WO1998039048A2 - Hollow medical wires and methods of constructing same - Google Patents
Hollow medical wires and methods of constructing same Download PDFInfo
- Publication number
- WO1998039048A2 WO1998039048A2 PCT/US1998/004500 US9804500W WO9839048A2 WO 1998039048 A2 WO1998039048 A2 WO 1998039048A2 US 9804500 W US9804500 W US 9804500W WO 9839048 A2 WO9839048 A2 WO 9839048A2
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- Prior art keywords
- medical
- wire
- distal
- guidewire
- distal section
- Prior art date
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Classifications
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- 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
-
- 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
-
- 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
- A61M2025/09008—Guide wires having a 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
- A61M25/01—Introducing, guiding, advancing, emplacing or holding catheters
- A61M25/09—Guide wires
- A61M2025/09133—Guide wires having specific material compositions or coatings; Materials with specific mechanical behaviours, e.g. stiffness, strength to transmit torque
- A61M2025/09141—Guide wires having specific material compositions or coatings; Materials with specific mechanical behaviours, e.g. stiffness, strength to transmit torque made of shape memory alloys which take a particular shape at a certain temperature
-
- 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
- A61M2025/09175—Guide wires having specific characteristics at the distal tip
-
- 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
- A61M2025/09175—Guide wires having specific characteristics at the distal tip
- A61M2025/09183—Guide wires having specific characteristics at the distal tip having tools at the distal tip
-
- 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
- A61M2025/1052—Balloon catheters with special features or adapted for special applications for temporarily occluding a vessel for isolating a sector
Definitions
- the present invention generally relates to surgical device design and fabrication and, more particularly, to hollow medical wires used as guidewires, catheters, and the like, and methods of constructing same. Description of the Related Art
- the catheter is comprised of an elongate hollow body which has mounted on its distal end an inflatable therapy balloon.
- the catheter body in this case is typically constructed from a plastic material and is hollow (e.g., sometimes referred to as "microtubing"), both to supply inflation fluids to the balloon and to allow the catheter device to ride over a thin wire to the site to be treated.
- this medical device is referred to as an "over-the-wire" therapy catheter.
- the thin wire over which the catheter rides is commonly referred to as a "guidewire,” obviously, because it guides the therapy balloon to the treatment location.
- guidewires are typically made from a solid construction, i.e., they are not normally hollow since they do not need to carry fluids to the therapy site.
- Such medical wires can be adapted to guide other types of therapy devices well, such as stents, atherectom ⁇ devices, laser devices, ultrasound devices, drug delivery devices, and the like.
- balloon angioplasty device Another type of balloon angioplasty device is referred to as a "single operator" balloon catheter. More common in Europe, this type of device rides along a guidewire with only a short section of the device (i.e., the "single operator") actually riding completely over with the guidewire.
- a “balloon-on-a- wire” or a "fixed-wire balloon” catheter is referred to as a "balloon-on-a- wire" or a "fixed-wire balloon” catheter.
- the body of the catheter in this case is typically a hollow metallic wire (e.g., a "hypotube") or plastic wire, providing inflation fluid to the balloon mounted on the distal end.
- This type of therapy balloon device is less common in the U.S., being used in about less than 5% of the angioplasty procedures which are performed, compared with both over-the-wire and single operator type therapy balloon catheters which are used about 70% and 25% of the time, respectively.
- Pushability refers to the ability of a medical guidewire to be efficiently and easily pushed through the vasculature of the patient without damage thereto, but also without getting hung up, blocked, kinked, etc. Excessive force should not be necessary.
- the relative stiffness or rigidity of the material from which the wire is made is a key mechanical feature of the wire, at least with respect to its pushability. That is, the wire must be stiff enough to be successfully and efficiently pushed through the vessels to the treatment site, but not too stiff to cause damage.
- a guidewire that is not sufficiently stiff or rigid will suffer "prolapse.” This condition occurs when the wire bends over on itself or strays down a branching vessel without progressing to its intended site.
- a wire that is too limp lacks sufficient strength to have good pushability characteristics, which are important in virtually all guidewire applications.
- Trackability in the case of guidewires, refers to the ability of the wire to have another device, such as a therapy catheter, efficiently pushed over it to a particular location. Thus, this is also an important feature of catheters which must also "track” efficiently over a guidewire. Time is usually of the essence with respect to many noninvasive therapy procedures since the blood flow of the patient may be interrupted partially or wholly, during such therapy. In addition, there are often a number of "exchanges" during such procedures in which one over the wire device is removed and replaced with another - both riding on the same guidewire. Thus, the ability of the guidewire to provide good tracking characteristics is important to the success of the wire. Again, the stiffness of the wire plays an important role in its trackability characteristics. Also, the lubricity of the material from which the wire is made will enhance its trackability by reducing frictional forces.
- Torqueability refers to the ability of a medical wire to be accurately turned or rotated. It is often important, in traversing bends or turns, that the wire be rotated into a certain position. Ideally, a guidewire should exhibit 1:1 torqueability characteristics; for example, a one-quarter turn by the physician at the proximal end should result in precisely a one-quarter turn in the wire at the distal end. As one may expect, such ideal torqueability is very difficult to achieve in present medical wire technology. Flexibility is another important characteristic of medical wires. It relates to the ability of the wire to follow a tortuous path, i.e., winding and bending its way through the tight turns of a patient's vasculature. Small radius turns are found especially in the coronary arteries.
- guidewire technology also faces the challenge of extremely small dimensions.
- guidewires used in therapeutic procedures performed in peripheral vessels often have an outer diameter of about .035 inches to around .038 inches.
- Wires used in connection with the coronary arteries are even smaller, ranging from .014 inches to .018 inches OD.
- Some devices even utilize guidewires with outer diameters of .009 inches. With these extremely small dimensions, it is very difficult to maintain the functional requirements for medical guidewires as outlined above.
- medical guidewires should also meet a number of structural requirements.
- the straightness of the wire is very important. If it is not as straight as possible, many functional features are lost, including most significantly the risk of damage to the vessel.
- the roundness of the wire contributes to its accurate torqueability. Consistent wall thickness, lubricity, and many other structural and dimensional characteristics also play an important role.
- the plastic deformation of a superelastic material may be accelerated through a number of cyclical deformations, sometimes referred to as fatigue. Such cyclical deformations can occur if the wire experiences a number of tight turns, such as is possible in the coronary arteries.
- Such superelastic materials include a variety of nickel titanium (NiTi) alloys, commonly referred to as "nitinol,” and other alloys exhibiting similar properties such as Cu-Zn-Mn and Fe-Mn-Si ternary alloys.
- the present invention comprises a catheter having an elongate hollow body and a distally mounted occlusion device, preferably an occlusion balloon.
- the catheter body which serves as a guidewire, comprises a hypotube constructed from a specially selected superelastic nitinol material.
- the nitinol material exhibits unique nonlinear characteristics which provide unexpectedly high guidewire performance features.
- the present catheter can deliver deployment media to the distal occlusion device, or assist in many other functions such as irrigation, drug delivery, and the like.
- the distal end of the catheters also provide it with a soft tip in order to avoid injury to the patient.
- the body of the catheter, just proximal the occlusion balloon, is provided with a series of spaced radial radiopaque markers in order to provide visible reference points for the physician within the working space.
- the present invention comprises a catheter of similar construction in which the superelastic nitinol body does not necessarily serve as a guidewire.
- the present invention comprises a composite medical wire device in which the wire is only partially constructed from the preferred nonlinear superelastic nitinol material.
- the material may be joined with other materials (such as stainless steel, polymers or plastics, etc.) so as to be utilized for a given application.
- the distal section is constructed from the special nitinol material in order to achieve superior performance in softness and elasticity, but other sections may be formed from this material as well.
- the elongate body of the catheter can be internally constructed from the preferred nitinol material and then covered with a biiayer of stainless steel to form a concentric construction.
- special heat treatments can be applied to the distal section to provide it with superior softness and flexibility.
- such flexibility can be achieved through tapering to very small wall thicknesses.
- the preferred superelastic medical wire comprises a Ni-Ti (nitinol) binary alloy having a nickel content between 50.0% and 51.5% by atomic weight, and preferably about 50.8%.
- the wire material can also be selected from a group of nitinol family ternary alloys comprising of Ni-Ti-V, Ni-Ti-Co, Ni-Ti-Cu, Ni-Ti-Cr, Ni-Ti-Nb, Ni-Ti-Pd or from a group of non-nitinol ternary alloys comprising Fe-Mn-Si.
- a catheter or guidewire of the present invention constructed from the selected nitinol material exhibits outstanding performance characteristics.
- the present invention wire devices also exhibit important characteristics of high recoverable strain and low modulus.
- recoverable strains in the range of about 1 % to about 8% are feasible. This allows the present medical wire device to undergo high deformation without plastically deforming, a characteristic which is especially important in the case of thin-walled hollow hypotubes.
- the medical wire device of the present invention provides excellent handleability and "feel" for the physician.
- the nitinol material undergoes special heat treatment in order to achieve transformational effects. In this case, substantially constant stresses are maintained over a wide range of recoverable strains, improving even further the performance of the device.
- the present invention comprises a medical guidewire having an elongate body with distal and proximal sections.
- the body is constructed at least partially from a non-linear, superelastic nickel titanium alloy material having a nickel content in the range of about 50% to 51.5% atomic weight.
- the distal section of the body receives heat treatments in the range of 300°C-600°C for about 10 seconds to 60 minutes such that the material has recoverable strains in the range of about 1 % to about 8%.
- the device also is provided with an occlusion device mounted on its distal section, and a lumen formed in the elongate body for communicating fluids from the proximal section to the distal section of the body. A passage way is formed through the distal section to communicate said fluids to the occlusion device.
- the present invention comprises a medical catheter having an elongate body and having distal and proximal sections.
- the body is constructed from a nickel titanium alloy material having a nickel content in the range of 50.0%-51.5% by atomic weight.
- At least the distal section of the body is constructed from a transformational nickel titanium alloy material exhibiting substantially constant stress over a range of recoverable strain from about 1% to about 8%.
- the device is also provided with a balloon mounted on its distal section and a lumen formed in the elongate body for communicating fluids from the proximal section to the distal section of the body. A passageway is formed through the distal section to communicate fluids to the balloon.
- present invention comprises a medical wire having an elongate body with distal and proximal sections. At least the distal section is partially constructed from a nickel titanium alloy material having substantially constant stress values over a range of recoverable strains from about 1 % to about 8%. The proximal section is constructed from a second material having a modulus which is different for a given strain than the alloy material.
- the present invention comprises a medical wire having an elongate body comprising a hollow non-linear superelastic nickel titanium alloy material having recoverable strain in the range of 1 % to at least 8%..
- FIGURE 1 is a schematic view of the medical catheter of the present invention
- FIGURE 2 is a schematic cross-sectional view of a distal portion of the catheter apparatus shown in FIGURE
- FIGURE 3 is a schematic view of a hollow guide wire comprising a series of radiopaque markers
- FIGURE 4A is a graph comparing the stress-strain characteristics of non-transformational and transformational superelasticity
- FIGURE 4B is a graph comparing the stored deformation energies of non-transformational and transformational superelasticity
- FIGURE 5A is a schematic cutaway view of a vessel and a medical wire positioned within the vessel;
- FIGURE 5B is a schematic view of a medical wire positioned within the coronary arteries;
- FIGURE 6 is a Ni-Ti phase diagram
- FIGURE 7A is a schematic view of an embodiment to straighten the hypotube by rolling
- FIGURE 7B is a schematic view of an alternative embodiment to straighten the hypotube by twisting
- FIGURE 8A is a schematic cross-sectional view of an embodiment of a composite hollow guidewire
- FIGURE 8B is a schematic cross-sectional view of a joint in the composite hollow guidewire
- FIGURE 8C is a schematic cross sectional view of another embodiment of the composite hollow guidewire.
- FIGURES 9A-9C are schematic cross-sectional views of alternative embodiments of a hollow catheter having holes, valves, and the like, to permit the escape of irrigation or other fluids.
- the catheter apparatus 10 is generally comprised of four communicating members including an elongated body or tubular member 14, a balloon member 16 and a core-wire member 20 and a coil member 22.
- the catheter apparatus 10 is preferably provided with an outer coating of a lubricous material, such as Teflon.
- the body member 14 of the catheter apparatus 10 is in the form of hypotubing and is provided with proximal and distal ends 14A and 14B and as well as an inner lumen 15 extending along the tubular member 14.
- the balloon member 16 is coaxially mounted on the distal end 14B of the tubular member 14 by suitable adhesives 19 and 21 at a proximal end 16A and a distal end 16B of the balloon member 16 as in the manner shown in FIGURE 2.
- the core-wire member 20 of the catheter 10 may be comprised of a flexible wire 20.
- the flexible wire 20 is joined by soldering, brazing or using adhesives at a proximal end 20A of the flexible wire 20 to the distal end 14B of the tubular member 14 as in the manner show in FIGURE 2.
- the proximal end 20A of the flexible wire 20 has a transverse cross sectional area substantially less than the smallest transverse cross-sectional area of the inner lumen 15 of the tubular member 14.
- the flexible wire 20 tapers in the distal end 20B to smaller diameters to provide greater flexibility to the flexible wire 20.
- the flexible wire may be in the form of a solid rod or a helical coil or wire ribbon or combinations thereof.
- the distal end 20B of the flexible wire 20 is secured to a rounded plug 18 of solder or braze at a distal end of the coil member 22.
- the coil member 22 of the catheter 10 may be comprised of a helical coil.
- the coil member 22 is coaxially disposed about the flexible wire 20, and is secured to the flexible wire 20 by soldering, brazing or using adhesives at about the proximal end 20A of the flexible wire 20 as in the manner shown in FIGURE 2.
- the balloon member 16 is preferably a compliant balloon formed of a suitable elastic material such as C-FlexTM, a latex or the like. Other occlusive or therapy devices could also be used.
- the flexible coil 22 is preferably formed of a wire of platinum based alloy so as to be visible during fluoroscopy.
- the flexible core-wire 20 may preferably be formed of a superelastic nickel-titanium alloy or stainless steel.
- the tubular member 14 is preferably formed of a superelastic nickel-titanium alloy described below in more detail.
- FIGURE 3 illustrates another aspect of the catheter of the present invention.
- a radiopaque marker ring 11A is indicated near the distal tip of the catheter 11. This allows the physician to detect the location of the catheter under fluoroscopy or other visualization.
- therapy catheters 13 dashed lines
- FIGURE 3 illustrates a hypothetical location of this therapy catheter marker 17, but illustrates the therapy catheter 13 itself in dashed lines.
- the position of the therapy marker 17 is gauged by visualization means such as fluoroscopy.
- visualization means such as fluoroscopy.
- the exact location of the occlusion balloon 25 is not always known.
- the occlusion balloon 25 is typically relatively short so as to avoid interfering with the therapy in the treatment location.
- the guidewire 12 in which the occlusion balloon 25 is mounted may shift slightly during the procedure, and may interfere therewith or become damaged itself from the action of the therapy catheter 13.
- a series of radiopaque markers are formed on the body of the guidewire 12 as indicated in FIGURE 3. These markers 22 are uniformly spaced apart by a given dimension such as 1 mm in order to also provide the physician with a reference system within the working area, in using these markers, once the relative positions of the guide catheter ring 11A and the therapy marker 17 are determined, the number of guidewire markers 22 in between these two reference points can be used to reposition the guidewire if necessary.
- any relative movement of any of these devices i.e., the guide catheter 11, the therapy catheter 13, or the guidewire 12, can be detected and steered into the desired location in the patient's body as well as measured for easy correction.
- Such markers 22 can be of a typical type and manufactured from radiopaque materials such as platinum, gold, etc. They can be embodied in the wall of the guidewire 12 or applied as plating to a reduced diameter portion thereof in order to maintain its smooth outer profile. Moreover, it should be noted that this feature of the invention can also be applied to other types of medical wires, with or without occlusion balloons, and in conjunction with other types of guiding or therapy catheters.
- Non-linear Superelastic Nitinol In accordance with the principles of the present invention, the elongated body member 14 of the catheter
- the body 14 is constructed from a superelastic nitinol and, more particularly, a superelastic nitinol which exhibits non-linear behavior characteristics with respect to its stress-strain relationship (FIGURE 4A).
- FOGURE 4A stress-strain relationship
- Ni-Ti alloys or nitinol alloys are the most important of the shape memory alloys (SMA). Such materials can adjust their properties and shape according to changes in their environment, specifically changes in applied stress and temperature. In this respect, nitinol alloys can change their shape by strains greater than 8% and adjust constraining forces by a factor of 5 times. The scientific foundations of the shape memory effect is well known in the art.
- Superelasticity refers to the ability of a material to reversibl ⁇ transform its crystal structure and shape in order to relieve applied stresses so that the material can undergo large elastic deformations without the onset of plastic deformation.
- This superelasticity often referred to as transformational superelasticity, exhibits itself as the parent crystal structure of the material as it transforms into a different crystal structure.
- the parent crystal structure or the phase is known as the austenitic phase and the product crystal structure is known as the martensitic phase.
- Such formed martensite is termed stress induced martensite.
- superelastic characteristics of the nitinol alloys can be best viewed by the stress strain diagrams obtained from various mechanical testing methods such as tensile tests, torsion tests, bending tests or compression tests.
- the tensile test emerges as the most common mechanical testing method.
- tensile tests provide very useful information about both the type of deformation and the amount of deformation that a test sample undergoes under an applied stress.
- FIGURES 4A and 4B provide very valuable information about the deformation characteristics of the superelastic nitinol alloys under tensile test conditions.
- these tensile stress strain diagrams are equivalent to stress strain diagrams provided with torsion, bending and compression tests.
- FIGURE 4A in a tensile stress-strain (deformation) diagram of austenitic superelastic alloys, superelastic materials in general exhibit two different types of non-linear elastic deformation characteristic.
- the first deformation characteristic which is referred to as transformational non-iinear superelastic deformation, can be depicted by a first hysteresis 31 defined by a loading curve 30 and an unloading curve 40.
- the loading curve 30 and unloading curve 40 are non-linear curves thereby representing a non-linear superelastic deformation behavior.
- FIGURE 4A illustrates a second deformation characteristic referred to as non- transformational.
- non-transformational superelastic deformation is also non-iinear due to a second hysteresis 51 defined by a loading curve 50 and an unloading curve 52.
- the non-linearity in this case is a less emphasized non-linearity so that the curves 50 and 52 follow a rather smooth change.
- the first and second hysteresis 31 and 51 occur due to internal friction and plastic deformation.
- the austenitic phase elastically deforms with increasing stress up to a critical yielding stress value 35 where martensitic transformation begins. After this critical stress point 35, the material continues to transform into martensite. Throughout the transformation, despite a constant increase in deformation rate of the material, the applied stress remains about the same critical stress value 35 thereby revealing the superelastic property of the material.
- the curve 30 no longer follows a straight path but a linearly increasing path 39 where the martensitic material elastically deforms up to a point 37 where unloading begins.
- the martensite structure transforms into austenite structure. Due to internal friction, there is not an overlap of loading and unloading curves 30 and 40, and the unloading curve 40 moves down to lower stress values.
- the martensitic phase is first unloaded along the linear portion 49 of the curve 40.
- a critical stress value 47 martensite to austenite transformation begins and continues along the unloading plateau 42.
- the elastic deformation on austenitic material is unloaded along the linear portion 43.
- the unloading does not totally reverse the superelastic deformation.
- a permanent deformation or "set" 48 remains after the completion of unloading.
- non-transformational superelastic deformation does not produce a plateau of constant stress. Due to little or no martensitic transformation, the loading and unloading curves 50 and 52 demonstrate a less non-linear increase and decrease respectively. In other words, changes in superelastic deformation behavior are not as drastic as in the case of transformational superelasticity. In fact, as is seen in FIGURE 4A, curves 50 and 52 adopt a rather smooth change in non-linearity. In such materials, a high level of elastic deformation can only be possible with the application of high levels of stress. However, it is understood that the modulus of elasticity for such non-transformational nitinol alloys is still significantly lower than the modulus of elasticity for stainless steels.
- the difference in elastic deformation behavior for the transformational and non-transformational cases can be clearly seen in FIGURE 4B by means of stored elastic energies for each deformation case.
- the stored elastic deformation energy can be defined with areas 55 and 56 under the respective unloading curves 40 and 52. It would be understood that, at a random deformation value e ⁇ , the non-transformational superelastic deformation stores more elastic deformation energy which is equivalent to spring back energy of the superelastic material.
- the spring back energy in transformational case can be increased by increasing the deformation range beyond e ⁇ . However, an increase more than 6% deformation reduces the stiffness of the material and hence reduces the spring back force and the unloading stress.
- the medical wires of the present invention take advantage of particular non-linear superelastic nitinol characteristics to achieve better functional performance, especially in terms of flexibility and handleability.
- the present medical wires also demonstrate, in practice and under adverse conditions, improved characteristics of pushability, trackability, and torqueability, especially in comparison to previous superelastic and elastic wires.
- the present medical wire in addition to its superelasticity, also exhibits the following excellent characteristics: very high recoverable strain with virtually no permanent set; a relatively low modulus compared to other elastic materials; and some hysteresis in its unloading curve.
- superelasticity refers to the ability of a material to recover strain after deformation.
- the medical wire of the present invention advantageously recovers strain over a wide range of deformations, typically 1-8% and even 9-10% in some cases where there has been careful attention to the heat treatment of the wire material.
- This high recoverable strain characteristic in the present wire allows the wire to traverse a wide range of tortuous turns without plastic deformation, which of course would inhibit or destroy the performance of a wire.
- FIGURE 5A This characteristic can be illustrated schematically with reference to FIGURE 5A. This figure is a cutaway view of a vessel 26 exhibiting a sharp turn.
- the medical wire is shown traversing the turn; although, it will be noted that no guide catheter within the vessel 26 is illustrated for simplicity, and that the medical wire 14 of the present invention may be used with or without a guide catheter. With the medical wire 14 of the present invention, it has unexpectedly been discovered that turns of even very small radii can be traversed with confidence without plastic deformation. The following calculations adequately illustrate this point. That is, for a hollow tube, the strain experienced in bending is given as follows:
- a typical recoverable strain for a hollow medical wire can be as high as .4%. If the medical tube has a diameter of .014" (overage), then the radius is 1.75". This means that an elastic stainless steel wire having this maximum strain cannot bend around a turn having a radius smaller than 1.75" without suffering plastic deformation. However, for the medical wire 14 of the present invention, having similar dimensions, maximum recoverable strain can easily be about 6%. Thus, solving the above equation for the radius yields a result of only 0.117". For maximum recoverable strains of 8%, which are within the range of the present invention, even tighter turns can be traversed.
- the medical wire 14 of the present invention can successfully avoid permanent deformation over a wide variety of adverse conditions, thus providing excellent tortuosity characteristics. Furthermore, because plastic deformation is avoided, the pushability and torqueability characteristics of the present wire 14 are maintained. This is compared with previous medical wires which begin with as good or even better characteristics of pushability and torqueability, but because they experience plastic deformation traversing a certain number of tortuous turns or pushing against obstructions, their performance characteristics in actuality are greatly diminished.
- Nitinol in general, is used in certain medical wire applications because of its enhanced flexibility and corresponding kink resistance in comparison with stainless steel. Kinking greatly reduces the ability to push or steer a wire into the desired location, and also obviously reduces the ability to slide a catheter over the wire. Thus, the flexibility of nitinol, which derives generally from its low modulus, is an advantage in certain applications.
- Stainless steel however, according to conventional thought, is more often selected for medical wire and catheter applications due to its enhanced torqueability and pushability characteristics. These characteristics are derived from the greater rigidity of stainless as compared to nitinol. From this perspective, therefore, the flexibility of nitinol can be considered a disadvantage, and indeed, many nitinol alloys are too flexible to perform well in connection with torqueability and pushability.
- nitinol alloys which are carefully selected in accordance with the principles of the present invention can out perform stainless steel not only in terms of flexibility, but of torqueability and pushability as well. This is true for a wide range of recoverable strains, including, but not limited to those within the elastic limit of stainless steel (being about .4 to .6% in tension). It is especially true for strains beyond the elastic limit of stainless steel. It will be noted that, in bending, the elastic limit of a solid stainless steel wire may be slightly higher than the range quoted above (such as about .8%); although, in a tubular construction (e.g., a hypotube), the elastic limit of stainless may vary.
- the hollow medical wires and catheters of the present invention constructed in accordance with the material selection criteria prescribed herein, provide excellent torqueability and pushability characteristics, as well as flexibility and kink resistance.
- the present invention also demonstrates enhanced characteristics of handleability.
- FIGURES 5A and 5B relates to the containment of the wire as it undergoes bending. Under conditions of higher wall friction, the nitinol wire again out-performed the stainless steel wire, even below the elastic limit of the stainless steel. This is probably due to the higher coefficient of friction and higher modulus of the stainless, which causes it to form local indentations in the wall of the tubing (which may take the form of a guide catheter or the wall of a blood vessel).
- nitinol wires within the scope of the present invention not only provide enhanced torqueability, but also help to avoid damage to sensitive tissue.
- the nitinol wires and catheters of the present invention provide enhanced characteristics over similar sized stainless wires and catheters not only in terms of flexibility, but also torqueability, pushability, and handleability.
- the medical wire of the present invention is also able to achieve other advantages by exhibiting a relatively low modulus. That is, for a given strain, the stress exhibited by the present medical wire 14 is relatively lower than with previous superelastic medical wires. This characteristic advantageously exhibits itself in the functionality of the present wire 14. For example, in the context of a tortuous path, as the wire 14 turns the corner of a tight radius turn, it becomes "loaded” in the sense that the bending it experiences causes a certain amount of deformation or strain. According to this stress-strain relationship, there is induced a corresponding stress force in the wire 14, which manifests itself in the tendency of the material to want to straighten out to its original straight configuration.
- FIGURE 5B shows the guide wire 14 of the present invention within a coronary artery 29 in the heart 34. Smooth and consistent pushing forces provide a better feel of the wire for the physician, and can be utilized to precisely traverse the vasculature of the patient and position the wire at the precise location for successful treatment.
- stress values can be advantageously adjusted according to heat treatment or other post- construction condition
- stress values in the range of 20-100 (Klbs. per square inch) (ksi) (150 MPa-750 MPa) have been found to be suitable for the present medical wire, at least at strains in the range of 2-6% or more.
- Another advantageous characteristic of the present medical wire is its ability to generate an even lower stress upon unloading. That is, in contrast to the above discussion directed to low stress values upon loading (i.e., as the wire traverses a tight turn), the present wire exhibits even lower stress values as the wire completes the turn (i.e., during unloading). As soon as a length of the wire is sufficiently beyond a turn to allow it to straighten itself, it may be considered unloaded.
- the unloading portion of the stress strain curve in the present wire gives, for a given strain, the stress value induced in the material as it recovers its strain.
- the area under the unloading curve is sometimes referred to as the elastic or springback energy because it characterizes the forces experienced by the material as it returns to its original configuration.
- a high springback energy causes a whipping effect at the distal end.
- the plateau stresses are preferably in the range of 300-500 MPa, while upon unloading the stresses are less, e.g. 80-400 MPa.
- the hysteresis of the unloading curve increases with greater deformation; thus, at about 7% strain, an unloading stress of about 200 MPa is preferred.
- an even lower modulus is achievable with such transformational nitinols.
- one of the distinguishable characteristics of such materials is a relatively constant loading stress which is typically referred to as a "loading plateau.” That is, over a wide range of recoverable strains, the material exhibits a substantially constant stress value. As explained above, this allows the material to exhibit excellent performance characteristics, in terms of low friction and handleability. In use, doctors are able to apply smooth, constant pushing forces without a concern for excessive forces needed to traverse tight turns.
- an important aspect of the present invention is the selection of the proper non-linear superelastic nitinol sufficient to achieve the desired functional characteristics which are desired for a particular application.
- the selection of the appropriate non-linear material may vary depending on such desired characteristics and the various design tradeoffs which must be made.
- a transformational non-linear nitinol may be selected versus a non-transformational type. That is, in an application where cyclical deformations are experienced, the resistance to fatigue-induced plastic deformations is an important functional characteristic.
- one may select a non-transformational type non-linear nitinol because of its narrower hysteresis and higher strength.
- a given medical wire may also be constructed so as to have characteristics of both transformational and non-transformational materials.
- the proximal end of the medical wire may be constructed from a non-transformational nitinol to provide enhanced pushability and trackability characteristics, while the distal end of the same wire (say, in the range of the distal 2 to 15 cm) undergoes special conditioning in order to achieve a transformational state.
- the distal end will be softer and will exhibit the constant, reduced stress forces at even very high recoverable strains which are characteristic of non-transformational nitinols.
- Other advantages can be achieved with composite wires constructed from non-linear nitinols and stainless steel or other materials.
- the catheter illustrated in FIGURES 1-2 can be constructed, at least in part, from a transformational non-iinear nitinol having a recoverable strain of about 8%.
- maximal elongation and failure is at least about 14%, providing strong safety characteristics. Because of the material's transformation, it exhibits a loaded plateau stress at room temperature of about 75 ksi (500 MPa) and an unloading plateau stress of about 25 ksi (170 MPa).
- nitinol In regard to material selection, it will be noted that the process of alloying, nickel and titanium is a well- established art for the production of nitinol; however, as noted above, there are many nitinol materials which may not supply the desired performance characteristics. Nevertheless, various types of nitinol materials which may be successfully used in the construction of the medical wires of the present invention are commercially available from companies such as Memry Corp. which provides one suitable nitinol material known as Tinel® Alloy BB.
- Ms-temperature refers to temperature that martensitic transformation from austenite begins. At the Mf-temperature martensitic transformation finishes. Further, temperatures As and Af indicate the respective beginning and the end of austenitic reversion. However, as indicated before, the applied stress shifts these temperature ranges.
- Md temperature is defined as the temperature above which stress-induced martensitic transformation cannot occur.
- ⁇ 6x ⁇ T where ⁇ T is the temperature difference between the body and the room temperatures. ⁇ is the amount of added stress due to the increase in temperature.
- the superelasticity of nitinol is considered to be its state during use more or less at body temperature.
- Ni-Ti alloy composition is preferably selected from a Nickel rich composition ranging from 50.0 atomic% Ni to 51.5 atomic % Ni, preferably from 50.6 atomic% Ni to 50.9 atomic% Ni.
- the superelastic alloy of the present invention may be selected from the group of nitinol family ternary alloys including Ni-Ti-V, Ni-Ti-Fe, Ni-Ti-Cu, Ni-Ti-Co, Ni-Ti-Cr, Ni-Ti-Nb, Ni-Ti-Pd or non-nitinol Fe-Mn-Si ternary alloys.
- nitinol family ternary alloys a preferred composition range basically determined by the formula: Ni(Atomic%) + Ti(Atomic%) + 3 rd Element(Atomic%) - 100 where, 3 rd Element(Atomic%) is less than 14% atomic weight.
- the 3 rd Element defines V, Fe, Cu, Co, Cr, Pd and Nb elements of the ternary compositions, such as Ni-Ti-V, etc.
- the distal section 14B (FIGURE 1) of the nitinol hypotube 14 must be very flexible to facilitate the entry of the distal section 14B into a desired blood vessel during angioplasty procedures. This is especially true of the distal most 30 cm or so of the medical wire which, in the case of a coronary guidewire, must enter the vessel without the protection of a guide catheter. Therefore, this section must exhibit a high degree of softness and a very low modulus. In accordance with the principles of present invention, this flexibility can be provided in various ways such as reducing the thickness at distal-end 14B or applying appropriate heat-treatments to the distal-end 14B, or both. Within the scope of this invention, it will be understood that the term heat treatment refers to any thermal treatment that has been applied to the material before or after inserting into patient's body.
- the wall thickness of the distal portion 14B of the hypotube 14 can be reduced to accommodate the need for flexibility at the distal end 14B.
- the wall thickness can be reduced to about .001 to about .0015".
- Thickness reduction at the distal-end 14B can be done by either tapering the distal- end or performing a uniform thickness reduction along the distal-end 14B.
- the distal-end 14B of the hypotube 14 can be tapered to a lower diameter to provide distal flexibility and proximal stiffness.
- the distal-end may be heat treated for a period of time to provide flexibility and softness.
- the heat-treatment reduces the force required to reach the elastic plateau 32 (FIGURE 4A) so that the heat treated distal-end 14B is more flexible than the proximal-end.
- the heat treatment can be done in salt baths such as the salt baths containing potassium nitrates, and preferably at a temperature range between 300 and 600 °C, and for a preferred time range of 10 to 60 minutes. It should also be noted that other sections of the medical wire, besides the distal section, could also receive special heat treatments in order to vary their characteristics for a particular purpose. Manufacturing Process
- the alloy of the present invention can be made superelastic by facilitating various thermal and/or mechanical treatments.
- the alloy can typically be shaped into the hypotube 14 or core wire 20 by cold working the material and/or heat treating the alloy.
- the cold work can be performed by reducing the tube wall diameter or the outer diameter of the tube.
- Various facilitating instruments such as swager, metal extrusion and drawing equipment can be utilized to provide cold work.
- the hypotube 14 is shaped by cold working the material at a preferred cold work range of 20-40%.
- Ni-Ti tubes are typically manufactured by inserting a core element in a cylindrical Ni-Ti bar and drawing this bar into smaller diameters through the use of series of dies and intermediate heat treatments above 600° C.
- the hypotube is preferably heat treated at a temperature range between 500 and 600°C.
- This heat treatment can preferably be done in a salt bath, such as potassium nitrate, or in a protective atmosphere, such as Argon gas, for 10 seconds to 60 minutes.
- the heat treated hypotube 14 may not be quenched but preferably cooled down to room temperature in a protective atmosphere.
- the resulting superelastic hypotube has a martensitic transformation temperature (Ms) of -30°C, and an austenitic transformation temperature (As) of 11 °C.
- Ms martensitic transformation temperature
- As austenitic transformation temperature
- the stress level at loading plateau 32 (FIGURE 4A) or loading plateau stress is 450 MPa
- the stress at unloading plateau 42 is 150 MPa. Under these conditions the material presents more than 6% superelasticity.
- the heat treatment can be performed at less than 500°C.
- This material can also have more than 6% superelasticity.
- the heat treatment temperature causes a significant shift in stress and transformation temperatures, Ms and As respectively. Particularly, lower heat treatment temperature increases the plateau stress.
- the resulting material have a loading plateau stress of 550 MPa and an unloading plateau stress of 320 MPa.
- Ms temperature is -75°C and As temperature is -3°C.
- hypotube 14 During the manufacturing of hypotube 14, the roundness and the straightness of the hypotube present an important problem. It is well-known that many cardiovascular applications require the use of straight and round tubing. This can be done through a series of thermo-mechanical treatments following the production of hypotube by the method given above. Thermo-mechanical treatments include twisting, pulling and bendings combined with heat treatments above 300°C. Various facilitating instruments can be used to provide roundness. As illustrated in FIGURE 7A, the hypotube 14 of the present invention can be drawn (in the direction of arrow 65) among a series of rotating rollers 64 to provide required roundness. Similarly, as illustrated in FIGURE 7B, the body of the hypotube 14 can be twisted about the longitudinal axis of the hypotube to provide further roundness.
- Twisting can be performed continuously or in discrete process steps. Twisting may be performed by securing the one end of the hypotube 14 using suitable means 66, and rotating the other end in the direction of the arrow 67 as in the manner shown in FIGURE 7B. During the twisting, variations in tube wall thickness are uniformly distributed along the length of the tube. However, it will be appreciated that twisting methods are well-known in the art and may be performed in a variety of ways.
- a solution treatment above 500°C and an aging process at relatively low temperatures, preferably 400°C may be applied to the cold worked hypotube.
- the resulting material has a loading plateau stress of 300 MPa, unloading plateau stress of 100 MPa. This process also presents more than 6% recoverable strain.
- the material may only be cold worked and the cold working process is not followed by an annealing step.
- the material superelasticity follows the hysteresis 51 as shown in FIGURE 4A. There are no plateau stresses or definite transformation temperatures. This material exhibits about 4% superelasticity.
- the hypotube 14 is preferably coated with an outer lubricous material coating, such as Teflon, to increase the lubricity of the hypotube 14.
- Teflon coating requires temperatures above 200°C. However, such high temperatures may interfere with the previous heat treatments and cause unwanted property changes, such as over softening of the material, in order to prevent such drawbacks, it is preferred that the Teflon coating be performed during some of the final heat treatments of the hypotube 14 so that the properties of the hypotube remains unchanged.
- the catheter apparatus 10 may be constructed using a single nitinol hypotubing or a composite structure comprising various tubing materials such as stainless steel, tantalum, titanium or nitinol alloys with varying Ni contents or even plastics.
- an exemplary composite structure can be formed by attaching a stainless steel hypotube 70 to a Ni-Ti hypotube 75 by using suitable adhesives, soldering, brazing, or press fitting, as in the manner shown in FIGURE 8A.
- Ni-Ti hypotube 75 may form the distal portion of the catheter apparatus 10 and have a length of about 20 cm.
- the composite wires of the present invention may also include other sections, beside the distal section, comprised of non-linear nitinol.
- the present composite medical wire will have two or more effective moduli in order to provide greater versatility in performance.
- FIGURE 8B Another method of joinder is illustrated in FIGURE 8B.
- a portion 78 of the proximal end of the nitinol hypotube 75 is fitted into the distal end of the stainless steel tube 70 and a joint 74 can be formed as in the manner shown in Figure 8B.
- the joint material such as solder or adhesives, can be applied through one or more holes 72 that are previously formed at the distal end of the stainless steel tubing 70.
- the outer surface of the fitting end 78 of the hypotube may be modified as shown, or in other ways. Alternatively, crimping or press fitting may be also applied to join materials.
- the stainless steel hypotube 75 may be disposed concentrically about the Ni-Ti hypotube 70.
- the stainless steel hypotube is sealingly secured about the periphery of the Ni-Ti hypotube 75 by using suitable adhesives.
- the component sections of the composite wire may have equal or approximately equal diameters. In other cases, one section may have a diameter greater than the other.
- a composite guidewire may be constructed so as to have a proximal section OD of 0.035" or 0.018" (to allow certain therapy devices to ride thereover more efficiently) and a distal section of .014" (to provide a narrow profile to cross the lesion).
- the hollow guidewire of the present invention can be advantageously used to deliver fluids for specific medical applications including coronary and neurological applications. During the course of such applications, it is often essential to deliver fluids to specific locations within the body.
- This fluid delivery is carried out using irrigation catheters.
- irrigation catheters serve as passage ways for delivery of fluids comprising either a contrast media to permit X-ray detection or other media to achieve localized drug therapy.
- this fluid may also comprise a fluid, such as saline, to inflate the balloon.
- FIGURE 9A illustrates a preferred embodiment of an irrigation catheter 80A constructed from superelastic nitinol hollow wire of the present invention.
- the irrigation catheter 80A is comprised of an hypotube 81 and a coil member 82.
- the hypotube 81 is provided with proximal and distal ends 81A and 81B and as well as a lumen 84 extending along the hypotube 81 and thereby providing a fluid passage way.
- the coil member 82 of the catheter 80A is joined to the distal end 81 B of the hypotube 81 as in the manner shown in FIGURE 9A.
- the distal end 81 B of the hypotube 81 may also include one or more perforations 85 thereof so that fluids can be delivered into or received from the desired body locations.
- gaps between the coil turns 86 also provide an effective passage way to deliver or receive fluids through coil member 82. Therefore, in this embodiment, perforations 85 at the distal end 81A of the hypotube 81 are optional so that the fluid may exit or enter the catheter 80A from the coil member 82.
- the catheter 80A of the present invention can be used for delivering drugs to the distal body locations, the catheter 80A can also be used in those applications where irrigation and aspiration are necessary for emboli removal.
- the outer diameter of this irrigation catheter must be 0.38" or smaller.
- FIGURE 9B shows a second embodiment of the present invention which comprises a multilumen irrigation catheter 80B.
- a portion of the catheter 80B comprising the hypotube 81 and the coil member 82 is configured similar to that of first embodiment.
- the present embodiment also comprises a balloon member 88 and a conduit 90.
- the conduit 90 is preferably disposed along the inner iumen 84 of the hypotube 81.
- the balloon member 88 is coaxially mounted on the distal end 81B of the hypotube 81 as in the manner shown in FIGURE 9B.
- the conduit 90 is provided with distal and proximal ends 90A and 90B as well as an inner Iumen 91.
- the proximal end 90A of the conduit is preferably connected to a gas source (not shown), while the distal end 90B is connected to the balloon member 88 through an inlet port 92 in the distal end 81 B of the hypotube 80.
- the distal end 90B of the conduit 90 and the inlet port 92 are seaiabiy connected to each other by suitable means such as adhesive to avoid any gas leak.
- the inner iumen 91 of the conduit 90 connects the gas source to the balloon member 88 so that the gas from the gas source can inflate the balloon member 88.
- the conduit 90 is preferably made of a flexible material such as polymide, poiyamide, or the like alloy and is in the form of hypotubing.
- the outer diameter of the conduit 90 is significantly smaller than the inner diameter of the Iumen 84 of the hypotube 81 so that fluid in the Iumen 84 can flow without any restriction.
- carbon dioxide (C0 2 ) gas is preferably employed to inflate balloon member 88.
- (C0 2 ) gas easily dissolves in blood and does not cause any harm in the patient's body, if an accidental leak occurs.
- the balloon member may be inflated using any of a number of harmless gases or fluids, or possible combinations thereof.
- FIGURE 9C shows a third embodiment of the present invention which comprises another single Iumen catheter 80C as in the case of first embodiment.
- a portion of the catheter 80C comprising the hypotube 81 and the coil member 82 is also configured similar to that of first embodiment.
- the present embodiment also comprises a balloon member 88.
- the balloon member 88 is coaxially mounted on the distal end 81 B of the hypotube 81 as in the manner shown in FIGURE 9B.
- Fill holes 93 are provided in the wall of the distal end 81 of the hypotube 81 along the section of hypotube enclosed within the balloon member 88. During the application, these fill holes 93 allow the passage of irrigation fluid into the balloon member 88. As the fluid pressure reaches up to inflation pressure of the balloon member 88, the balloon member is inflated.
- An exemplary inflation pressure range for the occlusion balloons can be given as 40 psi. However, for the therapeutic balloons, such pressure range can be as high as 200 psi.
- a number of valve members are also provided over the inner wall of the distal end 81 of the hypotube 81. The valve members are attached over the perforations 85 as in the manner shown in FIGURE 9C.
- the valve members 94 are comprised of elastomeric membranes. These membranes 94 can be configured and dimensioned to withstand some threshold fluid pressure, such as the inflation pressure of the balloon member 88.
- any pressure over this threshold pressure breaks open these membranes 94, i.e., activates valves 94, and delivers the irrigation fluid, through perforations 85, into the body locations.
- the fluid delivery can be also provided through leakages from both optional the slits (not shown) in the balloon member 88 and the gaps between the coil turns 86.
- the catheter 80C can be advantageously used for occlusion and irrigation therapies.
Abstract
Description
Claims
Priority Applications (4)
Application Number | Priority Date | Filing Date | Title |
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JP53888898A JP2001514544A (en) | 1997-03-06 | 1998-03-06 | Hollow medical wire and method of constructing the same |
EP98909033A EP0996480A2 (en) | 1997-03-06 | 1998-03-06 | Hollow medical wires and methods of constructing same |
AU66916/98A AU6691698A (en) | 1997-03-06 | 1998-03-06 | Hollow medical wires and methods of constructing same |
CA002287072A CA2287072A1 (en) | 1997-03-06 | 1998-03-06 | Hollow medical wires and methods of constructing same |
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US08/812,876 US6068623A (en) | 1997-03-06 | 1997-03-06 | Hollow medical wires and methods of constructing same |
US08/812,876 | 1997-03-06 |
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WO1998039048A2 true WO1998039048A2 (en) | 1998-09-11 |
WO1998039048A3 WO1998039048A3 (en) | 1998-12-03 |
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PCT/US1998/004500 WO1998039048A2 (en) | 1997-03-06 | 1998-03-06 | Hollow medical wires and methods of constructing same |
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US (4) | US6068623A (en) |
EP (1) | EP0996480A2 (en) |
JP (1) | JP2001514544A (en) |
AU (1) | AU6691698A (en) |
CA (1) | CA2287072A1 (en) |
WO (1) | WO1998039048A2 (en) |
Cited By (19)
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---|---|---|---|---|
WO1999026692A1 (en) | 1997-11-20 | 1999-06-03 | Percusurge, Inc. | Low profile catheter valve and inflation adaptor |
WO2000050113A2 (en) | 1999-02-22 | 2000-08-31 | Percusurge, Inc. | Balloon catheter with axial flexibility |
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WO2007059277A1 (en) * | 2005-11-16 | 2007-05-24 | William Cook Europe Aps | Cannula |
US7763012B2 (en) | 2003-09-02 | 2010-07-27 | St. Jude Medical, Cardiology Division, Inc. | Devices and methods for crossing a chronic total occlusion |
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US9713475B2 (en) | 2014-04-18 | 2017-07-25 | Covidien Lp | Embolic medical devices |
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Families Citing this family (296)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6682608B2 (en) * | 1990-12-18 | 2004-01-27 | Advanced Cardiovascular Systems, Inc. | Superelastic guiding member |
US20030069522A1 (en) * | 1995-12-07 | 2003-04-10 | Jacobsen Stephen J. | Slotted medical device |
US6958059B2 (en) | 1996-05-20 | 2005-10-25 | Medtronic Ave, Inc. | Methods and apparatuses for drug delivery to an intravascular occlusion |
US6544276B1 (en) * | 1996-05-20 | 2003-04-08 | Medtronic Ave. Inc. | Exchange method for emboli containment |
US6270477B1 (en) * | 1996-05-20 | 2001-08-07 | Percusurge, Inc. | Catheter for emboli containment |
US6068623A (en) * | 1997-03-06 | 2000-05-30 | Percusurge, Inc. | Hollow medical wires and methods of constructing same |
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US6905505B2 (en) * | 1996-07-26 | 2005-06-14 | Kensey Nash Corporation | System and method of use for agent delivery and revascularizing of grafts and vessels |
US6652546B1 (en) * | 1996-07-26 | 2003-11-25 | Kensey Nash Corporation | System and method of use for revascularizing stenotic bypass grafts and other occluded blood vessels |
US5779721A (en) | 1996-07-26 | 1998-07-14 | Kensey Nash Corporation | System and method of use for revascularizing stenotic bypass grafts and other blood vessels |
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US6080170A (en) * | 1996-07-26 | 2000-06-27 | Kensey Nash Corporation | System and method of use for revascularizing stenotic bypass grafts and other occluded blood vessels |
US9586023B2 (en) | 1998-02-06 | 2017-03-07 | Boston Scientific Limited | Direct stream hydrodynamic catheter system |
US9254143B2 (en) * | 1998-02-25 | 2016-02-09 | Revascular Therapeutics, Inc. | Guidewire for crossing occlusions or stenoses having a shapeable distal end |
US6824550B1 (en) | 2000-04-06 | 2004-11-30 | Norbon Medical, Inc. | Guidewire for crossing occlusions or stenosis |
US20080140101A1 (en) * | 2006-12-07 | 2008-06-12 | Revascular Therapeutic, Inc. | Apparatus for crossing occlusions or stenoses |
US20060074442A1 (en) * | 2000-04-06 | 2006-04-06 | Revascular Therapeutics, Inc. | Guidewire for crossing occlusions or stenoses |
US20070225615A1 (en) * | 2006-03-22 | 2007-09-27 | Revascular Therapeutics Inc. | Guidewire controller system |
US7645242B1 (en) * | 1998-12-31 | 2010-01-12 | Advanced Cardiovascular Systems, Inc. | Composite guidewire with drawn and filled tube construction |
US7717864B1 (en) | 1998-12-31 | 2010-05-18 | Advanced Cardiovascular Systems, Inc. | Composite guidewire with drawn and filled tube construction |
US6485507B1 (en) * | 1999-07-28 | 2002-11-26 | Scimed Life Systems | Multi-property nitinol by heat treatment |
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US6468262B1 (en) * | 1999-12-02 | 2002-10-22 | Embol-X, Inc. | Buoyant tip aspiration catheter and methods of use |
US6443926B1 (en) | 2000-02-01 | 2002-09-03 | Harold D. Kletschka | Embolic protection device having expandable trap |
US7322957B2 (en) * | 2000-02-01 | 2008-01-29 | Harold D. Kletschka | Angioplasty device and method of making same |
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AU2001238155A1 (en) | 2000-02-11 | 2001-08-20 | Percusurge, Inc. | Intravascular device for filtering emboli |
US6755794B2 (en) | 2000-04-25 | 2004-06-29 | Synovis Life Technologies, Inc. | Adjustable stylet |
CA2410971C (en) * | 2000-05-31 | 2007-12-18 | Brian K. Courtney | Embolization protection system for vascular procedures |
US8435225B2 (en) * | 2000-06-02 | 2013-05-07 | Fox Hollow Technologies, Inc. | Embolization protection system for vascular procedures |
DE60117796T2 (en) * | 2000-06-16 | 2006-11-30 | Abbott Laboratories, Abbott Park | BALLOONCLUSION DEVICE WITH A PROXIMAL VALVE |
US7101391B2 (en) * | 2000-09-18 | 2006-09-05 | Inflow Dynamics Inc. | Primarily niobium stent |
US7402173B2 (en) * | 2000-09-18 | 2008-07-22 | Boston Scientific Scimed, Inc. | Metal stent with surface layer of noble metal oxide and method of fabrication |
US6500185B1 (en) | 2000-09-29 | 2002-12-31 | Primus Medical, Inc. | Snare device |
US6685720B1 (en) * | 2000-10-16 | 2004-02-03 | Interventional Technologies | Catheter having improved shaped retention |
US7976648B1 (en) | 2000-11-02 | 2011-07-12 | Abbott Cardiovascular Systems Inc. | Heat treatment for cold worked nitinol to impart a shape setting capability without eventually developing stress-induced martensite |
US6602272B2 (en) * | 2000-11-02 | 2003-08-05 | Advanced Cardiovascular Systems, Inc. | Devices configured from heat shaped, strain hardened nickel-titanium |
US6626937B1 (en) | 2000-11-14 | 2003-09-30 | Advanced Cardiovascular Systems, Inc. | Austenitic nitinol medical devices |
US6638267B1 (en) | 2000-12-01 | 2003-10-28 | Advanced Cardiovascular Systems, Inc. | Guidewire with hypotube and internal insert |
US7128757B2 (en) * | 2000-12-27 | 2006-10-31 | Advanced Cardiovascular, Inc. | Radiopaque and MRI compatible nitinol alloys for medical devices |
US20060086440A1 (en) * | 2000-12-27 | 2006-04-27 | Boylan John F | Nitinol alloy design for improved mechanical stability and broader superelastic operating window |
US6855161B2 (en) * | 2000-12-27 | 2005-02-15 | Advanced Cardiovascular Systems, Inc. | Radiopaque nitinol alloys for medical devices |
US20030163128A1 (en) * | 2000-12-29 | 2003-08-28 | Afx, Inc. | Tissue ablation system with a sliding ablating device and method |
US6428559B1 (en) | 2001-04-03 | 2002-08-06 | Cordis Corporation | Removable, variable-diameter vascular filter system |
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US6636758B2 (en) | 2001-05-01 | 2003-10-21 | Concentric Medical, Inc. | Marker wire and process for using it |
US6635070B2 (en) | 2001-05-21 | 2003-10-21 | Bacchus Vascular, Inc. | Apparatus and methods for capturing particulate material within blood vessels |
US20030208142A1 (en) * | 2001-06-12 | 2003-11-06 | Boudewijn Alexander C | Vascular guidewire for magnetic resonance and /or fluoroscopy |
US6551341B2 (en) * | 2001-06-14 | 2003-04-22 | Advanced Cardiovascular Systems, Inc. | Devices configured from strain hardened Ni Ti tubing |
US6638245B2 (en) | 2001-06-26 | 2003-10-28 | Concentric Medical, Inc. | Balloon catheter |
US6702782B2 (en) | 2001-06-26 | 2004-03-09 | Concentric Medical, Inc. | Large lumen balloon catheter |
US6962598B2 (en) * | 2001-07-02 | 2005-11-08 | Rubicon Medical, Inc. | Methods, systems, and devices for providing embolic protection |
US6878153B2 (en) * | 2001-07-02 | 2005-04-12 | Rubicon Medical, Inc. | Methods, systems, and devices for providing embolic protection and removing embolic material |
US6951570B2 (en) * | 2001-07-02 | 2005-10-04 | Rubicon Medical, Inc. | Methods, systems, and devices for deploying a filter from a filter device |
US6997939B2 (en) * | 2001-07-02 | 2006-02-14 | Rubicon Medical, Inc. | Methods, systems, and devices for deploying an embolic protection filter |
ATE347393T1 (en) * | 2001-07-05 | 2006-12-15 | Precision Vascular Systems Inc | MEDICAL DEVICE HAVING A TORQUE-TRANSMITTING SOFT END PIECE AND METHOD FOR SHAPING IT |
JP4326942B2 (en) * | 2001-07-17 | 2009-09-09 | フォックス・ホロー・テクノロジーズ・インコーポレーテッド | Liquid exchange system for local irrigation and aspiration with controlled liquid volume |
US6656203B2 (en) | 2001-07-18 | 2003-12-02 | Cordis Corporation | Integral vascular filter system |
US6776765B2 (en) | 2001-08-21 | 2004-08-17 | Synovis Life Technologies, Inc. | Steerable stylet |
US7669799B2 (en) * | 2001-08-24 | 2010-03-02 | University Of Virginia Patent Foundation | Reversible shape memory multifunctional structural designs and method of using and making the same |
US20030048256A1 (en) * | 2001-09-07 | 2003-03-13 | Salmon Peter C. | Computing device with roll up components |
US7175655B1 (en) | 2001-09-17 | 2007-02-13 | Endovascular Technologies, Inc. | Avoiding stress-induced martensitic transformation in nickel titanium alloys used in medical devices |
US20030088195A1 (en) * | 2001-11-02 | 2003-05-08 | Vardi Gil M | Guidewire having measurement indicia |
US20030088240A1 (en) * | 2001-11-02 | 2003-05-08 | Vahid Saadat | Methods and apparatus for cryo-therapy |
US6942678B2 (en) * | 2001-11-06 | 2005-09-13 | Possis Medical, Inc. | Gas inflation/evacuation system and sealing system for guidewire assembly having occlusive device |
US7169161B2 (en) | 2001-11-06 | 2007-01-30 | Possis Medical, Inc. | Guidewire having occlusive device and repeatably crimpable proximal end |
US20060064071A1 (en) * | 2001-11-06 | 2006-03-23 | Possis Medical, Inc. | Gas inflation/evacuation system incorporating a reservoir and removably attached sealing system for a guidewire assembly having an occlusive device |
US6932828B2 (en) | 2001-11-06 | 2005-08-23 | Possis Medical, Inc. | Guidewire occlusion system utilizing repeatably inflatable gas-filled occlusive device |
US7520863B2 (en) * | 2002-03-22 | 2009-04-21 | Cordis Corporation | Guidewire with deflectable tip having improved torque characteristics |
US20070219464A1 (en) * | 2002-03-22 | 2007-09-20 | Stephen Davis | Guidewire with deflectable re-entry tip |
US20070213689A1 (en) * | 2002-03-22 | 2007-09-13 | Grewe David D | Deflectable tip infusion guidewire |
US7128718B2 (en) * | 2002-03-22 | 2006-10-31 | Cordis Corporation | Guidewire with deflectable tip |
US7351214B2 (en) * | 2002-03-22 | 2008-04-01 | Cordis Corporation | Steerable balloon catheter |
US7815600B2 (en) * | 2002-03-22 | 2010-10-19 | Cordis Corporation | Rapid-exchange balloon catheter shaft and method |
US7481778B2 (en) * | 2002-03-22 | 2009-01-27 | Cordis Corporation | Guidewire with deflectable tip having improved flexibility |
US20040147903A1 (en) * | 2002-04-05 | 2004-07-29 | Lucas Latini | Microcatheter having tip relief region |
US7959584B2 (en) * | 2002-05-29 | 2011-06-14 | Boston Scientific Scimed, Inc. | Dedicated distal protection guidewires |
US20030225434A1 (en) * | 2002-05-30 | 2003-12-04 | Jerald Glantz | Microcatheter |
EP1531983A1 (en) * | 2002-05-30 | 2005-05-25 | University Of Virginia Patent Foundation | Active energy absorbing cellular metals and method of manufacturing and using the same |
DE10258702A1 (en) * | 2002-06-21 | 2004-01-08 | Curative Medical Devices Gmbh | Catheter arrangement has distal and proximal catheters with lumen, bendable distal point, side slit and guide wire |
US6887258B2 (en) * | 2002-06-26 | 2005-05-03 | Advanced Cardiovascular Systems, Inc. | Embolic filtering devices for bifurcated vessels |
US7914467B2 (en) | 2002-07-25 | 2011-03-29 | Boston Scientific Scimed, Inc. | Tubular member having tapered transition for use in a medical device |
JP4602080B2 (en) * | 2002-07-25 | 2010-12-22 | ボストン サイエンティフィック リミテッド | Medical devices that travel through the human body structure |
US7309318B2 (en) * | 2002-09-18 | 2007-12-18 | Boston Scientific Scimed, Inc. | Flexible composite guidewire for intravascular catheter |
WO2004033016A1 (en) * | 2002-10-04 | 2004-04-22 | Advanced Cardiovascular Systems, Inc. | Radiopaque nitinol alloys for medical devices |
US20060241366A1 (en) * | 2002-10-31 | 2006-10-26 | Gary Falwell | Electrophysiology loop catheter |
US20040102719A1 (en) * | 2002-11-22 | 2004-05-27 | Velocimed, L.L.C. | Guide wire control catheters for crossing occlusions and related methods of use |
US20040116831A1 (en) * | 2002-12-13 | 2004-06-17 | Scimed Life Systems, Inc. | Distal protection guidewire with nitinol core |
US7077811B2 (en) * | 2002-12-23 | 2006-07-18 | Scimed Life Systems, Inc. | Guidewire tip construction |
US20040143286A1 (en) * | 2003-01-17 | 2004-07-22 | Johnson Eric G. | Catheter with disruptable guidewire channel |
US8377035B2 (en) | 2003-01-17 | 2013-02-19 | Boston Scientific Scimed, Inc. | Unbalanced reinforcement members for medical device |
US7169118B2 (en) * | 2003-02-26 | 2007-01-30 | Scimed Life Systems, Inc. | Elongate medical device with distal cap |
US8167821B2 (en) * | 2003-02-26 | 2012-05-01 | Boston Scientific Scimed, Inc. | Multiple diameter guidewire |
US20040167438A1 (en) * | 2003-02-26 | 2004-08-26 | Sharrow James S. | Reinforced medical device |
US20040167439A1 (en) * | 2003-02-26 | 2004-08-26 | Sharrow James S. | Guidewire having textured proximal portion |
US20040167437A1 (en) * | 2003-02-26 | 2004-08-26 | Sharrow James S. | Articulating intracorporal medical device |
US7001369B2 (en) | 2003-03-27 | 2006-02-21 | Scimed Life Systems, Inc. | Medical device |
US20040199052A1 (en) | 2003-04-01 | 2004-10-07 | Scimed Life Systems, Inc. | Endoscopic imaging system |
US7303533B2 (en) * | 2003-04-10 | 2007-12-04 | Intraluminal Therapeutics, Inc. | Shapeable intraluminal device and method therefor |
US7582740B2 (en) * | 2003-04-17 | 2009-09-01 | The Trustees Of Columbia University In The City Of New York | Methods and kits for detecting SARS-associated coronavirus |
US7591832B2 (en) * | 2003-04-24 | 2009-09-22 | Medtronic, Inc. | Expandable guide sheath and apparatus with distal protection and methods for use |
US8388628B2 (en) * | 2003-04-24 | 2013-03-05 | Medtronic, Inc. | Expandable sheath for delivering instruments and agents into a body lumen and methods for use |
US7942892B2 (en) * | 2003-05-01 | 2011-05-17 | Abbott Cardiovascular Systems Inc. | Radiopaque nitinol embolic protection frame |
US7789979B2 (en) * | 2003-05-02 | 2010-09-07 | Gore Enterprise Holdings, Inc. | Shape memory alloy articles with improved fatigue performance and methods therefor |
US7632288B2 (en) | 2003-05-12 | 2009-12-15 | Boston Scientific Scimed, Inc. | Cutting balloon catheter with improved pushability |
US20060286342A1 (en) * | 2003-05-28 | 2006-12-21 | Elzey Dana M | Re-entrant cellular multifunctional structure for energy absorption and method of manufacturing and using the same |
US7758604B2 (en) | 2003-05-29 | 2010-07-20 | Boston Scientific Scimed, Inc. | Cutting balloon catheter with improved balloon configuration |
JP4141336B2 (en) * | 2003-06-26 | 2008-08-27 | 朝日インテック株式会社 | Manufacturing method of medical guide wire |
US20050004594A1 (en) * | 2003-07-02 | 2005-01-06 | Jeffrey Nool | Devices and methods for aspirating from filters |
US7780626B2 (en) | 2003-08-08 | 2010-08-24 | Boston Scientific Scimed, Inc. | Catheter shaft for regulation of inflation and deflation |
US7887557B2 (en) * | 2003-08-14 | 2011-02-15 | Boston Scientific Scimed, Inc. | Catheter having a cutting balloon including multiple cavities or multiple channels |
US7455737B2 (en) * | 2003-08-25 | 2008-11-25 | Boston Scientific Scimed, Inc. | Selective treatment of linear elastic materials to produce localized areas of superelasticity |
WO2005020912A2 (en) * | 2003-08-25 | 2005-03-10 | 3M Innovative Properties Company | Delivery of immune response modifier compounds |
US7699865B2 (en) * | 2003-09-12 | 2010-04-20 | Rubicon Medical, Inc. | Actuating constraining mechanism |
US8535344B2 (en) | 2003-09-12 | 2013-09-17 | Rubicon Medical, Inc. | Methods, systems, and devices for providing embolic protection and removing embolic material |
JP4691640B2 (en) * | 2003-10-03 | 2011-06-01 | メドトロニック,インコーポレイテッド | Inflatable sheath and device and method of manufacturing the same |
US7824345B2 (en) | 2003-12-22 | 2010-11-02 | Boston Scientific Scimed, Inc. | Medical device with push force limiter |
AU2005206767B2 (en) | 2004-01-09 | 2009-09-17 | Corazon Technologies, Inc. | Multilumen catheters and methods for their use |
US20050159728A1 (en) * | 2004-01-15 | 2005-07-21 | Thomas Medical Products, Inc. | Steerable sheath |
US20050197597A1 (en) * | 2004-03-05 | 2005-09-08 | Medtronic Vascular, Inc. | Guidewire with hollow distal section |
EP1727585B1 (en) * | 2004-03-17 | 2010-10-13 | Cook Incorporated | Second wire apparatus and installation procedure |
US7754047B2 (en) | 2004-04-08 | 2010-07-13 | Boston Scientific Scimed, Inc. | Cutting balloon catheter and method for blade mounting |
US7566319B2 (en) | 2004-04-21 | 2009-07-28 | Boston Scientific Scimed, Inc. | Traction balloon |
US8239002B2 (en) * | 2004-08-12 | 2012-08-07 | Novatek Medical Ltd. | Guiding a tool for medical treatment by detecting a source of radioactivity |
EP1805506A4 (en) | 2004-08-12 | 2010-06-02 | Navotek Medical Ltd | Localization of a radioactive source within a body of a subject |
US7952079B2 (en) * | 2004-08-12 | 2011-05-31 | Navotek Medical Ltd. | Localization of a radioactive source |
DE102004040868A1 (en) | 2004-08-23 | 2006-03-09 | Miloslavski, Elina | Device for removing thrombi |
US7993350B2 (en) | 2004-10-04 | 2011-08-09 | Medtronic, Inc. | Shapeable or steerable guide sheaths and methods for making and using them |
EP1804659A4 (en) * | 2004-10-19 | 2010-11-03 | Navotek Medical Ltd | Locating a catheter tip using a tracked guide |
US20060089569A1 (en) * | 2004-10-26 | 2006-04-27 | Soukup Thomas M | Articulator with adjustable stiffness distal portion |
US7291158B2 (en) * | 2004-11-12 | 2007-11-06 | Boston Scientific Scimed, Inc. | Cutting balloon catheter having a segmented blade |
US8038691B2 (en) | 2004-11-12 | 2011-10-18 | Boston Scientific Scimed, Inc. | Cutting balloon catheter having flexible atherotomes |
US7632242B2 (en) * | 2004-12-09 | 2009-12-15 | Boston Scientific Scimed, Inc. | Catheter including a compliant balloon |
US20090209987A1 (en) * | 2005-02-01 | 2009-08-20 | Mathews Eric D | Snare with capture-area enhancement |
JP2008532576A (en) * | 2005-02-02 | 2008-08-21 | ピーコック,ジェイムズ,シー | Complete vascular occlusion treatment system and method |
US20060184191A1 (en) * | 2005-02-11 | 2006-08-17 | Boston Scientific Scimed, Inc. | Cutting balloon catheter having increased flexibility regions |
US20060229638A1 (en) * | 2005-03-29 | 2006-10-12 | Abrams Robert M | Articulating retrieval device |
AT501283B8 (en) * | 2005-05-10 | 2007-02-15 | Hans-Peter Dr Steiner | DEVICE FOR UTERIN EMBRYO TRANSFER |
US7901367B2 (en) * | 2005-06-30 | 2011-03-08 | Cook Incorporated | Wire guide advancement system |
ATE555737T1 (en) * | 2005-08-11 | 2012-05-15 | Navotek Medical Ltd | LOCALIZATION OF A RADIOACTIVE SOURCE |
US8075497B2 (en) * | 2005-08-25 | 2011-12-13 | Cook Medical Technologies Llc | Wire guide having distal coupling tip |
US9005138B2 (en) * | 2005-08-25 | 2015-04-14 | Cook Medical Technologies Llc | Wire guide having distal coupling tip |
US7615031B2 (en) * | 2005-09-01 | 2009-11-10 | Medrad, Inc. | Gas inflation/evacuation system incorporating a multiple element valved guidewire assembly having an occlusive device |
US20070060878A1 (en) | 2005-09-01 | 2007-03-15 | Possis Medical, Inc. | Occlusive guidewire system having an ergonomic handheld control mechanism and torqueable kink-resistant guidewire |
US8608703B2 (en) | 2007-06-12 | 2013-12-17 | Medrad, Inc. | Infusion flow guidewire system |
US20080097294A1 (en) * | 2006-02-21 | 2008-04-24 | Possis Medical, Inc. | Occlusive guidewire system having an ergonomic handheld control mechanism prepackaged in a pressurized gaseous environment and a compatible prepackaged torqueable kink-resistant guidewire with distal occlusive balloon |
US7758565B2 (en) * | 2005-10-18 | 2010-07-20 | Cook Incorporated | Identifiable wire guide |
US8137291B2 (en) * | 2005-10-27 | 2012-03-20 | Cook Medical Technologies Llc | Wire guide having distal coupling tip |
US7850623B2 (en) | 2005-10-27 | 2010-12-14 | Boston Scientific Scimed, Inc. | Elongate medical device with continuous reinforcement member |
US7731693B2 (en) * | 2005-10-27 | 2010-06-08 | Cook Incorporated | Coupling wire guide |
US20070106245A1 (en) * | 2005-11-08 | 2007-05-10 | Kerberos Proximal Solutions, Inc. | Infusion guidewire |
DE602006009545D1 (en) * | 2005-11-16 | 2009-11-12 | William Cook Europe As | FAST EXCHANGEABLE BALLOON CATHETER AND MANUFACTURING METHOD THEREFOR |
US8162878B2 (en) | 2005-12-05 | 2012-04-24 | Medrad, Inc. | Exhaust-pressure-operated balloon catheter system |
US7892186B2 (en) | 2005-12-09 | 2011-02-22 | Heraeus Materials S.A. | Handle and articulator system and method |
JP2009523481A (en) * | 2006-01-12 | 2009-06-25 | ミネソタ メディカル ディベロップメント、インコーポレイテッド | Titanium / molybdenum alloy guide wire |
US7811238B2 (en) | 2006-01-13 | 2010-10-12 | Cook Incorporated | Wire guide having distal coupling tip |
US20070167877A1 (en) * | 2006-01-17 | 2007-07-19 | Euteneuer Charles L | Medical catheters and methods |
US20070167972A1 (en) * | 2006-01-17 | 2007-07-19 | Euteneuer Charles L | Balloon apparatus and methods |
US20070167876A1 (en) * | 2006-01-17 | 2007-07-19 | Euteneuer Charles L | Occluding guidewire and methods |
TWI285543B (en) * | 2006-01-24 | 2007-08-21 | Everest Display Inc | Capsule laparoscope having a mechanism of direction control and releasing |
US7798980B2 (en) * | 2006-01-31 | 2010-09-21 | Cook Incorporated | Wire guide having distal coupling tip for attachment to a previously introduced wire guide |
US7785275B2 (en) | 2006-01-31 | 2010-08-31 | Cook Incorporated | Wire guide having distal coupling tip |
US20070191790A1 (en) * | 2006-02-16 | 2007-08-16 | Cook Incorporated | Wire guide having distal coupling tip |
US7785317B2 (en) * | 2006-03-29 | 2010-08-31 | Codman & Shurtleff, Inc. | Joined metal tubing and method of manufacture |
US9757260B2 (en) | 2006-03-30 | 2017-09-12 | Medtronic Vascular, Inc. | Prosthesis with guide lumen |
US8777979B2 (en) | 2006-04-17 | 2014-07-15 | Covidien Lp | System and method for mechanically positioning intravascular implants |
CN101448464B (en) | 2006-04-17 | 2011-05-04 | 微治疗公司 | System and method for mechanically positioning intravascular implants |
US8932348B2 (en) | 2006-05-18 | 2015-01-13 | Edwards Lifesciences Corporation | Device and method for improving heart valve function |
WO2007139814A2 (en) | 2006-05-23 | 2007-12-06 | University Of Virginia Patent Foundation | Method and apparatus for jet blast deflection |
EP2032080B1 (en) | 2006-06-01 | 2017-05-03 | Edwards Lifesciences Corporation | Prosthetic insert for improving heart valve function |
US8133190B2 (en) * | 2006-06-22 | 2012-03-13 | Cook Medical Technologies Llc | Weldable wire guide with distal coupling tip |
US9867530B2 (en) | 2006-08-14 | 2018-01-16 | Volcano Corporation | Telescopic side port catheter device with imaging system and method for accessing side branch occlusions |
US8728010B2 (en) * | 2006-08-24 | 2014-05-20 | Boston Scientific Scimed, Inc. | Elongate medical device including deformable distal end |
JP2010503484A (en) | 2006-09-13 | 2010-02-04 | ボストン サイエンティフィック リミテッド | Transverse guide wire |
US20080119762A1 (en) * | 2006-11-16 | 2008-05-22 | Tateishi Tadasu | Guide wire |
US8556914B2 (en) | 2006-12-15 | 2013-10-15 | Boston Scientific Scimed, Inc. | Medical device including structure for crossing an occlusion in a vessel |
CA2680793C (en) | 2007-03-13 | 2015-07-07 | Microtherapeutics, Inc. | An implant, a mandrel, and a method of forming an implant |
US8622991B2 (en) * | 2007-03-19 | 2014-01-07 | Insuline Medical Ltd. | Method and device for drug delivery |
US9220837B2 (en) | 2007-03-19 | 2015-12-29 | Insuline Medical Ltd. | Method and device for drug delivery |
CN104069567A (en) | 2007-03-19 | 2014-10-01 | 茵苏莱恩医药有限公司 | Drug delivery device |
US20080262474A1 (en) * | 2007-04-20 | 2008-10-23 | Boston Scientific Scimed, Inc. | Medical device |
US8974418B2 (en) * | 2007-06-12 | 2015-03-10 | Boston Scientific Limited | Forwardly directed fluid jet crossing catheter |
US20080319386A1 (en) * | 2007-06-20 | 2008-12-25 | Possis Medical, Inc. | Forwardly directable fluid jet crossing catheter |
WO2009009802A1 (en) * | 2007-07-12 | 2009-01-15 | Volcano Corporation | Oct-ivus catheter for concurrent luminal imaging |
US9596993B2 (en) | 2007-07-12 | 2017-03-21 | Volcano Corporation | Automatic calibration systems and methods of use |
WO2009009799A1 (en) * | 2007-07-12 | 2009-01-15 | Volcano Corporation | Catheter for in vivo imaging |
US8409114B2 (en) * | 2007-08-02 | 2013-04-02 | Boston Scientific Scimed, Inc. | Composite elongate medical device including distal tubular member |
US20090036832A1 (en) * | 2007-08-03 | 2009-02-05 | Boston Scientific Scimed, Inc. | Guidewires and methods for manufacturing guidewires |
US8105246B2 (en) * | 2007-08-03 | 2012-01-31 | Boston Scientific Scimed, Inc. | Elongate medical device having enhanced torque and methods thereof |
US8821477B2 (en) | 2007-08-06 | 2014-09-02 | Boston Scientific Scimed, Inc. | Alternative micromachined structures |
US9808595B2 (en) * | 2007-08-07 | 2017-11-07 | Boston Scientific Scimed, Inc | Microfabricated catheter with improved bonding structure |
US7841994B2 (en) | 2007-11-02 | 2010-11-30 | Boston Scientific Scimed, Inc. | Medical device for crossing an occlusion in a vessel |
US8303538B2 (en) | 2007-12-17 | 2012-11-06 | Medrad, Inc. | Rheolytic thrombectomy catheter with self-inflating distal balloon |
EP2231229A1 (en) | 2007-12-18 | 2010-09-29 | Insuline Medical Ltd. | Drug delivery device with sensor for closed-loop operation |
US8636270B2 (en) * | 2007-12-19 | 2014-01-28 | Boston Scientific Scimed, Inc. | Structure for use as part of a medical device |
EP2227285A4 (en) | 2007-12-26 | 2013-07-31 | Medrad Inc | Rheolytic thrombectomy catheter with self-inflating proximal balloon with drug infusion capabilities |
WO2009094511A1 (en) * | 2008-01-24 | 2009-07-30 | Boston Scientific Scimed, Inc. | Structure for use as part of a medical device |
US8647294B2 (en) | 2008-03-20 | 2014-02-11 | Medrad, Inc. | Direct stream hydrodynamic catheter system |
WO2009120622A1 (en) * | 2008-03-24 | 2009-10-01 | Boston Scientific Scimed, Inc. | Flexible endoscope with core member |
US8376961B2 (en) | 2008-04-07 | 2013-02-19 | Boston Scientific Scimed, Inc. | Micromachined composite guidewire structure with anisotropic bending properties |
US20090299171A1 (en) * | 2008-06-03 | 2009-12-03 | Medtronic Vascular, Inc. | Intraluminal Access and Imaging Device |
EP2156806A1 (en) * | 2008-08-18 | 2010-02-24 | Navotek Medical Ltd. | Implantation device for soft tissue markers and other implants |
US8535243B2 (en) | 2008-09-10 | 2013-09-17 | Boston Scientific Scimed, Inc. | Medical devices and tapered tubular members for use in medical devices |
US8414714B2 (en) | 2008-10-31 | 2013-04-09 | Fort Wayne Metals Research Products Corporation | Method for imparting improved fatigue strength to wire made of shape memory alloys, and medical devices made from such wire |
MX2011004817A (en) | 2008-11-07 | 2011-07-28 | Insuline Medical Ltd | Device and method for drug delivery. |
US8657821B2 (en) * | 2008-11-14 | 2014-02-25 | Revascular Therapeutics Inc. | Method and system for reversibly controlled drilling of luminal occlusions |
US8162891B2 (en) * | 2008-11-26 | 2012-04-24 | Revascular Therapeutics, Inc. | Delivery and exchange catheter for storing guidewire |
US8795254B2 (en) | 2008-12-10 | 2014-08-05 | Boston Scientific Scimed, Inc. | Medical devices with a slotted tubular member having improved stress distribution |
US20100152711A1 (en) * | 2008-12-15 | 2010-06-17 | Boston Scientific Scimed, Inc. | Offset coupling region |
US8444669B2 (en) | 2008-12-15 | 2013-05-21 | Boston Scientific Scimed, Inc. | Embolic filter delivery system and method |
US20170202657A1 (en) | 2009-01-16 | 2017-07-20 | Claret Medical, Inc. | Intravascular blood filters and methods of use |
WO2010083527A2 (en) * | 2009-01-16 | 2010-07-22 | Claret Medical, Inc. | Intravascular blood filter |
US9326843B2 (en) | 2009-01-16 | 2016-05-03 | Claret Medical, Inc. | Intravascular blood filters and methods of use |
EP2459120A4 (en) | 2009-07-27 | 2017-11-01 | Claret Medical, Inc. | Dual endovascular filter and methods of use |
US8801633B2 (en) | 2009-08-31 | 2014-08-12 | Neometrics, Inc. | High-modulus superelastic alloy wire for medical and dental purposes |
EP3300691B1 (en) | 2009-09-21 | 2021-06-30 | Boston Scientific Scimed, Inc. | Intravascular blood filters |
JP4913198B2 (en) * | 2009-10-27 | 2012-04-11 | 株式会社パテントストラ | Medical guide wire, method for manufacturing medical guide wire, assembly of medical guide wire, microcatheter and guiding catheter, and assembly of medical guide wire, balloon catheter and guiding catheter |
US8137293B2 (en) | 2009-11-17 | 2012-03-20 | Boston Scientific Scimed, Inc. | Guidewires including a porous nickel-titanium alloy |
US20110190831A1 (en) * | 2010-01-29 | 2011-08-04 | Kyphon Sarl | Steerable balloon catheter |
EP2552530A1 (en) | 2010-03-31 | 2013-02-06 | Boston Scientific Scimed, Inc. | Guidewire with a flexural rigidity profile |
WO2011162287A1 (en) * | 2010-06-22 | 2011-12-29 | オリンパスメディカルシステムズ株式会社 | Tissue clamp production method and tissue clamp |
EP2603254A4 (en) | 2010-08-12 | 2016-08-24 | Boston Scient Ltd | Infusion flow system and fluid coupling |
US8500658B2 (en) * | 2010-10-28 | 2013-08-06 | Abbott Cardiovascular Systems Inc. | Nickel-titanium core guide wire |
US11141063B2 (en) | 2010-12-23 | 2021-10-12 | Philips Image Guided Therapy Corporation | Integrated system architectures and methods of use |
US9345565B2 (en) | 2010-12-30 | 2016-05-24 | Claret Medical, Inc. | Steerable dual filter cerebral protection system |
US11040140B2 (en) | 2010-12-31 | 2021-06-22 | Philips Image Guided Therapy Corporation | Deep vein thrombosis therapeutic methods |
WO2012106628A1 (en) | 2011-02-04 | 2012-08-09 | Boston Scientific Scimed, Inc. | Guidewires and methods for making and using the same |
US20120232528A1 (en) * | 2011-03-07 | 2012-09-13 | Abbott Cardiovascular Systems Inc. | Delivery system with incremental markers |
JP4913249B2 (en) * | 2011-04-27 | 2012-04-11 | 株式会社パテントストラ | Medical guide wire and manufacturing method thereof |
JP5733794B2 (en) * | 2011-05-10 | 2015-06-10 | 朝日インテック株式会社 | Medical guidewire |
US9072874B2 (en) | 2011-05-13 | 2015-07-07 | Boston Scientific Scimed, Inc. | Medical devices with a heat transfer region and a heat sink region and methods for manufacturing medical devices |
JP4913252B1 (en) * | 2011-05-30 | 2012-04-11 | 株式会社パテントストラ | Medical guide wire and manufacturing method thereof |
US9360630B2 (en) | 2011-08-31 | 2016-06-07 | Volcano Corporation | Optical-electrical rotary joint and methods of use |
CN104023782A (en) | 2011-12-28 | 2014-09-03 | 泰尔茂株式会社 | Guide wire |
US10029076B2 (en) | 2012-02-28 | 2018-07-24 | Covidien Lp | Intravascular guidewire |
US9474605B2 (en) | 2012-05-16 | 2016-10-25 | Edwards Lifesciences Corporation | Devices and methods for reducing cardiac valve regurgitation |
US9324141B2 (en) | 2012-10-05 | 2016-04-26 | Volcano Corporation | Removal of A-scan streaking artifact |
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US9858668B2 (en) | 2012-10-05 | 2018-01-02 | Volcano Corporation | Guidewire artifact removal in images |
US9292918B2 (en) | 2012-10-05 | 2016-03-22 | Volcano Corporation | Methods and systems for transforming luminal images |
JP2015532536A (en) | 2012-10-05 | 2015-11-09 | デイビッド ウェルフォード, | System and method for amplifying light |
US10568586B2 (en) | 2012-10-05 | 2020-02-25 | Volcano Corporation | Systems for indicating parameters in an imaging data set and methods of use |
US10070827B2 (en) | 2012-10-05 | 2018-09-11 | Volcano Corporation | Automatic image playback |
US9286673B2 (en) | 2012-10-05 | 2016-03-15 | Volcano Corporation | Systems for correcting distortions in a medical image and methods of use thereof |
US9367965B2 (en) | 2012-10-05 | 2016-06-14 | Volcano Corporation | Systems and methods for generating images of tissue |
US11272845B2 (en) | 2012-10-05 | 2022-03-15 | Philips Image Guided Therapy Corporation | System and method for instant and automatic border detection |
US9840734B2 (en) | 2012-10-22 | 2017-12-12 | Raindance Technologies, Inc. | Methods for analyzing DNA |
JP6322210B2 (en) | 2012-12-13 | 2018-05-09 | ボルケーノ コーポレイション | Devices, systems, and methods for targeted intubation |
EP2934282B1 (en) | 2012-12-20 | 2020-04-29 | Volcano Corporation | Locating intravascular images |
US10939826B2 (en) | 2012-12-20 | 2021-03-09 | Philips Image Guided Therapy Corporation | Aspirating and removing biological material |
US11406498B2 (en) | 2012-12-20 | 2022-08-09 | Philips Image Guided Therapy Corporation | Implant delivery system and implants |
JP2016504589A (en) | 2012-12-20 | 2016-02-12 | ナサニエル ジェイ. ケンプ, | Optical coherence tomography system reconfigurable between different imaging modes |
US10942022B2 (en) | 2012-12-20 | 2021-03-09 | Philips Image Guided Therapy Corporation | Manual calibration of imaging system |
WO2014099899A1 (en) | 2012-12-20 | 2014-06-26 | Jeremy Stigall | Smooth transition catheters |
WO2014099672A1 (en) | 2012-12-21 | 2014-06-26 | Andrew Hancock | System and method for multipath processing of image signals |
US10191220B2 (en) | 2012-12-21 | 2019-01-29 | Volcano Corporation | Power-efficient optical circuit |
US10058284B2 (en) | 2012-12-21 | 2018-08-28 | Volcano Corporation | Simultaneous imaging, monitoring, and therapy |
US10166003B2 (en) | 2012-12-21 | 2019-01-01 | Volcano Corporation | Ultrasound imaging with variable line density |
US9612105B2 (en) | 2012-12-21 | 2017-04-04 | Volcano Corporation | Polarization sensitive optical coherence tomography system |
US9486143B2 (en) | 2012-12-21 | 2016-11-08 | Volcano Corporation | Intravascular forward imaging device |
JP2016502884A (en) | 2012-12-21 | 2016-02-01 | ダグラス メイヤー, | Rotating ultrasound imaging catheter with extended catheter body telescope |
WO2014099896A1 (en) | 2012-12-21 | 2014-06-26 | David Welford | Systems and methods for narrowing a wavelength emission of light |
US10413317B2 (en) | 2012-12-21 | 2019-09-17 | Volcano Corporation | System and method for catheter steering and operation |
JP2016508757A (en) | 2012-12-21 | 2016-03-24 | ジェイソン スペンサー, | System and method for graphical processing of medical data |
CN105103163A (en) | 2013-03-07 | 2015-11-25 | 火山公司 | Multimodal segmentation in intravascular images |
US10226597B2 (en) | 2013-03-07 | 2019-03-12 | Volcano Corporation | Guidewire with centering mechanism |
EP3895604A1 (en) | 2013-03-12 | 2021-10-20 | Collins, Donna | Systems and methods for diagnosing coronary microvascular disease |
US20140276923A1 (en) | 2013-03-12 | 2014-09-18 | Volcano Corporation | Vibrating catheter and methods of use |
US11026591B2 (en) | 2013-03-13 | 2021-06-08 | Philips Image Guided Therapy Corporation | Intravascular pressure sensor calibration |
US9301687B2 (en) | 2013-03-13 | 2016-04-05 | Volcano Corporation | System and method for OCT depth calibration |
CN105120759B (en) | 2013-03-13 | 2018-02-23 | 火山公司 | System and method for producing image from rotation intravascular ultrasound equipment |
US10292677B2 (en) | 2013-03-14 | 2019-05-21 | Volcano Corporation | Endoluminal filter having enhanced echogenic properties |
US10219887B2 (en) | 2013-03-14 | 2019-03-05 | Volcano Corporation | Filters with echogenic characteristics |
EP2967606B1 (en) | 2013-03-14 | 2018-05-16 | Volcano Corporation | Filters with echogenic characteristics |
US10124437B2 (en) | 2013-08-19 | 2018-11-13 | Covidien Lp | Laser welding of nickel titanium alloys |
US20150094690A1 (en) * | 2013-09-30 | 2015-04-02 | Abbott Cardiovasular Systems Inc. | Guidewire with varying properties |
US10335580B2 (en) | 2013-09-30 | 2019-07-02 | Abbott Cardiovascular Systems Inc. | Guidewire with varying properties |
US9901706B2 (en) | 2014-04-11 | 2018-02-27 | Boston Scientific Scimed, Inc. | Catheters and catheter shafts |
US9566144B2 (en) | 2015-04-22 | 2017-02-14 | Claret Medical, Inc. | Vascular filters, deflectors, and methods |
US11351048B2 (en) | 2015-11-16 | 2022-06-07 | Boston Scientific Scimed, Inc. | Stent delivery systems with a reinforced deployment sheath |
JP7091320B2 (en) * | 2016-10-06 | 2022-06-27 | ミビ・ニューロサイエンス・インコーポレイテッド | Catheter for performing hydraulic displacement and removal of thrombotic clots, as well as hydraulic displacement |
WO2018156655A1 (en) | 2017-02-22 | 2018-08-30 | Claret Medical, Inc. | Systems and methods for protecting the cerebral vasculature |
US11224910B2 (en) * | 2017-03-03 | 2022-01-18 | Cook Medical Technologies Llc | Method of forming a bend of a predetermined bend angle in a shape memory alloy wire and method of making a self-expanding stent |
WO2018183832A1 (en) * | 2017-03-30 | 2018-10-04 | University Of Hawaii | Steerable surgical devices with shape memory alloy wires |
US11141145B2 (en) | 2017-08-25 | 2021-10-12 | Edwards Lifesciences Corporation | Devices and methods for securing a tissue anchor |
WO2019084541A1 (en) | 2017-10-27 | 2019-05-02 | Claret Medical, Inc. | Systems and methods for protecting the cerebral vasculature |
EP4212127A1 (en) | 2017-12-19 | 2023-07-19 | Boston Scientific Scimed, Inc. | System for protecting the cerebral vasculature |
US10799350B2 (en) | 2018-01-05 | 2020-10-13 | Edwards Lifesciences Corporation | Percutaneous implant retrieval connector and method |
EP3720389A1 (en) | 2018-01-22 | 2020-10-14 | Edwards Lifesciences Corporation | Heart shape preserving anchor |
WO2019204732A1 (en) * | 2018-04-19 | 2019-10-24 | Wake Forest University Health Sciences | A medical device for use in a nerve block procedure that obviates the need for injecting test doses, and a method |
US11439491B2 (en) | 2018-04-26 | 2022-09-13 | Claret Medical, Inc. | Systems and methods for protecting the cerebral vasculature |
US11007061B2 (en) | 2018-05-24 | 2021-05-18 | Edwards Lifesciences Corporation | Adjustable percutaneous heart valve repair system |
CN112930152A (en) | 2018-08-21 | 2021-06-08 | 波士顿科学国际有限公司 | System and method for protecting cerebral blood vessels |
US11684759B2 (en) | 2020-01-22 | 2023-06-27 | Abbott Cardiovascular Systems Inc. | Guidewire having varying diameters and method of making |
CN116172640A (en) * | 2021-11-26 | 2023-05-30 | 先健科技(深圳)有限公司 | Push cable, push system, heat treatment method and preparation method of push cable |
Family Cites Families (78)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3144868A (en) * | 1960-10-21 | 1964-08-18 | Mario E Jascalevich | Drainage and feeding cannulae |
GB1315652A (en) | 1969-05-01 | 1973-05-02 | Fulmer Res Inst Ltd | Heat-recoverable alloys |
US3753792A (en) | 1969-07-02 | 1973-08-21 | Robertshaw Controls Co | Method of achieving thermally balanced hot wire relay type devices |
SU449105A1 (en) | 1972-04-17 | 1974-11-05 | Сибирский Физико-Технический Институт Имени В.Д.Кузнецова При Томском Государственном Университете | The method of ordering the internal deformations during phase transformations |
US3890977A (en) * | 1974-03-01 | 1975-06-24 | Bruce C Wilson | Kinetic memory electrodes, catheters and cannulae |
US4036669A (en) | 1975-02-18 | 1977-07-19 | Raychem Corporation | Mechanical preconditioning method |
CA1153264A (en) * | 1979-02-08 | 1983-09-06 | Hidenaga Yoshimura | Medical vascular guide wire and self-guiding type catheter |
US4435229A (en) | 1979-09-25 | 1984-03-06 | Johnson Alfred D | Method of preparing a two-way shape memory alloy |
US4511354A (en) * | 1980-05-07 | 1985-04-16 | Medical Research Associates, Ltd. | Hydrocarbon block copolymer with dispersed polysiloxane |
US4304613A (en) | 1980-05-12 | 1981-12-08 | The United States Of America As Represented By The Secretary Of The Navy | TiNi Base alloy shape memory enhancement through thermal and mechanical processing |
DE3235974A1 (en) * | 1981-11-24 | 1983-06-01 | Volkmar Dipl.-Ing. Merkel (FH), 8520 Erlangen | DEVICE FOR REMOVAL OR FOR THE EXPANSION OF CONSTRAINTS IN BODY LIQUID LEADING VESSELS |
JPS58151445A (en) | 1982-02-27 | 1983-09-08 | Tohoku Metal Ind Ltd | Titanium-nickel alloy having reversible shape storage effect and its manufacture |
US4445892A (en) * | 1982-05-06 | 1984-05-01 | Laserscope, Inc. | Dual balloon catheter device |
US4468216A (en) * | 1982-05-20 | 1984-08-28 | Rudolph Muto | Irrigation suction catheter |
CA1232814A (en) * | 1983-09-16 | 1988-02-16 | Hidetoshi Sakamoto | Guide wire for catheter |
US5067957A (en) * | 1983-10-14 | 1991-11-26 | Raychem Corporation | Method of inserting medical devices incorporating SIM alloy elements |
US5190546A (en) * | 1983-10-14 | 1993-03-02 | Raychem Corporation | Medical devices incorporating SIM alloy elements |
US4665906A (en) * | 1983-10-14 | 1987-05-19 | Raychem Corporation | Medical devices incorporating sim alloy elements |
US4758222A (en) * | 1985-05-03 | 1988-07-19 | Mccoy William C | Steerable and aimable catheter |
US4484955A (en) | 1983-12-12 | 1984-11-27 | Hochstein Peter A | Shape memory material and method of treating same |
JPS6184361A (en) | 1984-09-29 | 1986-04-28 | Tohoku Metal Ind Ltd | Manufacture of pseudoelastic spring |
JPS61183455A (en) | 1985-02-06 | 1986-08-16 | Furukawa Electric Co Ltd:The | Manufacture of ni-ti type shape memory material |
US5449343A (en) * | 1985-07-30 | 1995-09-12 | Advanced Cardiovascular Systems, Inc. | Steerable dilatation catheter |
JPS6260851A (en) | 1985-09-11 | 1987-03-17 | Sumitomo Metal Mining Co Ltd | Manufacture of shape memory ni-ti alloy |
US4655746A (en) * | 1985-12-02 | 1987-04-07 | Target Therapeutics | Catheter device |
JPS62199758A (en) | 1986-02-27 | 1987-09-03 | Nippon Stainless Steel Co Ltd | Manufacture of shape memory alloy material |
IT8629545V0 (en) * | 1986-06-12 | 1986-06-12 | Fina Ernesto | SET BALLOON URETERAL CATHETER BALLOON FOR EXTRACTION OF URETERAL STONES |
US4748982A (en) * | 1987-01-06 | 1988-06-07 | Advanced Cardiovascular Systems, Inc. | Reinforced balloon dilatation catheter with slitted exchange sleeve and method |
JPH0665742B2 (en) | 1987-01-08 | 1994-08-24 | 株式会社ト−キン | Shape memory TiNiV alloy manufacturing method |
US5025799A (en) * | 1987-05-13 | 1991-06-25 | Wilson Bruce C | Steerable memory alloy guide wires |
JPS63312955A (en) | 1987-06-15 | 1988-12-21 | Aichi Steel Works Ltd | Manufacture of ni-ti alloy-type thermosensitive working element material excellent in heat cycle life |
JPS6480367A (en) * | 1987-09-21 | 1989-03-27 | Terumo Corp | Member for correcting ureter |
US4964409A (en) * | 1989-05-11 | 1990-10-23 | Advanced Cardiovascular Systems, Inc. | Flexible hollow guiding member with means for fluid communication therethrough |
US6071273A (en) * | 1988-02-29 | 2000-06-06 | Scimed Life Systems, Inc. | Fixed wire dilatation balloon catheter |
US4838268A (en) * | 1988-03-07 | 1989-06-13 | Scimed Life Systems, Inc. | Non-over-the wire balloon catheter |
JPH01242763A (en) | 1988-03-23 | 1989-09-27 | Hitachi Metals Ltd | Manufacture of ti-ni shape memory alloy reduced in hysteresis |
US4881981A (en) * | 1988-04-20 | 1989-11-21 | Johnson Service Company | Method for producing a shape memory alloy member having specific physical and mechanical properties |
US4998917A (en) * | 1988-05-26 | 1991-03-12 | Advanced Cardiovascular Systems, Inc. | High torque steerable dilatation catheter |
JPH02149651A (en) | 1988-07-22 | 1990-06-08 | Hitachi Metals Ltd | Manufacture of ti-ni series superelastic alloy |
JPH0255064A (en) * | 1988-08-03 | 1990-02-23 | Toa O | Skin removal for throm bus in blood vessel using catheter and throm bus removing system in blood vessel using catheter |
US4998923A (en) * | 1988-08-11 | 1991-03-12 | Advanced Cardiovascular Systems, Inc. | Steerable dilatation catheter |
CH676426A5 (en) * | 1988-09-27 | 1991-01-31 | Schneider Shiley Ag | |
US4935068A (en) * | 1989-01-23 | 1990-06-19 | Raychem Corporation | Method of treating a sample of an alloy |
US5035686A (en) * | 1989-01-27 | 1991-07-30 | C. R. Bard, Inc. | Catheter exchange system with detachable luer fitting |
US4946466A (en) * | 1989-03-03 | 1990-08-07 | Cordis Corporation | Transluminal angioplasty apparatus |
EP0395098B1 (en) * | 1989-04-28 | 1994-04-06 | Tokin Corporation | Readily operable catheter guide wire using shape memory alloy with pseudo elasticity |
US5120308A (en) * | 1989-05-03 | 1992-06-09 | Progressive Angioplasty Systems, Inc. | Catheter with high tactile guide wire |
US5169386A (en) * | 1989-09-11 | 1992-12-08 | Bruce B. Becker | Method and catheter for dilatation of the lacrimal system |
DE8910856U1 (en) * | 1989-09-12 | 1989-11-30 | Schneider (Europe) Ag, Zuerich, Ch | |
US5279546A (en) * | 1990-06-27 | 1994-01-18 | Lake Region Manufacturing Company, Inc. | Thrombolysis catheter system |
US5211636A (en) * | 1990-10-31 | 1993-05-18 | Lake Region Manufacturing Co., Inc. | Steerable infusion guide wire |
DE69129098T2 (en) * | 1990-12-18 | 1998-09-17 | Advanced Cardiovascular System | Process for producing a super-elastic guide part |
US5184627A (en) * | 1991-01-18 | 1993-02-09 | Boston Scientific Corporation | Infusion guidewire including proximal stiffening sheath |
US5167239A (en) * | 1991-05-30 | 1992-12-01 | Endomedix Corporation | Anchorable guidewire |
US5221270A (en) * | 1991-06-28 | 1993-06-22 | Cook Incorporated | Soft tip guiding catheter |
US5324259A (en) * | 1991-12-18 | 1994-06-28 | Advanced Cardiovascular Systems, Inc. | Intravascular catheter with means to seal guidewire port |
US5243996A (en) | 1992-01-03 | 1993-09-14 | Cook, Incorporated | Small-diameter superelastic wire guide |
US5209727A (en) * | 1992-01-29 | 1993-05-11 | Interventional Technologies, Inc. | Guide wire with integral angioplasty balloon |
US5417658A (en) * | 1992-03-17 | 1995-05-23 | Scimed Life Systems, Inc. | Balloon dilatation catheter having a torsionally soft component |
US5290230A (en) * | 1992-05-11 | 1994-03-01 | Advanced Cardiovascular Systems, Inc. | Intraluminal catheter with a composite shaft |
US5500180A (en) * | 1992-09-30 | 1996-03-19 | C. R. Bard, Inc. | Method of making a distensible dilatation balloon using a block copolymer |
ES2102187T3 (en) * | 1992-11-18 | 1997-07-16 | Spectrascience Inc | DIAGNOSTIC DEVICE FOR IMAGE FORMATION. |
US5281200A (en) * | 1992-12-08 | 1994-01-25 | Cordis Corporation | Multiple component balloon catheter system and stenosis treatment procedure |
US5403274A (en) * | 1993-03-15 | 1995-04-04 | Cannon; Louis A. | Perfusion catheter and method of use |
US5322508A (en) * | 1993-04-08 | 1994-06-21 | Cordis Corporation | Guidewire fluid delivery system and method of use |
US5456667A (en) * | 1993-05-20 | 1995-10-10 | Advanced Cardiovascular Systems, Inc. | Temporary stenting catheter with one-piece expandable segment |
US5344402A (en) * | 1993-06-30 | 1994-09-06 | Cardiovascular Dynamics, Inc. | Low profile perfusion catheter |
US5462529A (en) * | 1993-09-29 | 1995-10-31 | Technology Development Center | Adjustable treatment chamber catheter |
US5476450A (en) * | 1993-11-04 | 1995-12-19 | Ruggio; Joseph M. | Apparatus and method for aspirating intravascular, pulmonary and cardiac obstructions |
WO1996015824A1 (en) * | 1994-11-23 | 1996-05-30 | Micro Interventional Systems, Inc. | High torque balloon catheter |
EP0729765B1 (en) * | 1995-03-02 | 2000-06-14 | Schneider (Europe) GmbH | A method for manufacturing a guide wire |
US5951793A (en) * | 1995-07-12 | 1999-09-14 | The Furukawa Electric Co., Ltd. | Ni-Ti-Pd superelastic alloy material, its manufacturing method, and orthodontic archwire made of this alloy material |
WO1997011735A1 (en) * | 1995-09-27 | 1997-04-03 | Interventional Innovations Corporation | Nickel titanium guide wires for occlusion and drug delivery |
US6019736A (en) * | 1995-11-06 | 2000-02-01 | Francisco J. Avellanet | Guidewire for catheter |
US6068623A (en) * | 1997-03-06 | 2000-05-30 | Percusurge, Inc. | Hollow medical wires and methods of constructing same |
US5706828A (en) | 1996-07-30 | 1998-01-13 | Mike Corporation | Sudorific mask |
US6042553A (en) * | 1997-04-15 | 2000-03-28 | Symbiosis Corporation | Linear elastic member |
US5964770A (en) * | 1997-09-30 | 1999-10-12 | Litana Ltd. | High strength medical devices of shape memory alloy |
-
1997
- 1997-03-06 US US08/812,876 patent/US6068623A/en not_active Expired - Lifetime
-
1998
- 1998-03-06 WO PCT/US1998/004500 patent/WO1998039048A2/en not_active Application Discontinuation
- 1998-03-06 CA CA002287072A patent/CA2287072A1/en not_active Abandoned
- 1998-03-06 EP EP98909033A patent/EP0996480A2/en not_active Ceased
- 1998-03-06 AU AU66916/98A patent/AU6691698A/en not_active Abandoned
- 1998-03-06 JP JP53888898A patent/JP2001514544A/en not_active Ceased
-
1999
- 1999-10-08 US US09/415,607 patent/US6217567B1/en not_active Expired - Lifetime
-
2000
- 2000-02-16 US US09/505,380 patent/US6375628B1/en not_active Expired - Lifetime
-
2001
- 2001-04-17 US US09/837,872 patent/US20020095137A1/en not_active Abandoned
Non-Patent Citations (1)
Title |
---|
None |
Cited By (27)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO1999026692A1 (en) | 1997-11-20 | 1999-06-03 | Percusurge, Inc. | Low profile catheter valve and inflation adaptor |
WO2000050113A2 (en) | 1999-02-22 | 2000-08-31 | Percusurge, Inc. | Balloon catheter with axial flexibility |
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US7763012B2 (en) | 2003-09-02 | 2010-07-27 | St. Jude Medical, Cardiology Division, Inc. | Devices and methods for crossing a chronic total occlusion |
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US9289215B2 (en) | 2007-03-13 | 2016-03-22 | Covidien Lp | Implant including a coil and a stretch-resistant member |
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EP2408356A4 (en) * | 2009-03-17 | 2013-07-31 | Opsens Inc | Eccentric pressure catheter with guidewire compatibility |
US8894587B2 (en) | 2009-07-02 | 2014-11-25 | Asahi Intecc Co., Ltd. | Medical guide wire, method of making the same, and assembly of balloon catheter and guiding catheter combined with the medical guide wire |
WO2011084240A1 (en) * | 2009-12-17 | 2011-07-14 | Cook Incorporated | Method of improving the properties of a component of a medical device comprising a nickel-titanium-chromium alloy |
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Also Published As
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CA2287072A1 (en) | 1998-09-11 |
US6217567B1 (en) | 2001-04-17 |
EP0996480A2 (en) | 2000-05-03 |
US6068623A (en) | 2000-05-30 |
US20020095137A1 (en) | 2002-07-18 |
JP2001514544A (en) | 2001-09-11 |
US6375628B1 (en) | 2002-04-23 |
AU6691698A (en) | 1998-09-22 |
WO1998039048A3 (en) | 1998-12-03 |
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