CA2032510C - A catheter with a balloon - Google Patents
A catheter with a balloonInfo
- Publication number
- CA2032510C CA2032510C CA002032510A CA2032510A CA2032510C CA 2032510 C CA2032510 C CA 2032510C CA 002032510 A CA002032510 A CA 002032510A CA 2032510 A CA2032510 A CA 2032510A CA 2032510 C CA2032510 C CA 2032510C
- Authority
- CA
- Canada
- Prior art keywords
- yarn
- catheter
- balloon
- elastic
- elastic yarn
- 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 - Lifetime
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
- A61M29/00—Dilators with or without means for introducing media, e.g. remedies
- A61M29/02—Dilators made of swellable material
-
- 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
- A61M25/10—Balloon catheters
- A61M25/1027—Making of balloon catheters
- A61M25/1029—Production methods of the balloon members, e.g. blow-moulding, extruding, deposition or by wrapping a plurality of layers of balloon material around a mandril
-
- 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
- A61M25/10—Balloon catheters
- A61M25/1027—Making of balloon catheters
-
- 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
- A61M25/10—Balloon catheters
- A61M25/1027—Making of balloon catheters
- A61M25/1034—Joining of shaft and balloon
-
- 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
- A61M25/10—Balloon catheters
- A61M2025/1043—Balloon catheters with special features or adapted for special applications
- A61M2025/1084—Balloon catheters with special features or adapted for special applications having features for increasing the shape stability, the reproducibility or for limiting expansion, e.g. containments, wrapped around fibres, yarns or strands
Abstract
The present invention relates to a catheter with a balloon characterized by a feature that the balloon is reinforced with a composite yarn consisting of an elastic yarn and a non-elastic yarn with a larger free length than that of said elastic yarn.
As the catheter with a balloon has a balloon with large stretchability, when the catheter is inserted into a blood vessel or taken out on a surginal operation, it is possible not only to make surely the diameter small without producing any wrinkle but to stretch surely to the same size and the same shape at any time. Therefore, not only reliability of the surginal operation is improved but also a cut wound for the surginal operation could be smaller. There exist such advantages that treatment and management after the surginal operation are simple and the time required for recovery is extremely short and smaller daily burdens of a patient and an attendant are needed.
As the catheter with a balloon has a balloon with large stretchability, when the catheter is inserted into a blood vessel or taken out on a surginal operation, it is possible not only to make surely the diameter small without producing any wrinkle but to stretch surely to the same size and the same shape at any time. Therefore, not only reliability of the surginal operation is improved but also a cut wound for the surginal operation could be smaller. There exist such advantages that treatment and management after the surginal operation are simple and the time required for recovery is extremely short and smaller daily burdens of a patient and an attendant are needed.
Description
2032sla A CATHETER WITH A BALLOON
Technical Field The present invention relates to a catheter with a balloon for expanding a constricted valve of the heart or a constricted or occluded blood vessel and normalizing thereby blood flow in medical treatment.
Background Technology As material for the balloon, thin membranes (films) of synthetic resins such as polyethylene, polyvinyl chloride or polyester, which have no stretchability but pressure resistance, have been used for preventing blood vessels from damage caused by an excessive expansion. It is not preferable that when these balloons are expanded, the surfaces thereof become slippery and cause the balloons to slip out or when they are deflated, wrinkles are produced which rub the inner walls of blood vessels, cause damages and accelerate formation of thrombi.
Therefore, it has been proposed, in order to improve the balloon, to prevent the formation of wrinkles when deflated by using a polyurethane or a silicone as a material for the balloon (Japanese Unexamined Patent Publication No. 91970/1984 and No. 103,453/1986) or by drawing the deflated balloon (Japanese Unexamined Patent Publication No. 125,386/1978), or to prevent an excessive expansion and to make the expansion uniform by incorporating a knitted fabric into a balloon.
In addition, Inoue proposed to use rubber as a - 2032~10balloon raw material and to form a guitar-shaped constricted part on the balloon by pinching the balloon with a knitted fabric having several stripes of bands for pinching a constricted valve of the heart so that the balloon does not slip out (Japanese Unexamined Patent Publication No. 23506/-1982).
However, when these balloons are used, the outer diameters became too large, and exposure and incision of a blood vessel is required when the balloon is inserted. This resulted in a longer time for recovery and patient's inconvenience after medical treatment.
On the other hand, it is proposed in Japanese Unexamined Patent Publication No. 103,453/1986 that a knitted fabric be put in a balloon. This re~uires a complicated work consisting of knitting a parallelly-twisted yarn of a polyimide yarn and a urethane yarn as a covering on the outer surface of a balloon expanded to a required expanded diameter. In addition, the diameter of the balloon can not be made small and the balloon can not be stretched in the longitudinal direction.
Disclosure of the Invention To solve these problems of the conventional technology, the present invention proposes as follows.
The present invention provides a catheter with a balloon reinforced with a composite fiber consisting of an elastic yarn and a non-elastic yarn, wherein the non-elastic yarn has a larger free length than the elastic yarn.
As the catheter with a balloon of the present invention exhibits larger balloon stretchability, it is possible to make the outer diameter smaller for a balloon with large expansion diameter used in a tearing and opening technique for a valve of the heart etc., and the catheter with the balloon can be inserted in a blood vessel by means of a simple Celludinga method. Therefore, the catheter of the invention has such advantages that incision for a surgical operation can be smaller; treatment and management after the surgical operation may be simple and the time required for recovery is extremely short; and the daily burdens on the patient and an attendant are thereby reduced.
In addition, when the catheter with a balloon of the present invention is pushed into a blood vessel and an inner heart to a diseased part, an inserting operation placing a guide wire and an expanded balloon in the blood flow can be easily performed and as the apex of the balloon is soft, there is substantially no possibility of damaging the inner wall of the blood vessel and the workability thereof is also good. Moreover, preparation of a cylindrical body made of the composite yarn and a cylindrical elastic film and the assembling thereof for manufacturing the balloon are easy and the yield is good. The cost can be lowered, too.
203~5~0 Brief Description of the Drawings An example of a structure of a catheter with a balloon of the present invention will be explained with reference to the accompanying drawings, in which:
Figure 1 is a schematic view of a catheter with a balloon according to one embodiment of the present invention, and Figure 2 is an enlarged schematic view illustrating an expanded state of the balloon part of the catheter shown in Figure 1.
In the Figures, reference number 1 indicates a tube part and reference number 2 indicates a balloon part.
Preferred Embodiments of the Present Invention As illustrated in Figure 1, the catheter includes a balloon 2 constituting a three-layered structure with a cylindrical body consisting of a cylindrical elastic film and a composite yarn attached on the apex of a tube 1 with a smooth surface and a round cross-section. On the rear end of the tube 1, if necessary, a fluid inlet and a take-up opening for an air removal tube placed in a fluid transferring path may be provided. In the catheter with a balloon of the present invention, the ratio of the free length of an elastic yarn to a non-elastic yarn is preferably 0.15-0.5 and more preferably 0.2-0.35. If this ratio is too large, the balloon is hardly sufficiently expanded, and if this ratio is too small, the reinforcing effect by means of the non-elastic r~ 76199--10 2032~10 yarn is reduced and breakage of the balloon, when expanded, easily occurs. However, if a careful consideration is paid for manufacturing the balloon tc avcid the breakage, even when the ratio is larger than the above-described value, the effect of the present invention can be accomplished.
The ratio of the free length can be determined by measuring a kink of the S-S curve of the composite yarn to the higher tension side. When the free length of the non-elastic yarn fluctuates and the kink is unclear, the ratio can be determined by extrapolating the straight lines before and behind the full length.
As the structure of the composite yarn, preferred is a core-sheath yarn in which the core is made of an elastic yarn and the sheath is made of a non-elastic yarn, because the core and sheath yarns are hardly separated. To make the composite yarns easily stretchable by an inner pressure or to preset the part order of stretching and the final stretched state, in sGme cases, the yarns may be stretched and shrunk in advance. In these cases, there is a possibility that separation of the constituting yarns negatively influences on the effect of the present invention.
For this reason, the above-mentioned core-sheath yarn is preferred.
For manufacturing the core-sheath yarn, preferred is a method in which twisting or entangling the elastic yarn by means of a fluid is performed while a non-elastic yarn is overfed. Especially preferred is a core-sheath yarn made by winding spirally a twisted yarn of a synthetic fiber on a urethane yarn, because such a yarn is compact. As the non-elastic yarn, a textured yarn is preferable because its stretchability, adhesiveness with an elastic film etc., are excellent. Among textured yarns, false-twisted textured yarns with excellent stretchability are preferable. When a non-textured yarn is used, the non-elastic yarn could possibly separate from an elastic yarn easily but this defect can be avoided by increasing the number of twists.
It is preferable that the balloon consists of a three-layered structure of an elastic film/a cylindrical body of a composite yarn/an elastic film. The inner elastic film provides a reinforcing effect caused by the composite yarn. The outer elastic film enables better passage through the blood vessel. The balloon based on the present invention can be applied to most catheters that employ a balloon. Furthermore, excellent effects can be expected when the balloon is applied to a catheter with a balloon wherein one end of the balloon is fixed on the inner tube (the inner tube may be an inner-filled rod) and the other end thereof is fixed on the outer tube of a double tube wherein both the inner and outer tubes can be concentrically slidable each other. Namely, in the catheter with a balloon, the outer diameter of the balloon can be furthermore decreased by sliding both tubes, thereby stretching the - 203251o balloon in the axial direction when it is inserted in a blood vessel and inside of the heart or taken out thereof.
If the rigidity of the inner tube is too small and will not stretch the balloon, the balloon can be effectively stretched in the axial direction by providing a stopper on the apex of the inner tube and pushing the stopper with a rod insertable in the inner tube. If the rigidity of the outer tube is insufficient, it is preferable that a high-modules fiber is fixed on the apex of the outer tube and is guided to the opposite end.
The elastic film may be made of a thin membrane with large stretchability and smooth surface in such a way that the thickness of the front end side is smaller than that of the rear end. As the raw material, polyurethanes and rubbers are used. Especially, rubbers having small initial moduli are excellent materials as raw materials for the elastic film.
The thickness of the elastic film is preferably in the rar,ge of 0.1-0.4 mm and it is not necessary that the inner and the outer layers have the same thickness.
Difference in thickness between the front end side and the rear end side is preferably about 5-20% and the difference can be created by making the front end side thinner, for example, when a cylindrical elastic film is prepared or by expanding a corresponding part of the prepared cylindrical elastic film and fixing the residual -elongation thereGf as a simple method.
As the cylindrical body made of the composite yarn, a knitted fabric, a woven fabric, a braid or a wound body in a cylindrical shape with a large twill angle can be used. Among them, a stretchable cylindrically-knitted structure is preferable.
When a guitar-shape balloon is prepared, for example, an elastic band is adhered on the middle part of an elastic body with an adhesive such as a rubber paste.
As the elastic yarn being a core yarn for a textured yarn, any stretchable fiber can be used without specific limitation. For example, a single yarn or a twisted yarn made of a rubber such as natural rubber and synthetic rubber or a polyurethane is suitable. As the yarn to be wound made of a synthetic fiber, not only high-tenacity nylon, polyester and "Teflon " yarns but high-tenacity polyimide and polyethylene yarns can be used as a single yarn, but a twisted flexible yarn is preferable.
The thickness of these yarns is not specifically limited as the required pressure-resistant characteristics may be different depending upon the position to be worked and the purpose, but in many cases, the thickness of the elastic yarn being a core yarn is in the range of 10-50D and that of the tenacity or high tenacity yarn to be wound is in the range of 30-150D.
Trade-mark A 76l99-lo Then, if the outer elastic film is adhered on a cylindrical body of a composite yarn and the inside of the cylindrical body of the composite yarn between an elastic film is coated with a silicone oil etc., a gap caused by expansion or shrinkage is not produced and a uniform expansion can be obtained. The length of the balloon can be freely set and in many cases, it is preferably in the range of 15-70 mm.
It is preferable that both ends and apexes of the balloon and the connected parts with tubes are finished with an adhesive to make their surfaces smooth.
As the raw material used for a soft inner tube in coaxially (concentrically)-assembled tubes, for example, polyvinyl chloride and polyurethane are preferably used.
The length of this tube is preferably 5-25 cm and it is preferable that the diameter is 14 Fr or smaller as it is inserted by means of Celludinga method.
In addition, as the relatively hard outer tube with torque characteristics, for example, a tube made of a synthetic resin such as polyethylene, "Teflon ", polypropylene and nylon is used. Besides these tubes, also preferable are for example, hard tubes such as a tube made by extracting a plasticizer for polyvinyl chloride with a solvent or a tube cured by crosslinking by means of irradiation. It is preferable that the diameter of this outer tube is 14 Fr Trade-mark _ g _ ~ 76199-10 or smaller because of the above-described reason. In addition, the length is not specifically defined as it is different depending on age and size of the patient and the distance from the inserted part to the position to be cured, but a product with a total length in the range of 50-200 cm is preferably used.
In addition, depending on the position to be cured, a relatively hard tube similar to the outer tube can be sometimes preferably substituted for the soft inner tube as the relatively hard tube provides an action making insertion of a rigid body easy.
Furthermore, if a contrast-medium such as barium sulfate, a bismuth compound or a metal powder such as tungsten is mixed in these tubes, it is preferable that the position in the blood vessel can be helpfully thereby detected by X-ray irradiation.
In addition, as the raw material of the yarn or the knitted fabric buried in or set along with the soft inner tube, a thin and strong one is preferable and for example, the yarns can be all used but polyamide yarns are the best among them.
In addition, it is necessary that an air removal tube set between an inner tube and an outer tube does not interfere with the flexibility of the soft tube and a tube with a thin thickness and a small diameter, for example a ~ 76199-10 203~
tube made of polyimide or "Teflon " or a polyethylene tube is used.
As a rigid body inserted in an inner tube and stretching a balloon, for example, a stainless pipe or thin rod can be used.
In addition, as a fluid expanding a balloon, for example, physiological saline, carbon dioxide or a contrast-medium is used. These fluids are used by a method wherein a specified amount thereof is injected thereinto by means of an injection cylinder etc.
The catheter with a balloon of the present invention has such features that the stretchability is large and it exhibits pressure resistance and a uniform expanding property by usina a cylindrical body made of a composite yarn with enlarged stretchability.
By the present invention, even a balloon with a large diameter can be inserted in a blood vessel in such a way that it is made long and slender and small and in addition, there is no possibility of damaging the inner wall of the blood vessel when the apex part of a tube rubs it and the balloon can be transferred to the position to be cured through the blood vessel and the heart by utilizing a guide wire and the floating property of the balloon.
Therefore, the time required for curing is short and management after surgical operation is simple and *
Trade-mark A 76199-lo -recovery can be rapidly performed. Furthermore, this method can be provided as a method wherein expansion of the occluded part of a blood vessel or an opening technique for a valve of the heart by means of a balloon can be non-operationally, simply and easily performed. In addition, the balloons of the present invention can be furthermore simply manufactured in such a way that products with various sizes are separately manufactured to provide catheter with balloons with good yield and with low cost.
(Examples) The present invention will be explained in more detail by using examples as follows.
Example 1.
A false-twisted textured yarn consisting of a polyester yarn (a non-elastic yarn) of 70D-24f was inter-twisted to a polyurethane yarn (an elastic yarn : "Opelon ") of 20D at a speed of 400 T/m while the former was overfed 300% to the urethane yarn to manufacture a composite yarn.
The ratio of free length of said yarn was 0.26 read from the S-S curve.
A balloon was prepared by using this composite yarn.
Namely, as an outer tube, a polyethylene tube containing a contrast-medium with 13.5 Fr and a length of 560 mm and a polyvinyl chloride tube containing 45 parts Trade-mark A 76l99-lo of DOP with 13.5 Fr and a length of 130 mm were connected through a stainless pipe with a diameter of 3.5 mm and a stainless pipe with a diameter of 3 mm and a length of 6 mm was attached on the apex of the polyvinyl chloride tube. In this time, a polyimide twisted yarn of 400D was placed on the hollow side of the polyvinyl chloride and fixed on stainless pipes on both sides. As an inner tube, 203~5~ n on the apex of a polyvinyl chloride tube containing 45 parts of DOP with 6.6 Fr, a stainless pipe with a diameter of 1.6 mm and a length of 7 mm having a projected part inside made by means of a corset was attached and a stainless pipe with 14G and a length of 70 mm and a needle base was inserted in the rear end. Connection of the inner and outer pipes and the inserted stainless pipe were bound and fixed with a nylon yarn with a thickness of 70 ~m. This inner tube was passed through a W-connector and furthermore inserted into the outer tube and then said outer tube was fixed on the W-connector to prepare a ~ube part.
Then, as an inner elastic film of the balloon, a rubber with a thickness of 0.25 mm and a length of 25 mm was bound and fixed on each apex of the inner tube and the outer tube with a nylon yarn with a thickness of 70 ~m and the surface thereof was coated with a small amount of a silicone oil. Separately, a cylindrically-knitted fabric was prepared by knitting said composite yarn by means of a knitting machine wherein 50 knitting needles were arranged on a circumference with a diameter of 20 mm. On the middle part of said knitted fabric with a length of 30 mm, a rubber with a thickness of 0.25 mm and a length of 7 mm was adhered with a rubber paste to prepare a band.
Furthermore on the outside thereof, a part prepared by ;~3~0 adhering a rubber tube with a thickness on the front side of 0.25 mm and a thickness on the rear side of 0.3 mm was covered. They were all fitted together in such a way that the total length was 25 mm and both ends thereof were bound and fixed with a nylon yarn with a thickness of 70 ~m. Then, excess knitted fabric and rubbers were cut off to complete a balloon part.
Then, after a polyimide tube with a diameter of 0.9 mm was inserted into a fluid transferring path between the inner and outer tubes from one of remaining openings of the W-connector up to 10 mm to the balloon, the rear part up to the inside of the W-connector was covered with a reinforcing polyethylene tube. After a two directional stopcock was fixed on the rear end thereof and the gaps of the openings were filled with an adhesive material, finally, the surfaces of the both ends of the balloon, the apex and the connected parts of tubes were finished smoothly with an epoxy resin to complete a catheter with a balloon of the present invention.
This catheter with a balloon was attached on an injection cylinder and after water was substituted for air while air was evacuated from an air vent, about 7 ml of water was injected therein. Only apex part of this balloon was expanded to about 23 mm. Then, when the injected amount was made to 23 ml, the balloon turned into - 20~5~0 a cylindrical shape with a diameter of about 28 mm.
Then, water was pulled out and the surface was smoothly shrunk without producing wrinkles. Then, a stainless steel tube with a diameter of 1.19 mm was inserted into the inner tube to push the apex part of the inner tube and to stretch thereby the balloon from 25 mm to 55 mm. The diameter of the balloon was changed thereby from about 7 mm to 4.5 mm. When the stainless tube was pulled backward, the balloon was returned to its original diameter and length.
Example 2.
A catheter with a balloon similar to the one of Example 1 was used for a clinical treatment for an inter-related tearing and opening technique for the mitral valve. Namely, using a method perforating the atrium partition, a specially-made guide wire was inserted into the left atrium through the s~in, the crotch vein, the right atrium and the atrium partition. Then, a dilator of 14 Fr was forwarded along with this guide and the perforated parts on the crotch vein and the atrium partition were expanded. A catheter with a balloon of the present invention was successively inserted into the left atrium from the right atrium through the atrium partition and only the apex of the balloon was expanded to a diameter of 10 mm by using carbon dioxide and it was run 2032~
into a valve opening with the blood flow as a Swanganz catheter was. Then, it was inserted into the left ventricle and the apex side of the balloon was furthermore expanded by using a contrast-medium and it was lightly drawn nearby and brought into contact with the valve opening to be teared and opened. At this position, the balloon was furthermore expanded and the valve opening was pinched with the constricted balloon. The balloon was expanded as they were under this condition and the valve opening can be enlarged without slipping out of the balloon.
The tearing and opening techni~ue needed 1 hour containing 5 sec for expansion and shrinkage of the balloon without any side effect. 3 days were needed from entering a hospital to leaving the hospital. The time needed was only less than a half in comparison with a tearing and opening techni~ue accompanied with exposure and cutting-out of the blood vessel.
Example 3.
A catheter with a balloon was prepared in the same way as in Example 1, but the denier of "Opelon" yarn as the elastic yarn was 30D and the ratio of overfeeding a polyester yarn and the number of twist thereof were changed to 270% and 400 T/m respectively.
In this catheter with a balloon, the ratio of free ;~03251~
length of the constituting yarns of the composite yarn was apparently 0.28 and the balloon exhibited the maximum expanded diameter of 30 mm and the minimum shrunk diameter of 4-5 mm and excellent stretching characteristics without generation of wrinkle.
Possibility of Industrial Application The catheter with a balloon of the present invention can be widely used for a method for medical treatment wherein a shrunk balloon is got into a constricted or occluded blood vessel and a fluid is pressed into the balloon to expand the balloon and the expanded balloon enlarges the constricted or the occluded blood vessel to make the constricted or occluded part normal. Especially, it can be widely used for a non-surgical and through-skin type valve tearing and opening operation substituting for a valve incisive operation for the valve of the heart which is constricted by aging, calcination or a se~uela of rheumatic heat and a valve substitutive operation for an artificial valve.
Technical Field The present invention relates to a catheter with a balloon for expanding a constricted valve of the heart or a constricted or occluded blood vessel and normalizing thereby blood flow in medical treatment.
Background Technology As material for the balloon, thin membranes (films) of synthetic resins such as polyethylene, polyvinyl chloride or polyester, which have no stretchability but pressure resistance, have been used for preventing blood vessels from damage caused by an excessive expansion. It is not preferable that when these balloons are expanded, the surfaces thereof become slippery and cause the balloons to slip out or when they are deflated, wrinkles are produced which rub the inner walls of blood vessels, cause damages and accelerate formation of thrombi.
Therefore, it has been proposed, in order to improve the balloon, to prevent the formation of wrinkles when deflated by using a polyurethane or a silicone as a material for the balloon (Japanese Unexamined Patent Publication No. 91970/1984 and No. 103,453/1986) or by drawing the deflated balloon (Japanese Unexamined Patent Publication No. 125,386/1978), or to prevent an excessive expansion and to make the expansion uniform by incorporating a knitted fabric into a balloon.
In addition, Inoue proposed to use rubber as a - 2032~10balloon raw material and to form a guitar-shaped constricted part on the balloon by pinching the balloon with a knitted fabric having several stripes of bands for pinching a constricted valve of the heart so that the balloon does not slip out (Japanese Unexamined Patent Publication No. 23506/-1982).
However, when these balloons are used, the outer diameters became too large, and exposure and incision of a blood vessel is required when the balloon is inserted. This resulted in a longer time for recovery and patient's inconvenience after medical treatment.
On the other hand, it is proposed in Japanese Unexamined Patent Publication No. 103,453/1986 that a knitted fabric be put in a balloon. This re~uires a complicated work consisting of knitting a parallelly-twisted yarn of a polyimide yarn and a urethane yarn as a covering on the outer surface of a balloon expanded to a required expanded diameter. In addition, the diameter of the balloon can not be made small and the balloon can not be stretched in the longitudinal direction.
Disclosure of the Invention To solve these problems of the conventional technology, the present invention proposes as follows.
The present invention provides a catheter with a balloon reinforced with a composite fiber consisting of an elastic yarn and a non-elastic yarn, wherein the non-elastic yarn has a larger free length than the elastic yarn.
As the catheter with a balloon of the present invention exhibits larger balloon stretchability, it is possible to make the outer diameter smaller for a balloon with large expansion diameter used in a tearing and opening technique for a valve of the heart etc., and the catheter with the balloon can be inserted in a blood vessel by means of a simple Celludinga method. Therefore, the catheter of the invention has such advantages that incision for a surgical operation can be smaller; treatment and management after the surgical operation may be simple and the time required for recovery is extremely short; and the daily burdens on the patient and an attendant are thereby reduced.
In addition, when the catheter with a balloon of the present invention is pushed into a blood vessel and an inner heart to a diseased part, an inserting operation placing a guide wire and an expanded balloon in the blood flow can be easily performed and as the apex of the balloon is soft, there is substantially no possibility of damaging the inner wall of the blood vessel and the workability thereof is also good. Moreover, preparation of a cylindrical body made of the composite yarn and a cylindrical elastic film and the assembling thereof for manufacturing the balloon are easy and the yield is good. The cost can be lowered, too.
203~5~0 Brief Description of the Drawings An example of a structure of a catheter with a balloon of the present invention will be explained with reference to the accompanying drawings, in which:
Figure 1 is a schematic view of a catheter with a balloon according to one embodiment of the present invention, and Figure 2 is an enlarged schematic view illustrating an expanded state of the balloon part of the catheter shown in Figure 1.
In the Figures, reference number 1 indicates a tube part and reference number 2 indicates a balloon part.
Preferred Embodiments of the Present Invention As illustrated in Figure 1, the catheter includes a balloon 2 constituting a three-layered structure with a cylindrical body consisting of a cylindrical elastic film and a composite yarn attached on the apex of a tube 1 with a smooth surface and a round cross-section. On the rear end of the tube 1, if necessary, a fluid inlet and a take-up opening for an air removal tube placed in a fluid transferring path may be provided. In the catheter with a balloon of the present invention, the ratio of the free length of an elastic yarn to a non-elastic yarn is preferably 0.15-0.5 and more preferably 0.2-0.35. If this ratio is too large, the balloon is hardly sufficiently expanded, and if this ratio is too small, the reinforcing effect by means of the non-elastic r~ 76199--10 2032~10 yarn is reduced and breakage of the balloon, when expanded, easily occurs. However, if a careful consideration is paid for manufacturing the balloon tc avcid the breakage, even when the ratio is larger than the above-described value, the effect of the present invention can be accomplished.
The ratio of the free length can be determined by measuring a kink of the S-S curve of the composite yarn to the higher tension side. When the free length of the non-elastic yarn fluctuates and the kink is unclear, the ratio can be determined by extrapolating the straight lines before and behind the full length.
As the structure of the composite yarn, preferred is a core-sheath yarn in which the core is made of an elastic yarn and the sheath is made of a non-elastic yarn, because the core and sheath yarns are hardly separated. To make the composite yarns easily stretchable by an inner pressure or to preset the part order of stretching and the final stretched state, in sGme cases, the yarns may be stretched and shrunk in advance. In these cases, there is a possibility that separation of the constituting yarns negatively influences on the effect of the present invention.
For this reason, the above-mentioned core-sheath yarn is preferred.
For manufacturing the core-sheath yarn, preferred is a method in which twisting or entangling the elastic yarn by means of a fluid is performed while a non-elastic yarn is overfed. Especially preferred is a core-sheath yarn made by winding spirally a twisted yarn of a synthetic fiber on a urethane yarn, because such a yarn is compact. As the non-elastic yarn, a textured yarn is preferable because its stretchability, adhesiveness with an elastic film etc., are excellent. Among textured yarns, false-twisted textured yarns with excellent stretchability are preferable. When a non-textured yarn is used, the non-elastic yarn could possibly separate from an elastic yarn easily but this defect can be avoided by increasing the number of twists.
It is preferable that the balloon consists of a three-layered structure of an elastic film/a cylindrical body of a composite yarn/an elastic film. The inner elastic film provides a reinforcing effect caused by the composite yarn. The outer elastic film enables better passage through the blood vessel. The balloon based on the present invention can be applied to most catheters that employ a balloon. Furthermore, excellent effects can be expected when the balloon is applied to a catheter with a balloon wherein one end of the balloon is fixed on the inner tube (the inner tube may be an inner-filled rod) and the other end thereof is fixed on the outer tube of a double tube wherein both the inner and outer tubes can be concentrically slidable each other. Namely, in the catheter with a balloon, the outer diameter of the balloon can be furthermore decreased by sliding both tubes, thereby stretching the - 203251o balloon in the axial direction when it is inserted in a blood vessel and inside of the heart or taken out thereof.
If the rigidity of the inner tube is too small and will not stretch the balloon, the balloon can be effectively stretched in the axial direction by providing a stopper on the apex of the inner tube and pushing the stopper with a rod insertable in the inner tube. If the rigidity of the outer tube is insufficient, it is preferable that a high-modules fiber is fixed on the apex of the outer tube and is guided to the opposite end.
The elastic film may be made of a thin membrane with large stretchability and smooth surface in such a way that the thickness of the front end side is smaller than that of the rear end. As the raw material, polyurethanes and rubbers are used. Especially, rubbers having small initial moduli are excellent materials as raw materials for the elastic film.
The thickness of the elastic film is preferably in the rar,ge of 0.1-0.4 mm and it is not necessary that the inner and the outer layers have the same thickness.
Difference in thickness between the front end side and the rear end side is preferably about 5-20% and the difference can be created by making the front end side thinner, for example, when a cylindrical elastic film is prepared or by expanding a corresponding part of the prepared cylindrical elastic film and fixing the residual -elongation thereGf as a simple method.
As the cylindrical body made of the composite yarn, a knitted fabric, a woven fabric, a braid or a wound body in a cylindrical shape with a large twill angle can be used. Among them, a stretchable cylindrically-knitted structure is preferable.
When a guitar-shape balloon is prepared, for example, an elastic band is adhered on the middle part of an elastic body with an adhesive such as a rubber paste.
As the elastic yarn being a core yarn for a textured yarn, any stretchable fiber can be used without specific limitation. For example, a single yarn or a twisted yarn made of a rubber such as natural rubber and synthetic rubber or a polyurethane is suitable. As the yarn to be wound made of a synthetic fiber, not only high-tenacity nylon, polyester and "Teflon " yarns but high-tenacity polyimide and polyethylene yarns can be used as a single yarn, but a twisted flexible yarn is preferable.
The thickness of these yarns is not specifically limited as the required pressure-resistant characteristics may be different depending upon the position to be worked and the purpose, but in many cases, the thickness of the elastic yarn being a core yarn is in the range of 10-50D and that of the tenacity or high tenacity yarn to be wound is in the range of 30-150D.
Trade-mark A 76l99-lo Then, if the outer elastic film is adhered on a cylindrical body of a composite yarn and the inside of the cylindrical body of the composite yarn between an elastic film is coated with a silicone oil etc., a gap caused by expansion or shrinkage is not produced and a uniform expansion can be obtained. The length of the balloon can be freely set and in many cases, it is preferably in the range of 15-70 mm.
It is preferable that both ends and apexes of the balloon and the connected parts with tubes are finished with an adhesive to make their surfaces smooth.
As the raw material used for a soft inner tube in coaxially (concentrically)-assembled tubes, for example, polyvinyl chloride and polyurethane are preferably used.
The length of this tube is preferably 5-25 cm and it is preferable that the diameter is 14 Fr or smaller as it is inserted by means of Celludinga method.
In addition, as the relatively hard outer tube with torque characteristics, for example, a tube made of a synthetic resin such as polyethylene, "Teflon ", polypropylene and nylon is used. Besides these tubes, also preferable are for example, hard tubes such as a tube made by extracting a plasticizer for polyvinyl chloride with a solvent or a tube cured by crosslinking by means of irradiation. It is preferable that the diameter of this outer tube is 14 Fr Trade-mark _ g _ ~ 76199-10 or smaller because of the above-described reason. In addition, the length is not specifically defined as it is different depending on age and size of the patient and the distance from the inserted part to the position to be cured, but a product with a total length in the range of 50-200 cm is preferably used.
In addition, depending on the position to be cured, a relatively hard tube similar to the outer tube can be sometimes preferably substituted for the soft inner tube as the relatively hard tube provides an action making insertion of a rigid body easy.
Furthermore, if a contrast-medium such as barium sulfate, a bismuth compound or a metal powder such as tungsten is mixed in these tubes, it is preferable that the position in the blood vessel can be helpfully thereby detected by X-ray irradiation.
In addition, as the raw material of the yarn or the knitted fabric buried in or set along with the soft inner tube, a thin and strong one is preferable and for example, the yarns can be all used but polyamide yarns are the best among them.
In addition, it is necessary that an air removal tube set between an inner tube and an outer tube does not interfere with the flexibility of the soft tube and a tube with a thin thickness and a small diameter, for example a ~ 76199-10 203~
tube made of polyimide or "Teflon " or a polyethylene tube is used.
As a rigid body inserted in an inner tube and stretching a balloon, for example, a stainless pipe or thin rod can be used.
In addition, as a fluid expanding a balloon, for example, physiological saline, carbon dioxide or a contrast-medium is used. These fluids are used by a method wherein a specified amount thereof is injected thereinto by means of an injection cylinder etc.
The catheter with a balloon of the present invention has such features that the stretchability is large and it exhibits pressure resistance and a uniform expanding property by usina a cylindrical body made of a composite yarn with enlarged stretchability.
By the present invention, even a balloon with a large diameter can be inserted in a blood vessel in such a way that it is made long and slender and small and in addition, there is no possibility of damaging the inner wall of the blood vessel when the apex part of a tube rubs it and the balloon can be transferred to the position to be cured through the blood vessel and the heart by utilizing a guide wire and the floating property of the balloon.
Therefore, the time required for curing is short and management after surgical operation is simple and *
Trade-mark A 76199-lo -recovery can be rapidly performed. Furthermore, this method can be provided as a method wherein expansion of the occluded part of a blood vessel or an opening technique for a valve of the heart by means of a balloon can be non-operationally, simply and easily performed. In addition, the balloons of the present invention can be furthermore simply manufactured in such a way that products with various sizes are separately manufactured to provide catheter with balloons with good yield and with low cost.
(Examples) The present invention will be explained in more detail by using examples as follows.
Example 1.
A false-twisted textured yarn consisting of a polyester yarn (a non-elastic yarn) of 70D-24f was inter-twisted to a polyurethane yarn (an elastic yarn : "Opelon ") of 20D at a speed of 400 T/m while the former was overfed 300% to the urethane yarn to manufacture a composite yarn.
The ratio of free length of said yarn was 0.26 read from the S-S curve.
A balloon was prepared by using this composite yarn.
Namely, as an outer tube, a polyethylene tube containing a contrast-medium with 13.5 Fr and a length of 560 mm and a polyvinyl chloride tube containing 45 parts Trade-mark A 76l99-lo of DOP with 13.5 Fr and a length of 130 mm were connected through a stainless pipe with a diameter of 3.5 mm and a stainless pipe with a diameter of 3 mm and a length of 6 mm was attached on the apex of the polyvinyl chloride tube. In this time, a polyimide twisted yarn of 400D was placed on the hollow side of the polyvinyl chloride and fixed on stainless pipes on both sides. As an inner tube, 203~5~ n on the apex of a polyvinyl chloride tube containing 45 parts of DOP with 6.6 Fr, a stainless pipe with a diameter of 1.6 mm and a length of 7 mm having a projected part inside made by means of a corset was attached and a stainless pipe with 14G and a length of 70 mm and a needle base was inserted in the rear end. Connection of the inner and outer pipes and the inserted stainless pipe were bound and fixed with a nylon yarn with a thickness of 70 ~m. This inner tube was passed through a W-connector and furthermore inserted into the outer tube and then said outer tube was fixed on the W-connector to prepare a ~ube part.
Then, as an inner elastic film of the balloon, a rubber with a thickness of 0.25 mm and a length of 25 mm was bound and fixed on each apex of the inner tube and the outer tube with a nylon yarn with a thickness of 70 ~m and the surface thereof was coated with a small amount of a silicone oil. Separately, a cylindrically-knitted fabric was prepared by knitting said composite yarn by means of a knitting machine wherein 50 knitting needles were arranged on a circumference with a diameter of 20 mm. On the middle part of said knitted fabric with a length of 30 mm, a rubber with a thickness of 0.25 mm and a length of 7 mm was adhered with a rubber paste to prepare a band.
Furthermore on the outside thereof, a part prepared by ;~3~0 adhering a rubber tube with a thickness on the front side of 0.25 mm and a thickness on the rear side of 0.3 mm was covered. They were all fitted together in such a way that the total length was 25 mm and both ends thereof were bound and fixed with a nylon yarn with a thickness of 70 ~m. Then, excess knitted fabric and rubbers were cut off to complete a balloon part.
Then, after a polyimide tube with a diameter of 0.9 mm was inserted into a fluid transferring path between the inner and outer tubes from one of remaining openings of the W-connector up to 10 mm to the balloon, the rear part up to the inside of the W-connector was covered with a reinforcing polyethylene tube. After a two directional stopcock was fixed on the rear end thereof and the gaps of the openings were filled with an adhesive material, finally, the surfaces of the both ends of the balloon, the apex and the connected parts of tubes were finished smoothly with an epoxy resin to complete a catheter with a balloon of the present invention.
This catheter with a balloon was attached on an injection cylinder and after water was substituted for air while air was evacuated from an air vent, about 7 ml of water was injected therein. Only apex part of this balloon was expanded to about 23 mm. Then, when the injected amount was made to 23 ml, the balloon turned into - 20~5~0 a cylindrical shape with a diameter of about 28 mm.
Then, water was pulled out and the surface was smoothly shrunk without producing wrinkles. Then, a stainless steel tube with a diameter of 1.19 mm was inserted into the inner tube to push the apex part of the inner tube and to stretch thereby the balloon from 25 mm to 55 mm. The diameter of the balloon was changed thereby from about 7 mm to 4.5 mm. When the stainless tube was pulled backward, the balloon was returned to its original diameter and length.
Example 2.
A catheter with a balloon similar to the one of Example 1 was used for a clinical treatment for an inter-related tearing and opening technique for the mitral valve. Namely, using a method perforating the atrium partition, a specially-made guide wire was inserted into the left atrium through the s~in, the crotch vein, the right atrium and the atrium partition. Then, a dilator of 14 Fr was forwarded along with this guide and the perforated parts on the crotch vein and the atrium partition were expanded. A catheter with a balloon of the present invention was successively inserted into the left atrium from the right atrium through the atrium partition and only the apex of the balloon was expanded to a diameter of 10 mm by using carbon dioxide and it was run 2032~
into a valve opening with the blood flow as a Swanganz catheter was. Then, it was inserted into the left ventricle and the apex side of the balloon was furthermore expanded by using a contrast-medium and it was lightly drawn nearby and brought into contact with the valve opening to be teared and opened. At this position, the balloon was furthermore expanded and the valve opening was pinched with the constricted balloon. The balloon was expanded as they were under this condition and the valve opening can be enlarged without slipping out of the balloon.
The tearing and opening techni~ue needed 1 hour containing 5 sec for expansion and shrinkage of the balloon without any side effect. 3 days were needed from entering a hospital to leaving the hospital. The time needed was only less than a half in comparison with a tearing and opening techni~ue accompanied with exposure and cutting-out of the blood vessel.
Example 3.
A catheter with a balloon was prepared in the same way as in Example 1, but the denier of "Opelon" yarn as the elastic yarn was 30D and the ratio of overfeeding a polyester yarn and the number of twist thereof were changed to 270% and 400 T/m respectively.
In this catheter with a balloon, the ratio of free ;~03251~
length of the constituting yarns of the composite yarn was apparently 0.28 and the balloon exhibited the maximum expanded diameter of 30 mm and the minimum shrunk diameter of 4-5 mm and excellent stretching characteristics without generation of wrinkle.
Possibility of Industrial Application The catheter with a balloon of the present invention can be widely used for a method for medical treatment wherein a shrunk balloon is got into a constricted or occluded blood vessel and a fluid is pressed into the balloon to expand the balloon and the expanded balloon enlarges the constricted or the occluded blood vessel to make the constricted or occluded part normal. Especially, it can be widely used for a non-surgical and through-skin type valve tearing and opening operation substituting for a valve incisive operation for the valve of the heart which is constricted by aging, calcination or a se~uela of rheumatic heat and a valve substitutive operation for an artificial valve.
Claims (17)
PROPERTY OR PRIVILEGE IS CLAIMED ARE DEFINED AS FOLLOWS:
1. A catheter having a balloon reinforced with a composite yarn consisting of an elastic yarn and a non-elastic yarn, wherein the ratio of free length of the elastic yarn to the non-elastic yarn is of 0.15-0.5.
2. A catheter as described in claim 1, wherein the ratio of free length of the elastic yarn to the non-elastic yarn is of 0.2-0.35.
3. A catheter as described in claim 1, wherein the composite yarn is a core-sheath yarn composed of a core of the elastic yarn and a sheath of the non-elastic yarn.
4. A catheter as described in claim 3, wherein the core-sheath yarn is formed of a urethane yarn as the elastic yarn and a synthetic fiber-twisted yarn as the non-elastic yarn spirally wound on the urethane yarn.
5. A catheter as described in claim 1, wherein the non-elastic yarn is false-twisted textured yarn.
6. A catheter as described in any one of claims 1 to 5, wherein the composite yarn is in a knitted or woven fabric form.
7. A catheter as described in claim 6, wherein the composite yarn is in a knitted fabric form.
8. A catheter as described in any one of claims 1 to 5, wherein the balloon has a three-layered structure consisting of an elastic film/a cylindrical fabric of the composite yarn/an elastic film.
9. A catheter as described in claim 8, wherein the cylindrical fabric of the composite yarn is adhered with one or both of the elastic films.
10. A catheter as described in any one of claims 1 to 5, wherein one end of the balloon is fixed to an inner tube of a double tube in which the tubes are concentrically slidable each other and the other end of the balloon is fixed to an outer tube.
11. A catheter as described in claim 10, which further comprises a shaft insertable in the inner tube and a stopper for the shaft at an apex of the inner tube.
12. A catheter having a balloon comprising an outer elastic film, a reinforcing fabric and an inner elastic film, wherein the reinforcing fabric and the inner elastic film are not adhered with each other whereas the reinforcing fabric is adhered with the outer elastic film, and wherein the reinforcing fabric is made of a composite yarn consisting of an elastic yarn and a non-elastic yarn, the non-elastic yarn having a larger free length than the elastic yarn.
13. A catheter as described in claim 12, wherein the ratio of free length of the elastic yarn to the non-elastic yarn is 0.15-0.5
14. A catheter as described in claim 13, wherein the ratio of free length of the elastic yarn to the non-elastic yarn is of 0.2-0.35.
15. A catheter as described in claim 13, wherein the composite yarn is a core-sheath yarn composed of a core of the elastic yarn and a sheath of the non-elastic yarn.
16. A catheter as described in claim 15, wherein the core-sheath yarn is formed of a urethane yarn as the elastic yarn and a synthetic fiber-twisted yarn as the non-elastic yarn spirally wound on the urethane yarn.
17. A catheter as described in claim 13, 14, 15 or 16, wherein the non-elastic yarn is false-twisted textured yarn.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP1116607A JP2545981B2 (en) | 1989-05-09 | 1989-05-09 | Balloon catheter |
| JP116607 | 1989-05-09 |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CA2032510A1 CA2032510A1 (en) | 1990-11-10 |
| CA2032510C true CA2032510C (en) | 1996-11-05 |
Family
ID=14691357
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA002032510A Expired - Lifetime CA2032510C (en) | 1989-05-09 | 1990-05-09 | A catheter with a balloon |
Country Status (11)
| Country | Link |
|---|---|
| US (2) | US5201706A (en) |
| EP (1) | EP0425696B1 (en) |
| JP (1) | JP2545981B2 (en) |
| KR (1) | KR940002250B1 (en) |
| AT (1) | ATE124874T1 (en) |
| AU (2) | AU628563B2 (en) |
| CA (1) | CA2032510C (en) |
| DE (1) | DE69020856T2 (en) |
| ES (1) | ES2023095T3 (en) |
| HK (1) | HK1007288A1 (en) |
| WO (1) | WO1990013331A1 (en) |
Families Citing this family (149)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| DE69002295T2 (en) | 1989-09-25 | 1993-11-04 | Schneider Usa Inc | MULTILAYER EXTRUSION AS A METHOD FOR PRODUCING BALLOONS FOR VESSEL PLASTICS. |
| US5195969A (en) | 1991-04-26 | 1993-03-23 | Boston Scientific Corporation | Co-extruded medical balloons and catheter using such balloons |
| US5395331A (en) * | 1992-04-27 | 1995-03-07 | Minnesota Mining And Manufacturing Company | Retrograde coronary sinus catheter having a ribbed balloon |
| US5487730A (en) * | 1992-12-30 | 1996-01-30 | Medtronic, Inc. | Balloon catheter with balloon surface retention means |
| US5512051A (en) * | 1993-02-16 | 1996-04-30 | Boston Scientific Corporation | Slip-layered catheter balloon |
| US6025044A (en) * | 1993-08-18 | 2000-02-15 | W. L. Gore & Associates, Inc. | Thin-wall polytetrafluoroethylene tube |
| US5545209A (en) * | 1993-09-30 | 1996-08-13 | Texas Petrodet, Inc. | Controlled deployment of a medical device |
| WO1995009667A1 (en) | 1993-10-01 | 1995-04-13 | Boston Scientific Corporation | Medical device balloons containing thermoplastic elastomers |
| US6896842B1 (en) | 1993-10-01 | 2005-05-24 | Boston Scientific Corporation | Medical device balloons containing thermoplastic elastomers |
| JP3259267B2 (en) * | 1993-12-28 | 2002-02-25 | ニプロ株式会社 | Chemical injection device |
| US20030229372A1 (en) * | 1994-01-26 | 2003-12-11 | Kyphon Inc. | Inflatable device for use in surgical protocols relating to treatment of fractured or diseased bone |
| ES2287635T3 (en) * | 1994-01-26 | 2007-12-16 | Kyphon Inc. | IMPROVED FLAMMABLE DEVICE FOR USE IN SURGICAL METHODS RELATED TO BONE FIXATION. |
| US20060100635A1 (en) * | 1994-01-26 | 2006-05-11 | Kyphon, Inc. | Inflatable device for use in surgical protocol relating to fixation of bone |
| US6248110B1 (en) * | 1994-01-26 | 2001-06-19 | Kyphon, Inc. | Systems and methods for treating fractured or diseased bone using expandable bodies |
| JP3333211B2 (en) * | 1994-01-26 | 2002-10-15 | レイリー，マーク・エイ | Improved expandable device for use in a surgical method for bone treatment |
| DK63894A (en) * | 1994-06-06 | 1996-01-08 | Meadox Medicals Inc | Stent catheter and method for making such a stent catheter |
| US5647848A (en) * | 1995-06-07 | 1997-07-15 | Meadox Medicals, Inc. | High strength low compliance composite balloon for balloon catheters |
| US5766201A (en) * | 1995-06-07 | 1998-06-16 | Boston Scientific Corporation | Expandable catheter |
| US20050131269A1 (en) * | 1995-06-07 | 2005-06-16 | Talmadge Karen D. | System and method for delivering a therapeutic agent for bone disease |
| US20050131267A1 (en) * | 1995-06-07 | 2005-06-16 | Talmadge Karen D. | System and method for delivering a therapeutic agent for bone disease |
| US5752934A (en) * | 1995-09-18 | 1998-05-19 | W. L. Gore & Associates, Inc. | Balloon catheter device |
| US20060271091A1 (en) * | 1995-09-18 | 2006-11-30 | Campbell Carey V | Balloon catheter device |
| US5868704A (en) * | 1995-09-18 | 1999-02-09 | W. L. Gore & Associates, Inc. | Balloon catheter device |
| US6270477B1 (en) * | 1996-05-20 | 2001-08-07 | Percusurge, Inc. | Catheter for emboli containment |
| US6746425B1 (en) * | 1996-06-14 | 2004-06-08 | Futuremed Interventional | Medical balloon |
| US7252650B1 (en) | 1996-08-02 | 2007-08-07 | Ranier Limited | Balloon catheter |
| GB9616267D0 (en) | 1996-08-02 | 1996-09-11 | Ranier Ltd | Balloon catheter |
| EP1024753B1 (en) * | 1997-09-26 | 2003-04-09 | Duke University | Perfusion-occlusion catheter |
| US6126607A (en) * | 1997-11-03 | 2000-10-03 | Barzell-Whitmore Maroon Bells, Inc. | Ultrasound interface control system |
| US6325813B1 (en) * | 1998-08-18 | 2001-12-04 | Scimed Life Systems, Inc. | Method and apparatus for stabilizing vascular wall |
| US7892201B1 (en) | 1999-08-27 | 2011-02-22 | Gore Enterprise Holdings, Inc. | Balloon catheter and method of mounting same |
| US6533806B1 (en) * | 1999-10-01 | 2003-03-18 | Scimed Life Systems, Inc. | Balloon yielded delivery system and endovascular graft design for easy deployment |
| JP2001238956A (en) * | 1999-12-24 | 2001-09-04 | Toray Ind Inc | Catheter with balloon |
| CN1204937C (en) * | 1999-12-24 | 2005-06-08 | 东丽株式会社 | Catheter with balloon |
| US7947059B2 (en) | 2000-03-02 | 2011-05-24 | Boston Scientific Scimed, Inc. | Multilayer medical device |
| ATE318559T1 (en) * | 2000-04-05 | 2006-03-15 | Kyphon Inc | DEVICES FOR TREATING BROKEN AND/OR DISEASE BONES |
| SE519802C2 (en) * | 2001-02-09 | 2003-04-08 | Wallsten Medical Sa | Balloon catheter for application of pressure and heat |
| US7156860B2 (en) * | 2000-05-26 | 2007-01-02 | Wallsten Medical S.A. | Balloon catheter |
| US6686522B2 (en) | 2000-06-22 | 2004-02-03 | Shinko Corporation | Musical instrument with a body made of polyurethane foam |
| CA2419196A1 (en) * | 2000-08-11 | 2002-02-21 | Sdgi Holdings, Inc. | Surgical instrumentation and method for treatment of the spine |
| AU2002211639A1 (en) * | 2000-10-09 | 2002-04-22 | Tricardia, L.L.C. | Material useable for medical balloons and catheters |
| US6632235B2 (en) | 2001-04-19 | 2003-10-14 | Synthes (U.S.A.) | Inflatable device and method for reducing fractures in bone and in treating the spine |
| US7488339B2 (en) * | 2002-10-21 | 2009-02-10 | Boston Scientific Scimed, Inc. | Multilayer medical device |
| WO2004047689A1 (en) * | 2002-11-21 | 2004-06-10 | Sdgi Holdings, Inc. | Systems and techniques for intravertebral spinal stablization with expandable devices |
| ITGE20030007A1 (en) * | 2003-01-27 | 2004-07-28 | Sergio Capurro | COATED ELASTIC WIRE FOR SURGERY |
| US6951675B2 (en) | 2003-01-27 | 2005-10-04 | Scimed Life Systems, Inc. | Multilayer balloon catheter |
| AU2004212942A1 (en) | 2003-02-14 | 2004-09-02 | Depuy Spine, Inc. | In-situ formed intervertebral fusion device |
| US7163523B2 (en) * | 2003-02-26 | 2007-01-16 | Scimed Life Systems, Inc. | Balloon catheter |
| US7744620B2 (en) * | 2003-07-18 | 2010-06-29 | Intervalve, Inc. | Valvuloplasty catheter |
| US7166099B2 (en) | 2003-08-21 | 2007-01-23 | Boston Scientific Scimed, Inc. | Multilayer medical devices |
| US7287115B2 (en) * | 2003-10-30 | 2007-10-23 | Kabushiki Kaisha Toshiba | Multi-chip package type memory system |
| US20050123702A1 (en) * | 2003-12-03 | 2005-06-09 | Jim Beckham | Non-compliant medical balloon having a longitudinal fiber layer |
| US7491213B2 (en) * | 2004-01-13 | 2009-02-17 | Boston Scientific Scimed, Inc. | Catheter shaft having distal support |
| US7641664B2 (en) * | 2004-02-12 | 2010-01-05 | Warsaw Orthopedic, Inc. | Surgical instrumentation and method for treatment of a spinal structure |
| US7635510B2 (en) * | 2004-07-07 | 2009-12-22 | Boston Scientific Scimed, Inc. | High performance balloon catheter/component |
| US7354419B2 (en) * | 2004-10-15 | 2008-04-08 | Futuremed Interventional, Inc. | Medical balloon having strengthening rods |
| US7914487B2 (en) * | 2004-10-15 | 2011-03-29 | Futurematrix Interventional, Inc. | Non-compliant medical balloon having braided or knitted reinforcement |
| US7682335B2 (en) * | 2004-10-15 | 2010-03-23 | Futurematrix Interventional, Inc. | Non-compliant medical balloon having an integral non-woven fabric layer |
| US7309324B2 (en) * | 2004-10-15 | 2007-12-18 | Futuremed Interventional, Inc. | Non-compliant medical balloon having an integral woven fabric layer |
| US7632242B2 (en) | 2004-12-09 | 2009-12-15 | Boston Scientific Scimed, Inc. | Catheter including a compliant balloon |
| CA2596490A1 (en) * | 2005-02-09 | 2006-08-17 | Angiodynamics, Inc. | Reinforced balloon for a catheter |
| US8672990B2 (en) * | 2005-05-27 | 2014-03-18 | Boston Scientific Scimed, Inc. | Fiber mesh controlled expansion balloon catheter |
| US7500982B2 (en) * | 2005-06-22 | 2009-03-10 | Futurematrix Interventional, Inc. | Balloon dilation catheter having transition from coaxial lumens to non-coaxial multiple lumens |
| US7544201B2 (en) | 2005-07-05 | 2009-06-09 | Futurematrix Interventional, Inc. | Rapid exchange balloon dilation catheter having reinforced multi-lumen distal portion |
| US8366773B2 (en) | 2005-08-16 | 2013-02-05 | Benvenue Medical, Inc. | Apparatus and method for treating bone |
| US7670375B2 (en) | 2005-08-16 | 2010-03-02 | Benvenue Medical, Inc. | Methods for limiting the movement of material introduced between layers of spinal tissue |
| US8876763B2 (en) * | 2005-11-01 | 2014-11-04 | Boston Scientific Scimed, Inc. | Composite balloon |
| JP2009519770A (en) | 2005-12-16 | 2009-05-21 | インターフェイス・アソシエイツ・インコーポレーテッド | Medical multilayer balloon and method for producing the same |
| US7682371B2 (en) * | 2006-01-25 | 2010-03-23 | Medtronic Vascular, Inc. | Device with actuatable fluid-column occluder for prevention of embolization |
| CA2646404C (en) | 2006-02-14 | 2015-04-14 | C.R. Bard, Inc. | Coaxial pta balloon |
| US8858855B2 (en) | 2006-04-20 | 2014-10-14 | Boston Scientific Scimed, Inc. | High pressure balloon |
| US8118844B2 (en) | 2006-04-24 | 2012-02-21 | Warsaw Orthopedic, Inc. | Expandable device for insertion between anatomical structures and a procedure utilizing same |
| US20070270823A1 (en) | 2006-04-28 | 2007-11-22 | Sdgi Holdings, Inc. | Multi-chamber expandable interspinous process brace |
| US7943221B2 (en) * | 2006-05-22 | 2011-05-17 | Boston Scientific Scimed, Inc. | Hinged compliance fiber braid balloon |
| US20080097300A1 (en) * | 2006-08-07 | 2008-04-24 | Sherif Eskaros | Catheter balloon with multiple micropleats |
| US9180279B2 (en) | 2006-08-07 | 2015-11-10 | W. L. Gore & Associates, Inc. | Inflatable imbibed polymer devices |
| US20080097374A1 (en) * | 2006-08-07 | 2008-04-24 | Korleski Joseph E | Inflatable shaped balloons |
| US20080125711A1 (en) | 2006-08-07 | 2008-05-29 | Alpini Alfred A | Catheter balloons with integrated non-distensible seals |
| US7785290B2 (en) * | 2006-08-07 | 2010-08-31 | Gore Enterprise Holdings, Inc. | Non-shortening high angle wrapped balloons |
| US20080140173A1 (en) * | 2006-08-07 | 2008-06-12 | Sherif Eskaros | Non-shortening wrapped balloon |
| US8979886B2 (en) * | 2006-08-07 | 2015-03-17 | W. L. Gore & Associates, Inc. | Medical balloon and method of making the same |
| US8460240B2 (en) * | 2006-08-07 | 2013-06-11 | W. L. Gore & Associates, Inc. | Inflatable toroidal-shaped balloons |
| WO2008051452A2 (en) * | 2006-10-20 | 2008-05-02 | Boston Scientific Scimed, Inc. | Medical catheter assembly including a balloon bolster |
| US8105382B2 (en) | 2006-12-07 | 2012-01-31 | Interventional Spine, Inc. | Intervertebral implant |
| WO2008095052A2 (en) * | 2007-01-30 | 2008-08-07 | Loma Vista Medical, Inc., | Biological navigation device |
| WO2009134686A1 (en) * | 2008-04-27 | 2009-11-05 | Loma Vista Medical, Inc. | Biological navigation device |
| EP2124777A4 (en) | 2007-02-21 | 2013-06-05 | Benvenue Medical Inc | Devices for treating the spine |
| CA2678006C (en) | 2007-02-21 | 2014-10-14 | Benvenue Medical, Inc. | Devices for treating the spine |
| US8900307B2 (en) | 2007-06-26 | 2014-12-02 | DePuy Synthes Products, LLC | Highly lordosed fusion cage |
| US8313601B2 (en) * | 2007-08-06 | 2012-11-20 | Bard Peripheral Vascular, Inc. | Non-compliant medical balloon |
| US8002744B2 (en) * | 2007-08-06 | 2011-08-23 | Bard Peripheral Vascular, Inc | Non-compliant medical balloon |
| US20090099517A1 (en) * | 2007-10-10 | 2009-04-16 | C. R. Bard, Inc. | Reinforced, non-compliant angioplasty balloon |
| US20090149700A1 (en) * | 2007-11-02 | 2009-06-11 | Ruben Garcia | Method and apparatus for pubic sling insertion |
| EP2471493A1 (en) | 2008-01-17 | 2012-07-04 | Synthes GmbH | An expandable intervertebral implant and associated method of manufacturing the same |
| US8114136B2 (en) | 2008-03-18 | 2012-02-14 | Warsaw Orthopedic, Inc. | Implants and methods for inter-spinous process dynamic stabilization of a spinal motion segment |
| BRPI0910325A8 (en) | 2008-04-05 | 2019-01-29 | Synthes Gmbh | expandable intervertebral implant |
| EP2644225B1 (en) * | 2008-06-02 | 2020-12-23 | Loma Vista Medical, Inc. | Inflatable medical devices |
| JP2009291345A (en) * | 2008-06-04 | 2009-12-17 | Toray Ind Inc | Injector for inflating balloon |
| EP2147662A1 (en) * | 2008-07-23 | 2010-01-27 | Abbott Laboratories Vascular Enterprises Limited | Stent delivery system |
| WO2010042869A1 (en) | 2008-10-10 | 2010-04-15 | Intervalve, Inc. | Valvuloplasty catheter and methods |
| US20100094074A1 (en) * | 2008-10-10 | 2010-04-15 | Hologic Inc. | Brachytherapy apparatus and methods employing expandable medical devices comprising fixation elements |
| CA2741685A1 (en) * | 2008-10-30 | 2010-05-06 | R4 Vascular, Inc. | Rupture-resistant compliant radiopaque catheter balloon and methods for use of same in an intravascular surgical procedure |
| JP5245842B2 (en) * | 2009-01-09 | 2013-07-24 | 株式会社カネカ | Balloon catheter having a detachable balloon inflation liquid injection tube |
| US8728110B2 (en) * | 2009-01-16 | 2014-05-20 | Bard Peripheral Vascular, Inc. | Balloon dilation catheter shaft having end transition |
| US8814899B2 (en) * | 2009-02-23 | 2014-08-26 | Futurematrix Interventional, Inc. | Balloon catheter pressure relief valve |
| US9259559B2 (en) | 2009-02-23 | 2016-02-16 | Futurematrix Interventional, Inc. | Balloon catheter pressure relief valve |
| US8535327B2 (en) | 2009-03-17 | 2013-09-17 | Benvenue Medical, Inc. | Delivery apparatus for use with implantable medical devices |
| US9526620B2 (en) | 2009-03-30 | 2016-12-27 | DePuy Synthes Products, Inc. | Zero profile spinal fusion cage |
| EP2241284B1 (en) * | 2009-04-15 | 2012-09-19 | National University of Ireland, Galway | Intravasculature devices and balloons for use therewith |
| US8900215B2 (en) * | 2009-06-12 | 2014-12-02 | Bard Peripheral Vascular, Inc. | Semi-compliant medical balloon |
| WO2011028397A1 (en) | 2009-08-24 | 2011-03-10 | Cook Incorporated | Textile-reinforced high-pressure balloon |
| US9211391B2 (en) * | 2009-09-24 | 2015-12-15 | Bard Peripheral Vascular, Inc. | Balloon with variable pitch reinforcing fibers |
| US9393129B2 (en) | 2009-12-10 | 2016-07-19 | DePuy Synthes Products, Inc. | Bellows-like expandable interbody fusion cage |
| US8317831B2 (en) | 2010-01-13 | 2012-11-27 | Kyphon Sarl | Interspinous process spacer diagnostic balloon catheter and methods of use |
| US8147526B2 (en) | 2010-02-26 | 2012-04-03 | Kyphon Sarl | Interspinous process spacer diagnostic parallel balloon catheter and methods of use |
| US8808237B2 (en) * | 2010-04-26 | 2014-08-19 | Joseph Michael Thielen | Expandable perfusion balloon |
| US8440090B2 (en) | 2010-04-29 | 2013-05-14 | Abbott Cardiovascular Systems Inc. | Apparatus and method of making a variable stiffness multilayer catheter tubing |
| US9282979B2 (en) | 2010-06-24 | 2016-03-15 | DePuy Synthes Products, Inc. | Instruments and methods for non-parallel disc space preparation |
| US8979860B2 (en) | 2010-06-24 | 2015-03-17 | DePuy Synthes Products. LLC | Enhanced cage insertion device |
| EP2588034B1 (en) | 2010-06-29 | 2018-01-03 | Synthes GmbH | Distractible intervertebral implant |
| EP2593171B1 (en) | 2010-07-13 | 2019-08-28 | Loma Vista Medical, Inc. | Inflatable medical devices |
| EP2616130A1 (en) | 2010-09-13 | 2013-07-24 | Intervalve, Inc. | Positionable valvuloplasty catheter |
| US9402732B2 (en) | 2010-10-11 | 2016-08-02 | DePuy Synthes Products, Inc. | Expandable interspinous process spacer implant |
| US10188436B2 (en) | 2010-11-09 | 2019-01-29 | Loma Vista Medical, Inc. | Inflatable medical devices |
| US8597240B2 (en) | 2011-02-02 | 2013-12-03 | Futurematrix Interventional, Inc. | Coaxial catheter shaft having balloon attachment feature with axial fluid path |
| US8814873B2 (en) | 2011-06-24 | 2014-08-26 | Benvenue Medical, Inc. | Devices and methods for treating bone tissue |
| US9522070B2 (en) | 2013-03-07 | 2016-12-20 | Interventional Spine, Inc. | Intervertebral implant |
| US10085783B2 (en) | 2013-03-14 | 2018-10-02 | Izi Medical Products, Llc | Devices and methods for treating bone tissue |
| US10166376B2 (en) * | 2013-06-11 | 2019-01-01 | Covidien Lp | Restricted expansion dissector |
| AU2014280833B2 (en) | 2013-06-14 | 2019-04-18 | Organ Transport Pty Ltd | Cardiac function evaluation system |
| US10286190B2 (en) | 2013-12-11 | 2019-05-14 | Cook Medical Technologies Llc | Balloon catheter with dynamic vessel engaging member |
| GB2525220B (en) | 2014-04-16 | 2016-06-08 | Cook Medical Technologies Llc | Non-compliant high strength medical balloon |
| US11426290B2 (en) | 2015-03-06 | 2022-08-30 | DePuy Synthes Products, Inc. | Expandable intervertebral implant, system, kit and method |
| EP3442642A1 (en) | 2016-04-12 | 2019-02-20 | Boston Scientific Scimed, Inc. | Medical balloon |
| US11596522B2 (en) | 2016-06-28 | 2023-03-07 | Eit Emerging Implant Technologies Gmbh | Expandable and angularly adjustable intervertebral cages with articulating joint |
| US11510788B2 (en) | 2016-06-28 | 2022-11-29 | Eit Emerging Implant Technologies Gmbh | Expandable, angularly adjustable intervertebral cages |
| US10576254B2 (en) | 2016-08-05 | 2020-03-03 | Covidien Lp | Medical balloon having a plurality of structural layers |
| WO2018111898A1 (en) | 2016-12-13 | 2018-06-21 | Boston Scientific Scimed, Inc. | Medical balloon |
| US10888433B2 (en) | 2016-12-14 | 2021-01-12 | DePuy Synthes Products, Inc. | Intervertebral implant inserter and related methods |
| JP2020501723A (en) * | 2016-12-16 | 2020-01-23 | シー・アール・バード・インコーポレーテッドＣ Ｒ Ｂａｒｄ Ｉｎｃｏｒｐｏｒａｔｅｄ | Medical balloon, balloon catheter, and method thereof |
| EP3615099B1 (en) | 2017-04-25 | 2023-03-01 | Boston Scientific Scimed, Inc. | Medical balloon |
| US10398563B2 (en) | 2017-05-08 | 2019-09-03 | Medos International Sarl | Expandable cage |
| US11344424B2 (en) | 2017-06-14 | 2022-05-31 | Medos International Sarl | Expandable intervertebral implant and related methods |
| US10940016B2 (en) | 2017-07-05 | 2021-03-09 | Medos International Sarl | Expandable intervertebral fusion cage |
| US11446156B2 (en) | 2018-10-25 | 2022-09-20 | Medos International Sarl | Expandable intervertebral implant, inserter instrument, and related methods |
| US11426286B2 (en) | 2020-03-06 | 2022-08-30 | Eit Emerging Implant Technologies Gmbh | Expandable intervertebral implant |
| CN111420248A (en) * | 2020-04-09 | 2020-07-17 | 玮铭医疗器械(上海)有限公司 | Elastic balloon recovery device |
| US11850160B2 (en) | 2021-03-26 | 2023-12-26 | Medos International Sarl | Expandable lordotic intervertebral fusion cage |
| US11752009B2 (en) | 2021-04-06 | 2023-09-12 | Medos International Sarl | Expandable intervertebral fusion cage |
Family Cites Families (20)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| GB512456A (en) * | 1938-03-09 | 1939-09-15 | Helena Sadilkova | An apparatus for widening narrow or constricted internal organs of the body or their parts |
| US3657873A (en) * | 1969-12-08 | 1972-04-25 | Kirkland H Gibson | Composite elastic core yarn |
| US4024873A (en) * | 1976-05-24 | 1977-05-24 | Becton, Dickinson And Company | Balloon catheter assembly |
| JPS5335052A (en) * | 1976-09-09 | 1978-04-01 | Senichi Maeda | Wound folded yarn between elastic thread and unelastic thread and method of and apparatus for producing same |
| AT348094B (en) * | 1977-02-17 | 1979-01-25 | Hanecka Lubomir Dipl Ing | BALLOON CATHETER |
| US4327736A (en) * | 1979-11-20 | 1982-05-04 | Kanji Inoue | Balloon catheter |
| US4315512A (en) * | 1980-01-24 | 1982-02-16 | Fogarty Thomas J | Piston extension balloon dilatation catheter apparatus and method |
| US4608984A (en) * | 1980-10-17 | 1986-09-02 | Fogarty Thomas J | Self-retracting dilatation catheter |
| SU992072A1 (en) * | 1981-09-18 | 1983-01-30 | Куйбышевский медицинский институт им.Д.И.Ульянова | Catheter |
| SE445884B (en) * | 1982-04-30 | 1986-07-28 | Medinvent Sa | DEVICE FOR IMPLANTATION OF A RODFORM PROTECTION |
| US4637396A (en) * | 1984-10-26 | 1987-01-20 | Cook, Incorporated | Balloon catheter |
| JPS61228877A (en) * | 1985-04-03 | 1986-10-13 | 株式会社クラレ | Thin walled small caliber catheter |
| US4706670A (en) * | 1985-11-26 | 1987-11-17 | Meadox Surgimed A/S | Dilatation catheter |
| US4650466A (en) * | 1985-11-01 | 1987-03-17 | Angiobrade Partners | Angioplasty device |
| SU1477423A1 (en) * | 1986-01-16 | 1989-05-07 | Особое конструкторско-технологическое бюро Физико-технического института низких температур АН УССР | Inflatable catheter |
| NO890322L (en) * | 1988-02-28 | 1989-08-29 | Inst Textil Und Faserforsch St | Catheter. |
| DE68926862T2 (en) * | 1988-10-28 | 1996-11-21 | Kanji Inoue | Balloon catheter assembly |
| US4979491A (en) * | 1989-01-27 | 1990-12-25 | Combustion Research Corporation | Radiant tube and reflector hanger |
| EP0388486A1 (en) * | 1989-03-20 | 1990-09-26 | Gianfederico Dick | Steerable "PTCA" dilatation catheter with a regulating expansion section |
| US5057092A (en) * | 1990-04-04 | 1991-10-15 | Webster Wilton W Jr | Braided catheter with low modulus warp |
-
1989
- 1989-05-09 JP JP1116607A patent/JP2545981B2/en not_active Expired - Lifetime
-
1990
- 1990-05-09 KR KR1019900702669A patent/KR940002250B1/en not_active IP Right Cessation
- 1990-05-09 AU AU55669/90A patent/AU628563B2/en not_active Expired
- 1990-05-09 CA CA002032510A patent/CA2032510C/en not_active Expired - Lifetime
- 1990-05-09 EP EP90907418A patent/EP0425696B1/en not_active Expired - Lifetime
- 1990-05-09 AT AT90907418T patent/ATE124874T1/en active
- 1990-05-09 DE DE69020856T patent/DE69020856T2/en not_active Expired - Lifetime
- 1990-05-09 ES ES90907418T patent/ES2023095T3/en not_active Expired - Lifetime
- 1990-05-09 WO PCT/JP1990/000587 patent/WO1990013331A1/en active IP Right Grant
-
1991
- 1991-03-11 US US07/666,987 patent/US5201706A/en not_active Expired - Lifetime
-
1992
- 1992-10-15 AU AU27029/92A patent/AU648699B2/en not_active Expired
-
1993
- 1993-01-08 US US08/002,422 patent/US5330429A/en not_active Expired - Lifetime
-
1998
- 1998-06-25 HK HK98106569A patent/HK1007288A1/en not_active IP Right Cessation
Also Published As
| Publication number | Publication date |
|---|---|
| WO1990013331A1 (en) | 1990-11-15 |
| US5201706A (en) | 1993-04-13 |
| JPH02295566A (en) | 1990-12-06 |
| DE69020856T2 (en) | 1995-11-30 |
| AU628563B2 (en) | 1992-09-17 |
| KR920700052A (en) | 1992-02-19 |
| HK1007288A1 (en) | 1999-04-09 |
| ATE124874T1 (en) | 1995-07-15 |
| AU5566990A (en) | 1990-11-29 |
| ES2023095A4 (en) | 1992-01-01 |
| AU2702992A (en) | 1992-12-10 |
| EP0425696A1 (en) | 1991-05-08 |
| ES2023095T3 (en) | 1995-09-01 |
| DE69020856D1 (en) | 1995-08-17 |
| AU648699B2 (en) | 1994-04-28 |
| KR940002250B1 (en) | 1994-03-19 |
| JP2545981B2 (en) | 1996-10-23 |
| CA2032510A1 (en) | 1990-11-10 |
| US5330429A (en) | 1994-07-19 |
| EP0425696A4 (en) | 1991-09-25 |
| EP0425696B1 (en) | 1995-07-12 |
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