type catheter l' is made of a multi-hollow monofilament body having two continuously extending hollows and comprised of a tip part 6, a relatively flexible part 2, a tapering part 3 and a manipulating part 4. X-ray impermeable material 5 is inserted in one of the continuously extending hollows at least in the tip part 6 and in the manipulating part 4, and both ends of the X-ray impermeable material inserted hollow are closed. The other continuously extending hollow 9 forms a lumen for permitting liquid and/or gas, such as a drug solution, to pass therethrough, which lumen is opened to the outside of the monofilament body through an . ' ' , " ` .
~32~4 inlet opening $ at one end of the lumen 9 and through an outlet opening 7 bored in the tapering part 3. The outlet opening 7 may be bored not in the tapering part 3 but in a portion of the manipulating part 4, adjacent to the tapering part 3. The structure and function of the tip part 6, the flexible part 2 and the tapering part 3 are similar to those of the guide wire explained with reference to FIGs. lA and 6. The outlet opening 7 bored in the tapering part 3 or in a portion, adjacent thereto, of the manipulating part 4 preferably has a sectional shape, shown in FIG. 7A, such that the section becomes broader toward the outside of the monofilament body so as to avoid the undesirable retentivity of a drug solution. The inlet opening 8 may be capped when the catheter is not used.
Furthermore, the end portion of the monofilament body, having the inlet opening 8, may preferably be of a structure such that a connector or an injector can be connected thereto.
The self-guiding type catheter having the structure mentioned above with reference to FIGs. 7A and 7B is characterized as being very pliable and easy to manipulate.
Thus, it is easy to manipulate the catheter, inserted by degrees in blood vessels, so that the tip part of the catheter reaches the intended parts through large diameter curved blood vessels and small peripheral blood vessels. A
drug solution may be introduced into the catheter through the inlet opening thereof after the tip part thereof reaches the intended parts and, as a result, the drug solution can be selectively administered to the intended parts. Thus, a medical treatment can be accomplished without taking a great deal of time, i.e., without repeated insertion and withdrawal of guide wires and catheters. In stead of the infusion of a drug solution, the self-guiding type catheter may be used for, for example, the withdrawal of blood and other specimens and the monitering of heart functions.
It is preferable that the multi-hollow monofilament .
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3Z6~
body of the catheter have an exactly circular cross-section, at least over the entire length of the menipulating part, in order to make the insertion of the catheter into blood vessels and the manipulation thereof easy, and furthermore, to minimize the leakage of blood.
In this regard, the multi-hollow monofilament body should preferably have at least three continuously extending hollows, instead of two continuously extending hollows as illustrated in FIGs. 7A and 7B. It is easy to prepare a multi-hollow monofilament possessing an exactly circular cross-section in the case where the monofilament has three continuously extending hollows as illustrated in FlG. 7C, one hollow has X-ray impermeable material 5 inserted therein and another hollow forms a lumen 9 for infusion of a drug solution. The remaining hollow 10 is closed, i.e., heat-sealed, at both ends. Alternatively, this remaining hollow 10 may have X-ray impermeable material inserted therein or form a lumen for infusion of a drug solution.
It is also possible to provide four or more contimuously extending hollows in the multi-hollow monofilament body.
One modification of the self-guiding type catheter of FIGs. 7A and 7B, is illustrated in FIGs. 8A and 8B. The catheter 1' illustrated in FIGs. 8A and 8B is composed of a multi-hollow monofilament body having a substantially uniform diameter over the entire length thereof and two continuously extending hollows, one of the hollows having X-ray impermeable material inserted therein and the other forming a lumen 9 for infusion of a drug solution. This type catheter is poor in flexibility as compared with the 30 catheter illustrated in FIGs. 7A and 7B, and therefore, may be used in the case where the affected parts can be reached only through blood vessels having a large diameter and ` having no tortuous portions.
The thermoplastic synthetic resin used for the 35 preparation of the multi-hollow monofilament body of the catheter and the X-ray impermeable material to be inserted in the hollow of the monofilament body may be similar to :,.' .. . .
.
,~ :
326~
those mentioned hereinbefore with regard to the guide wire.
The size of the multi-lumene monofilament body of the catheter of the invention may also be similar to that of the guide wire mentioned hereinbefore, but is preferably somewhat larger than the guide wire. More specifically, the tip part preferably has a maximum diameter o~ ahout 0.5 - 3 mm, more preferably about 0.7 - 2 mm, and a length of about 0.5 - 5 mm, more preferably 0.7 - 4 mm. The flexible part preferably has a diameter of about 0.1 -0.5 mm, more preferably about 0.15 - 0.4 mm, and a length of about 10 - 100 mm, more preferably about 20 - 70 mm.
The tapering part preferably has a length of about 10 - 100 mm, morepreferably about 20 - 70 mm. The manipulating part preferably has a diameter of about 0.5 - 3 mm, more preferably 0.7 - 2 mm, and a length of at least about 20 cm, more preferably about 50 - 200 cm.
These sizes may be suitably varied depending upon, for example, the age and the physical condition of the pateient or the state of the parts for which a treatment is intended. It is preferable that the continuously extending hollows in the monofilament body have a large diameter.
The self-guiding type catheter of the invention may be manufactured as follows. A thermoplastic synthetic resin is melt-extruded through an annular orifice of a multi-hollow type spinneret equipped in an extruder to obtain an undrawn or slightly drawn continuous multi-hollow monofilament. The multi-hollow monofilament is cut into predetermined lengths. ~ portion o the entire length of each multi-hollow monofilament, which poirtion is adjacent to one end portion thereof, is drawn several times its original length, whereby a flexible part and a tapering part are simultaneously formed. X-ray impermeable material is inserted into at least one of the hollows in the undrawn or slightly drawn end portion of the monofilament, and then, its open end is heat-sealed to form the tip part.
X-ray impermeable material is also inserted into the hollow of the manipulating part from the end thereof opposite to .
., ~153Z6~
the tip part, and then, the open end is heat-sealed. In the case where a tungsten wire is used as the X-ray impermeable material, it is preferable that one end portion of the tungsten wire be tapered and inserted in the hollow of the manipulating part so that its tapered tip end is directed to the tip part of the catheter. Then, an outlet opening 7 (refer to FIG. 7A) is drilled through the wall of the tapering part by using a fine drill. The end portion of the monofilament body, which has an inlet opening 8 (FIG. 7A), may be provided with a cap or an adaptor to connect the catheter with an infusion pump. The multi-hollow monofilament body of the catheter may be surface-treated in manners similar to those herei~efore described with regard to the guide wire. Such a surface treatment enhances the self-lubricating property of the catheter, and thus, enables the minimization of thrombus deposition and makes the manipulation very easy.
The invention will now be illustrated by the following examples.
Example 1 Polyethylene terephthalate was melt-extruded in a conventional manner, by using an extruder provided with a spinneret having an annular orifice to obtain an undrawn hollow monofilament having an overall diameter of 0.7 mm and a hollow diameter of 0.35 mm. A tungsten piece of wire, 0.25 mm in diameter and 0.6 mm in length, was inserted in one end portion of the hollow monofilament, which portion had a length of 0.7 mm. Then, the open end was heat-sealed to form a tip part of a guide wire.
Thereafter, the portion adjacent to the tip part was drawn to form a flexible part 0.3 mm in diameter and 3 cm in length and a tapering part 0.3 - 0.7 mm in diameter and
4 cm in length. A tungsten wire having a diameter of 0.3 mm was inserted into a manipulating part 0.7 mm in diameter and 1,500 mm in length, and then, its open end was heat-sealed to thereby obtain a monofilament guide wire.
The clinical applications of the monofilament guide - , ' ', ,' : ~
':
- ~ .
~3264 wire to blood vessels were indicated as follows.
(i) The tip part of the guide wire (F) was advanced through the abdominal aorta (a) into the left renal artery (b) (refer to FIG. 2).
(ii) The tip part of the guide wire (F) was advanced through the aortic arch (c) into the carotid artery (d) (refer to FIG. 3).
(iii) The tip part of the guide wire (F) was advanced from the abdominal aorta through the coeliac artery (e) into the hepatic artery (f) (refer to FlG. 4).
(iv) The tip part of the guide wire (F) was advanced through the femoral artery (g) into the abdominal aorta (a) (refer to FIG. 5).
In FIGs. 2 through 5, an arrow indicates the direction in which blood flows and "F" indicates the guide wire. In all cases of (i) through (iv), listed above, the guide wire could be easily manipulated and it did not injure the walls of blood vessels. On the contrary, conventional coiled metal guide wire was difficult to advance into the intended peripheral blood vessel branches.
Example 2 Polyethylene terephthalate was melt-extruded in a conventional manner by using an extruder provided with a spinneret having an annular orifice to obtain a hollow monofilament having an overall diameter of 0.8 mm and a hollow diameter of 0.33 mm. The monofilament was cut into lengths of 1.3 m. A portion of each monofilament, which portion was adjacent to one end portion of the monofilament, was drawn about three times its original length to simultameously form a flexible part 0.3 mm in diameter and 20 mm in length and a tapering part 30 cm in length. Then, a tungsten piece having a diameter of 0.3 mm and a length of 1.5 mm was inserted in the undrawn end portion, and then, its open end was heat-sealed, to thereby form an oval spherical tip part 0.8 mm in diameter and 2.5 mm in length. Thereafter, a tungsten wire having a tapered end portion and having a dia=eter oi 0.25 mm and a ' ' ~ '' ' ` ' ' ~5326~ .
Length of 1.25 m was inserted in the other undrawn portion from the open end thereof, so that the tapered tip of the tungsten wire reached a midway point of the tapcring part, and then, the open end was heat-sealed, whereby a synthetic resin monofilament guide wire was obtained.
The adaptation of the guide wire to the blood vessel contour was tested by carrying out procédures similar those listed in Example 1. Even when the tip part of the guide wire was advanced into the carotid artery (d) making an acute angle with the aortic arch (c) (refer to FIG. 3) or advanced through the tortuous femoral artery (g) into the abdominal aorta (a) (refer to FIG. S), the guide wire could be easily manipulated without injury to the patient.
Example 3 A hollow monofilament having an overall diameter of 0.8 mm and a hollow diameter of 0.33 mm was prepared, in a manner similar to that mentioned in Example 2, from a molten mixture comprised of 95 weight % of polyethylene terephthalate and 5 weight % of a polytetrafuoroethylene resin "TLP - 10" (trade mark, supplied by Mitsul Fluorochemical Co.). The monofilament was cut into lengths of 1.3 m. A portion of each monofilament, which portion was adjacent to one end portion of the monofilament, was drawn about three times its original length to simultaneously form a flexible part 0.3 mm in diameter and 50 mm in length and a tapering part 30 mm in length. Then, a tungsten piece 0.3 mm in diameter and 1.5 mm in length was inserted in the undrawn end portion, and then, its open end was hcat-sealed, to thereby form an oval spharical tip part 0.8 mm in diameter and 2.5 mm in length~ Therea~ter, a tungsten wire having a tapered end portion and having a diameter of 0.25 mm and a length of 1.25 m was inserted in the other undrawn portion from the open end thereof, so that the tapered tip of the tungsten wire reached a midway point of the tapering part, and then, the open end was heat-sealed, whereby a monofilament guide wire was obtained.
~. ~
~53264 The guide wire was used for a clinical examination wherein a catheter was advanced throu~h the abdo~inal aorta into the let renal artery. The ~uide wire could be easily manipulated for the tip to reach the intended parts. The insertion of a catheter was also easy because of the lubricating property of the guide wire. The guide wire, withdrawn from the blood vessel, could be easily cleaned by lightly wiping it and had little or no thrombus deposition Lll~r~n.
Example 4 A hollow polyethylene terephthalate monofilament having a diameter of 0.8 mm and a hollow diameter of 0.33 mm was prepared in a manner similar to that mentioned in Example 2. The continuous monofilament was cut into lengths of 1.3 m. One portion of each monofilament, which portion was adjucent to one end portion of the monofilament, was drawn about three times its original len~th, to thereby simultaneously form a flcxible part 0.3 mm in diameter and 50 mm in length and a tapering part 30 mm in length. Then, a tungsten piece 0.3 mm diameter and 1.5 mm in length was inserted in the undrawn end portion, and then, its open end was heat-sealed, to thereby form an oval spherical tip part 0.8 mm in diameter and 2.5 mm in length. Thereafter, a tungsten wire havin~ a tapered end portion and having a diameter of 0.25 mm and a length of 1.25 m was inserted into each monifilament from ; the end thereof opposite to the tip part, so that the tapered tip of the tungsten wire was directed toward the tip part and reached a midway point in the tapering part, and then, the open end was heat-sealed, to thereby obtain monofilament guide wires.
One portion of the guide wires was subjected to the followin~ surface treatment (l).
(l) Silicone coatin~ treatment ~ 35 ~ 2 wei~ht % solution of "rlDX4-4159" (trade mark, `~ room tmeperature drying type silicone lubricant, supplied ~ by Dow Corning Co.) in isopropanol was prepared. The guide .
wire was immersed in the silicone solution. After being withdrawn from the silicone solution the guide wire was wiped hy a gauge to remove the excessive amount of the silicone solution, and then, dried under reduced pressure.
The so treated guide wire is referred to as "guide wire A" for brevity.
The remaining portion of the guide wires was subjected to the following surface treatment (2).
(2) Fluorine-containing resin coating treatment The guide wire was immarsed in "Teflon 30 J"
(trade name, an aqueous suspension containing 60 weight %
of polytetrafluoroethylene having a particle size of about 0.3 micron, supplied by Mitsu Fluorochemical Co.). After being withdrawn from the suspension, the guide wire was dried under reduced pressure. The so treated guide wire is referred to as "guiding wire B" for ~revity.
The guide wires ~ and ~ were used in a clinical examination, wherein a catheter was advanced through the abdominal aorta into the left renal artery. Both gu de wires A and B could be easily manipulated for their tips to reach the intended parts. The insertion of the catheter and the withdrawal of the guide wire were also very easy.
These gulde wires, withdrawn fro~ the blood vessel, could be easily cleaned by lightly wiping them and had little or no thrombus deposition thereon.
Example 5 A hollow monofilament having a diameter of 0.8 mm and a hollow diameter of 0.33 mm was pxepared in a manner similar to that mentioned in Example 2, from a tetrafluoroethylene/hexafluoropropylene copolymer "Teflon"
FEP resin (supplied by Mitsu Fluorochemical Co.). The continuous monofilament was cut into lengths of 1.3 m. One portion of each monofilament, which portion was adjacent to one end portion of the monofilament, was drawn about three times its original length, to thereby simultaneously for~ a flexible part 0.3 mm in diameter and 25 ~m in length and a tapering part 30 mm in length. Then, a tungsten piece ~.i ~3Z6~
O.3 mm in diameter and 1.5 mm in length was inserted in the undrawn end portion, and then, its open end was heat-sealed, to thereby form an oval, spherical tip part 0.8 mm in diameter and 2.5 mm in length. Thereafter, a ~ungsten wire having a tapered end portion and having a diameter of 0.25 mm and a length of 1.25 m was inserted into the monofilament from the end thereof opposite to the tip part, so that the tapered tip of the tungsten wire was directed toward the tip part and reached a midway point in the tapering part, and then, the open end was heat-sealed, to thereby obtain a monofilament guide wire.
The guide wire was used in a clinical examination, wherein a catheter was advanced through the abdominal aorta into the left renal artery. The guide wire could be easily manipulated for its tip to reach the intended parts.
The insertion of the catheter and the withdrawal of the guide wire were also very easy. The guide wire withdrawn from the blood vessel had only a very slight amount of thrombus deposition therein.
Example 6 Polyethylene terephthalate was melt-extruded in a conventional manner by using an extruder provided with a spinneret having a special orifice, to thereby obtain a multi-hollow monofilament having an overall diameter of 1 mm and having two continuously extending hollows, each 0.33 mm in diameter. The multi-hollow monofilament was cut into lengths of 1 5 m. One portion o each monofilament, which portion was adjacent to one end portion ~about 1 mm in length) of the monofilament, was drawn about three times its original length, to thereby simultaneously form a flexible part 0.3 mm in diameter and 50 mm in length and a tapering part 30 mm in length. Then, two tungsten pieces, each 0.3 mm in diameter and 0.5 mm in length, ware inserted into the two hollows, respectively, in the undrawn end portion of about 1 mm in length, and then, the open ends were heat-sealed. Thereafter, a tungsten wire having a tapered end portion and having a diameter of 0.25 mm was ..
, ~53~64 inserted into one of the two hollows extending form the end of the manipulating part to the end of the tapering part, so that the tapered tip of the tungsten wire was directed to the tip part and reached a point in close proximity to the end of the tapering ~art, and then, the open end of the hollow in which the tungsten wire was inserted was heat-sealed. A small opening having a diameter of 0.25 mm was drilled in the wall of the tapering part of the other hollow, to thereby form a medicament outlet opening through which the other hollow was opened into the outside.
The so obtained self-guiding type catheter, having a structure similar to that illustrated in FIGs. 7A and 7B, was used in a clinical examination, wherein the catheter was advanced from the abdominal aorta through the coeliac artery into the hepatic artery. Both images of the tip part and the manipulating part were very clear and could be easily monitored. The catheter could be easily ~anipulated for the tip of the catheter to reach the affected parts, for example, in a liver. The catheterization caused no adverse reaction to the patient. An exactly determined amount of a drug could be selectively administered to the affected parts by using a precision metering pump connected to the inlet opening of the catheter. This medical treatment required only a period of time equal to approximately 1/3 of the time required for the conventional procedure wherein a guide wire and a catheter are used.
The catheter could be smoothly withdrawn rom the blood vessel. The withdrawn catheter could be easily cleaned by wiping it with gauze, and had little or no thrombus deposition thereon.
.
!
:
. .
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.
The clinical applications of the monofilament guide - , ' ', ,' : ~
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~3264 wire to blood vessels were indicated as follows.
(i) The tip part of the guide wire (F) was advanced through the abdominal aorta (a) into the left renal artery (b) (refer to FIG. 2).
(ii) The tip part of the guide wire (F) was advanced through the aortic arch (c) into the carotid artery (d) (refer to FIG. 3).
(iii) The tip part of the guide wire (F) was advanced from the abdominal aorta through the coeliac artery (e) into the hepatic artery (f) (refer to FlG. 4).
(iv) The tip part of the guide wire (F) was advanced through the femoral artery (g) into the abdominal aorta (a) (refer to FIG. 5).
In FIGs. 2 through 5, an arrow indicates the direction in which blood flows and "F" indicates the guide wire. In all cases of (i) through (iv), listed above, the guide wire could be easily manipulated and it did not injure the walls of blood vessels. On the contrary, conventional coiled metal guide wire was difficult to advance into the intended peripheral blood vessel branches.
Example 2 Polyethylene terephthalate was melt-extruded in a conventional manner by using an extruder provided with a spinneret having an annular orifice to obtain a hollow monofilament having an overall diameter of 0.8 mm and a hollow diameter of 0.33 mm. The monofilament was cut into lengths of 1.3 m. A portion of each monofilament, which portion was adjacent to one end portion of the monofilament, was drawn about three times its original length to simultameously form a flexible part 0.3 mm in diameter and 20 mm in length and a tapering part 30 cm in length. Then, a tungsten piece having a diameter of 0.3 mm and a length of 1.5 mm was inserted in the undrawn end portion, and then, its open end was heat-sealed, to thereby form an oval spherical tip part 0.8 mm in diameter and 2.5 mm in length. Thereafter, a tungsten wire having a tapered end portion and having a dia=eter oi 0.25 mm and a ' ' ~ '' ' ` ' ' ~5326~ .
Length of 1.25 m was inserted in the other undrawn portion from the open end thereof, so that the tapered tip of the tungsten wire reached a midway point of the tapcring part, and then, the open end was heat-sealed, whereby a synthetic resin monofilament guide wire was obtained.
The adaptation of the guide wire to the blood vessel contour was tested by carrying out procédures similar those listed in Example 1. Even when the tip part of the guide wire was advanced into the carotid artery (d) making an acute angle with the aortic arch (c) (refer to FIG. 3) or advanced through the tortuous femoral artery (g) into the abdominal aorta (a) (refer to FIG. S), the guide wire could be easily manipulated without injury to the patient.
Example 3 A hollow monofilament having an overall diameter of 0.8 mm and a hollow diameter of 0.33 mm was prepared, in a manner similar to that mentioned in Example 2, from a molten mixture comprised of 95 weight % of polyethylene terephthalate and 5 weight % of a polytetrafuoroethylene resin "TLP - 10" (trade mark, supplied by Mitsul Fluorochemical Co.). The monofilament was cut into lengths of 1.3 m. A portion of each monofilament, which portion was adjacent to one end portion of the monofilament, was drawn about three times its original length to simultaneously form a flexible part 0.3 mm in diameter and 50 mm in length and a tapering part 30 mm in length. Then, a tungsten piece 0.3 mm in diameter and 1.5 mm in length was inserted in the undrawn end portion, and then, its open end was hcat-sealed, to thereby form an oval spharical tip part 0.8 mm in diameter and 2.5 mm in length~ Therea~ter, a tungsten wire having a tapered end portion and having a diameter of 0.25 mm and a length of 1.25 m was inserted in the other undrawn portion from the open end thereof, so that the tapered tip of the tungsten wire reached a midway point of the tapering part, and then, the open end was heat-sealed, whereby a monofilament guide wire was obtained.
~. ~
~53264 The guide wire was used for a clinical examination wherein a catheter was advanced throu~h the abdo~inal aorta into the let renal artery. The ~uide wire could be easily manipulated for the tip to reach the intended parts. The insertion of a catheter was also easy because of the lubricating property of the guide wire. The guide wire, withdrawn from the blood vessel, could be easily cleaned by lightly wiping it and had little or no thrombus deposition Lll~r~n.
Example 4 A hollow polyethylene terephthalate monofilament having a diameter of 0.8 mm and a hollow diameter of 0.33 mm was prepared in a manner similar to that mentioned in Example 2. The continuous monofilament was cut into lengths of 1.3 m. One portion of each monofilament, which portion was adjucent to one end portion of the monofilament, was drawn about three times its original len~th, to thereby simultaneously form a flcxible part 0.3 mm in diameter and 50 mm in length and a tapering part 30 mm in length. Then, a tungsten piece 0.3 mm diameter and 1.5 mm in length was inserted in the undrawn end portion, and then, its open end was heat-sealed, to thereby form an oval spherical tip part 0.8 mm in diameter and 2.5 mm in length. Thereafter, a tungsten wire havin~ a tapered end portion and having a diameter of 0.25 mm and a length of 1.25 m was inserted into each monifilament from ; the end thereof opposite to the tip part, so that the tapered tip of the tungsten wire was directed toward the tip part and reached a midway point in the tapering part, and then, the open end was heat-sealed, to thereby obtain monofilament guide wires.
One portion of the guide wires was subjected to the followin~ surface treatment (l).
(l) Silicone coatin~ treatment ~ 35 ~ 2 wei~ht % solution of "rlDX4-4159" (trade mark, `~ room tmeperature drying type silicone lubricant, supplied ~ by Dow Corning Co.) in isopropanol was prepared. The guide .
wire was immersed in the silicone solution. After being withdrawn from the silicone solution the guide wire was wiped hy a gauge to remove the excessive amount of the silicone solution, and then, dried under reduced pressure.
The so treated guide wire is referred to as "guide wire A" for brevity.
The remaining portion of the guide wires was subjected to the following surface treatment (2).
(2) Fluorine-containing resin coating treatment The guide wire was immarsed in "Teflon 30 J"
(trade name, an aqueous suspension containing 60 weight %
of polytetrafluoroethylene having a particle size of about 0.3 micron, supplied by Mitsu Fluorochemical Co.). After being withdrawn from the suspension, the guide wire was dried under reduced pressure. The so treated guide wire is referred to as "guiding wire B" for ~revity.
The guide wires ~ and ~ were used in a clinical examination, wherein a catheter was advanced through the abdominal aorta into the left renal artery. Both gu de wires A and B could be easily manipulated for their tips to reach the intended parts. The insertion of the catheter and the withdrawal of the guide wire were also very easy.
These gulde wires, withdrawn fro~ the blood vessel, could be easily cleaned by lightly wiping them and had little or no thrombus deposition thereon.
Example 5 A hollow monofilament having a diameter of 0.8 mm and a hollow diameter of 0.33 mm was pxepared in a manner similar to that mentioned in Example 2, from a tetrafluoroethylene/hexafluoropropylene copolymer "Teflon"
FEP resin (supplied by Mitsu Fluorochemical Co.). The continuous monofilament was cut into lengths of 1.3 m. One portion of each monofilament, which portion was adjacent to one end portion of the monofilament, was drawn about three times its original length, to thereby simultaneously for~ a flexible part 0.3 mm in diameter and 25 ~m in length and a tapering part 30 mm in length. Then, a tungsten piece ~.i ~3Z6~
O.3 mm in diameter and 1.5 mm in length was inserted in the undrawn end portion, and then, its open end was heat-sealed, to thereby form an oval, spherical tip part 0.8 mm in diameter and 2.5 mm in length. Thereafter, a ~ungsten wire having a tapered end portion and having a diameter of 0.25 mm and a length of 1.25 m was inserted into the monofilament from the end thereof opposite to the tip part, so that the tapered tip of the tungsten wire was directed toward the tip part and reached a midway point in the tapering part, and then, the open end was heat-sealed, to thereby obtain a monofilament guide wire.
The guide wire was used in a clinical examination, wherein a catheter was advanced through the abdominal aorta into the left renal artery. The guide wire could be easily manipulated for its tip to reach the intended parts.
The insertion of the catheter and the withdrawal of the guide wire were also very easy. The guide wire withdrawn from the blood vessel had only a very slight amount of thrombus deposition therein.
Example 6 Polyethylene terephthalate was melt-extruded in a conventional manner by using an extruder provided with a spinneret having a special orifice, to thereby obtain a multi-hollow monofilament having an overall diameter of 1 mm and having two continuously extending hollows, each 0.33 mm in diameter. The multi-hollow monofilament was cut into lengths of 1 5 m. One portion o each monofilament, which portion was adjacent to one end portion ~about 1 mm in length) of the monofilament, was drawn about three times its original length, to thereby simultaneously form a flexible part 0.3 mm in diameter and 50 mm in length and a tapering part 30 mm in length. Then, two tungsten pieces, each 0.3 mm in diameter and 0.5 mm in length, ware inserted into the two hollows, respectively, in the undrawn end portion of about 1 mm in length, and then, the open ends were heat-sealed. Thereafter, a tungsten wire having a tapered end portion and having a diameter of 0.25 mm was ..
, ~53~64 inserted into one of the two hollows extending form the end of the manipulating part to the end of the tapering part, so that the tapered tip of the tungsten wire was directed to the tip part and reached a point in close proximity to the end of the tapering ~art, and then, the open end of the hollow in which the tungsten wire was inserted was heat-sealed. A small opening having a diameter of 0.25 mm was drilled in the wall of the tapering part of the other hollow, to thereby form a medicament outlet opening through which the other hollow was opened into the outside.
The so obtained self-guiding type catheter, having a structure similar to that illustrated in FIGs. 7A and 7B, was used in a clinical examination, wherein the catheter was advanced from the abdominal aorta through the coeliac artery into the hepatic artery. Both images of the tip part and the manipulating part were very clear and could be easily monitored. The catheter could be easily ~anipulated for the tip of the catheter to reach the affected parts, for example, in a liver. The catheterization caused no adverse reaction to the patient. An exactly determined amount of a drug could be selectively administered to the affected parts by using a precision metering pump connected to the inlet opening of the catheter. This medical treatment required only a period of time equal to approximately 1/3 of the time required for the conventional procedure wherein a guide wire and a catheter are used.
The catheter could be smoothly withdrawn rom the blood vessel. The withdrawn catheter could be easily cleaned by wiping it with gauze, and had little or no thrombus deposition thereon.
.
!
:
. .
.,.~. , ~ .
.
Claims (15)
1. A medical vascular guide wire comprising a wire body made of a synthetic resin single hollow monofilament and com-prised of a tip part, a relatively flexible part having a smaller diameter than the other parts, a tapering part and a manipulating part, these four parts continuously formed in a line, in that order, along the monofilament axis, and; at least the tip part and the manipulating part having X-ray impermeable material inserted in the respective hollow portions thereof.
2. A medical vascular guide wire according to claim 1, wherein an X-ray impermeable material inserted at least within the hollow portion in the manipulating part is in the form of a metal wire, one end portion of which is tapered and is in-serted in the hollow portion in a manner such that the tapered end of the metal wire is directed to the tip part of the wire body.
3. A medical vascular guide wire according to claim 1 or 2, wherein the hollow monofilament is made of at least one melt-extrudable thermoplastic synthetic resin selected from the group consisting of polyesters, polyamides and polyolefins.
4. A medical vascular guide wire according to claim 1 or 2, wherein the hollow monofilament is made of a poly-blend comprised of, based on the total weight of the poly-blend, (i) 70 to 90% by weight of at least one melt-extrudable thermoplastic synthetic resin selected from the group con-sisting of polyesters, polyamides and polyolefins and (ii) 1 to 30% by weight of a fluorine-containing thermoplastic resin.
5. A medical vascular guide wire according to claim 1 or 2, wherein the wire body has been surface-treated by a method selected from the group consisting of (i) a silicone coating treatment, (ii) a fluorine-containing resin coating treatment and (iii) a plasma spark discharge treatment effected in an atmosphere of a gaseous organic fluorine-containing compound.
6. A medical vascular guide wire according to claim 1 or 2, wherein the hollow monofilament is made of a melt-extrudable fluorine-containing thermoplastic resin.
7. A medical vascular guide wire according to claim 1 or 2, wherein the respective parts of the wire body have the dimensions:
tip part: maximum diameter is about 0.5-3mm.
and length is about 0.5-5mm.;
relatively flexible part: diameter is about 0.1-0.5mm.
and length is about 10-100mm.;
tapered part: length is about 10-100mm., and;
manipulating part: diameter is about 0.5-3mm.
and length is at least about 200mm.
tip part: maximum diameter is about 0.5-3mm.
and length is about 0.5-5mm.;
relatively flexible part: diameter is about 0.1-0.5mm.
and length is about 10-100mm.;
tapered part: length is about 10-100mm., and;
manipulating part: diameter is about 0.5-3mm.
and length is at least about 200mm.
8. A self-guiding type catheter comprising a continuously extending body made of a synthetic resin, multi-hollow single monofilament and comprised of a tip part, a relatively flexible part having a smaller diameter than the other parts, a tapering part and a manipulating part, these four parts continuously formed in a line, in that order, along the monofilament axis;
said body having at least two hollow channels extending from one end of the manipulating part at least to the point in close proximity of the tapering part, at least one of said hollow channels having an X-ray impermeable material inserted at least within the hollow portion in the manipulating part, and at least one of the other hollow channels forming a lumen for permitting fluid selected from a liquid and a gas to pass therethrough, which lumen is opened to the outside of the body through an inlet opening at a distal end of the lumen and through an outlet opening provided at a point adjacent to the other distal end of the lumen; and said body further having at least two hollow portions in the tip part, at least one of said hollow portions having an X-ray impermeable material inserted therein.
said body having at least two hollow channels extending from one end of the manipulating part at least to the point in close proximity of the tapering part, at least one of said hollow channels having an X-ray impermeable material inserted at least within the hollow portion in the manipulating part, and at least one of the other hollow channels forming a lumen for permitting fluid selected from a liquid and a gas to pass therethrough, which lumen is opened to the outside of the body through an inlet opening at a distal end of the lumen and through an outlet opening provided at a point adjacent to the other distal end of the lumen; and said body further having at least two hollow portions in the tip part, at least one of said hollow portions having an X-ray impermeable material inserted therein.
9. A self-guiding type catheter according to claim 8, wherein said X-ray impermeable material inserted at least within the hollow portion in the manipulating part is in the form of a metal wire, one end portion of which is tapered and inserted in the hollow portion in a manner such that the tapered end of the metal wire is directed toward the tip part of the wire body.
10. A self-guiding type catheter according to claim 8 or 9, wherein the multi-hollow monofilament is made of at least one melt-extrudable thermoplastic synthetic resin selected from the group consisting of polyesters, polyamides and polyolefins.
11. A self-guiding type catheter according to claim 8 or 9, wherein the multi-hollow monofilament is made of a poly-blend comprised of, based on the total weight of the polyblend, (i) 70 to 99% by weight of at least one melt-extrudable thermo-plastic synthetic resin selected from the group consisting of polyesters, polyamides and polyolefins and (ii) 1 to 30% by weight of a fluorine-containing thermoplastic resin.
12. A self-guiding type catheter according to claim 8 or 9, wherein the catheter body has been surface-treated by a method selected from the group consisting of (i) a silicone coating treatment, (ii) a fluorine-containing resin coating treatment, or (iii) a plasma spark discharge treatment effected in an atmosphere of a gaseous organic fluorine-containing com-pound.
13. A self-guiding type catheter according to claim 8 or 9, wherein the multi-hollow monofilament is made of a melt-extrudable fluorine-containing thermoplastic resin.
14. A self-guiding type catheter according to claim 8 or 9, wherein the respective parts of the body have the dimensions:
tip-part: maximum diameter is about 0.53mm. and length is about 0.5-5mm.;
relatively flexible part: diameter is about 0.1-0.5mm.
and length is about 10-100mm.; and manipulating part: diameter is about 0.7-3mm. and length is at least about 200mm.
tip-part: maximum diameter is about 0.53mm. and length is about 0.5-5mm.;
relatively flexible part: diameter is about 0.1-0.5mm.
and length is about 10-100mm.; and manipulating part: diameter is about 0.7-3mm. and length is at least about 200mm.
15. A medical vascular guide wire according to claim 1, wherein an X-ray impermeable material inserted in a hollow portion extending from said tapered part to said manipulating part is in the form of a metal wire, one end portion of which is tapered and is inserted in the hollow portion in a manner such that the tapered end of the metal wire is directed to the tip part of the wire body.
Applications Claiming Priority (10)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP12814/79 | 1979-02-08 | ||
| JP1281479A JPS55116358A (en) | 1979-02-08 | 1979-02-08 | Flow guide wire for medical treatment |
| JP137560/79 | 1979-10-26 | ||
| JP137561/79 | 1979-10-26 | ||
| JP137558/79 | 1979-10-26 | ||
| JP13756179A JPS5663367A (en) | 1979-10-26 | 1979-10-26 | Catheter type flow guide wire |
| JP13755979A JPS5663365A (en) | 1979-10-26 | 1979-10-26 | Antiithrombus medical flow guide wire |
| JP13755879A JPS5663364A (en) | 1979-10-26 | 1979-10-26 | Medical flow guide wire |
| JP13756079A JPS5663366A (en) | 1979-10-26 | 1979-10-26 | Antiithrombus medical flow guide wire |
| JP137559/79 | 1979-10-26 |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA1153264A true CA1153264A (en) | 1983-09-06 |
Family
ID=27519435
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA000344317A Expired CA1153264A (en) | 1979-02-08 | 1980-01-24 | Medical vascular guide wire and self-guiding type catheter |
Country Status (4)
| Country | Link |
|---|---|
| US (1) | US4345602A (en) |
| EP (1) | EP0014424B1 (en) |
| CA (1) | CA1153264A (en) |
| DE (1) | DE3061460D1 (en) |
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| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| DE94003C (en) * | ||||
| DK131266A (en) * | ||||
| FR440731A (en) * | 1912-02-28 | 1912-07-19 | Louis Marie Clement Charnaux | Probe or armed cannula for explorations and hygienic and medical applications |
| US2268321A (en) * | 1940-11-20 | 1941-12-30 | Wardlyn Corp | Catheter |
| DE855318C (en) * | 1942-08-14 | 1952-11-13 | Willy Ruesch | Surgical instrument, in particular catheter, and method for its manufacture |
| US2688329A (en) * | 1953-03-19 | 1954-09-07 | American Cystoscope Makers Inc | Catheter |
| US3189031A (en) * | 1963-11-04 | 1965-06-15 | Andersen Prod H W | Gastrointestinal sump tube |
| US3435826A (en) * | 1964-05-27 | 1969-04-01 | Edwards Lab Inc | Embolectomy catheter |
| SE325986B (en) * | 1965-07-05 | 1970-07-13 | T Almen | |
| US3687142A (en) * | 1970-10-06 | 1972-08-29 | Saul Leibinzohn | Catheter |
| US3789841A (en) * | 1971-09-15 | 1974-02-05 | Becton Dickinson Co | Disposable guide wire |
-
1980
- 1980-01-24 CA CA000344317A patent/CA1153264A/en not_active Expired
- 1980-01-29 US US06/116,600 patent/US4345602A/en not_active Expired - Lifetime
- 1980-01-29 DE DE8080100445T patent/DE3061460D1/en not_active Expired
- 1980-01-29 EP EP80100445A patent/EP0014424B1/en not_active Expired
Also Published As
| Publication number | Publication date |
|---|---|
| EP0014424B1 (en) | 1982-12-29 |
| DE3061460D1 (en) | 1983-02-03 |
| US4345602A (en) | 1982-08-24 |
| EP0014424A1 (en) | 1980-08-20 |
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