WO1995001753A1 - Flexible housing for intracorporeal use - Google Patents
Flexible housing for intracorporeal use Download PDFInfo
- Publication number
- WO1995001753A1 WO1995001753A1 PCT/US1994/007766 US9407766W WO9501753A1 WO 1995001753 A1 WO1995001753 A1 WO 1995001753A1 US 9407766 W US9407766 W US 9407766W WO 9501753 A1 WO9501753 A1 WO 9501753A1
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- WO
- WIPO (PCT)
- Prior art keywords
- housing
- catheter
- temperature
- shape memory
- martensite phase
- Prior art date
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Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/32—Surgical cutting instruments
- A61B17/3205—Excision instruments
- A61B17/3207—Atherectomy devices working by cutting or abrading; Similar devices specially adapted for non-vascular obstructions
- A61B17/320783—Atherectomy devices working by cutting or abrading; Similar devices specially adapted for non-vascular obstructions through side-hole, e.g. sliding or rotating cutter inside catheter
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/01—Introducing, guiding, advancing, emplacing or holding catheters
- A61M25/0105—Steering means as part of the catheter or advancing means; Markers for positioning
- A61M25/0133—Tip steering devices
- A61M25/0141—Tip steering devices having flexible regions as a result of using materials with different mechanical properties
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/01—Introducing, guiding, advancing, emplacing or holding catheters
- A61M25/0105—Steering means as part of the catheter or advancing means; Markers for positioning
- A61M25/0133—Tip steering devices
- A61M25/0144—Tip steering devices having flexible regions as a result of inner reinforcement means, e.g. struts or rods
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M25/00—Catheters; Hollow probes
- A61M25/01—Introducing, guiding, advancing, emplacing or holding catheters
- A61M25/0105—Steering means as part of the catheter or advancing means; Markers for positioning
- A61M25/0133—Tip steering devices
- A61M25/0155—Tip steering devices with hydraulic or pneumatic means, e.g. balloons or inflatable compartments
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B2017/00831—Material properties
- A61B2017/00867—Material properties shape memory effect
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B17/00—Surgical instruments, devices or methods, e.g. tourniquets
- A61B17/22—Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for
- A61B2017/22051—Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for with an inflatable part, e.g. balloon, for positioning, blocking, or immobilisation
- A61B2017/22052—Implements for squeezing-off ulcers or the like on the inside of inner organs of the body; Implements for scraping-out cavities of body organs, e.g. bones; Calculus removers; Calculus smashing apparatus; Apparatus for removing obstructions in blood vessels, not otherwise provided for with an inflatable part, e.g. balloon, for positioning, blocking, or immobilisation eccentric
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/30—Joints
- A61F2002/30001—Additional features of subject-matter classified in A61F2/28, A61F2/30 and subgroups thereof
- A61F2002/30003—Material related properties of the prosthesis or of a coating on the prosthesis
- A61F2002/3006—Properties of materials and coating materials
- A61F2002/30092—Properties of materials and coating materials using shape memory or superelastic materials, e.g. nitinol
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2210/00—Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2210/0014—Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof using shape memory or superelastic materials, e.g. nitinol
- A61F2210/0023—Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof using shape memory or superelastic materials, e.g. nitinol operated at different temperatures whilst inside or touching the human body, heated or cooled by external energy source or cold supply
-
- 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
- A61M2205/00—General characteristics of the apparatus
- A61M2205/02—General characteristics of the apparatus characterised by a particular materials
- A61M2205/0266—Shape memory materials
Definitions
- This invention generally relates to a housing or other hollow device for intracorporeal use such as performing a therapeutic or diagnostic procedure within a body lumen or cavity within the housing.
- the housing is particularly useful with a catheter for removing tissue from a body lumen or cavity, such as the removal of atheroma from a patient's artery in an atherectomy procedure.
- a guiding catheter having a preshaped distal tip is percutaneously introduced into a patient's cardiovascular system through the femoral artery and advanced therein until the preshaped distal tip of the guiding catheter is disposed within the ascending aorta adjacent the ostium of the coronary artery in which the procedure is to be performed.
- the guiding catheter is twisted or torqued from the proximal end, which is outside the patient, to turn the distal tip of the guiding catheter so that it can be guided into the desired coronary ostium.
- An atherectomy catheter having a cutter head on its distal end is introduced into and advanced through the guiding catheter and out the distal tip thereof until the cutter head is properly positioned across the lesion to be treated.
- a positioning balloon on one side of the cutter head is inflated with liquid at relatively high pressures (e.g., 3-6 atmospheres) to press the cutter head against the stenotic tissue to be removed so that such tissue will be urged into the interior chamber of the cutter head where a cutting blade severs the tissue from the artery wall.
- the positioning balloon is then deflated so that the atherectomy catheter can be repositioned, e.g. rotated, to remove additional tissue from the stenosis in essentially the same manner.
- the positioning balloon is finally deflated and the catheter removed from the artery so that blood flow can resume through the artery.
- the cutter blade is axially rotated a relatively high speeds, e.g. 2000 rpm while the blade is advanced from one end of the housing to the other in order to sever the stenotic tissue which is urged into the interior chamber.
- DVI Devices for Vascular Intervention
- the cutter housing on most atherectomy catheters have been formed of high strength materials such as stainless steel. As a result, they have been rather stiff and this stiffness has been found to significantly restrict the ability of the atherectomy catheter to be advanced through tortuous arterial anatomy and to limit how far an atherectomy catheter can be advanced within a patient's arterial system. Softer, more flexible materials might be employed to form the cutter housing but when the housing is made of softer, more flexible materials, the housing can deform, e.g. kink, when being advanced through the shaped distal end of the guiding catheter or tortuous arterial anatomy so that the cutting blade within the housing cannot be properly moved within the inner chamber of the cutter housing for effective tissue removal.
- kink e.g. kink
- the present invention is directed to an improved housing for intracorporeal use and particularly to a housing for a catheter adapted to remove tissue or other material from a body lumen or cavity, such as an atherectomy catheter for removal of atheroma from a patient's artery.
- the flexible housing in one aspect of the invention has an inner chamber adapted to facilitate performance of a diagnostic or therapeutic procedure and is formed of a shape memory alloy which may have pseudoelastic, sometimes called superelastic, characteristics.
- the alloy preferably contains a predominant amount of NiTi, an intermetallic compound of nickel and titanium in a near equiatomic ratio of about 1 : 1 , to provide improved housing flexibility yet also provide sufficient housing strength to maintain the transverse shape of an inner chamber within the housing.
- the preferred alloy material of nickel and titanium is frequently called NITINOL, an acronym for Nickel Titanium aval Ordnance
- a suitable alloy composition includes about 30% to about 52% titanium, about 38% to about 52% nickel and additional alloying elements in amounts totaling not more than about 20% in the case of copper and not more than about 10% in the case of other alloying elements.
- the additional alloying elements may be selected from the group consisting of up to 3% each of iron, cobalt, chromium, platinum, palladium, zirconium, hafnium and niobium and up to - about 10% vanadium.
- the nickel level should be at least about 38%, but at nickel levels above 52% the alloy becomes too brittle to fabricate by cold working.
- the alloy consists mostly of a
- NiTi intermetallic compound and smaller quantities of other alloy constituents.
- Ni 14 Ti 1 Ni 3 Ti 2 or Ni 3 Ti may be formed and when titanium is in excess, Ti 2 Ni may be formed.
- All references to percent alloy compositions are atomic percent unless otherwise noted.
- the composition is selected within the above described ranges along with the thermomechanical processing variables for forming the flexible housing to provide a desired final austenite transition temperature (A f ).
- the final austenite transformation temperature (A f ) should range about 30° to about 60 ° C and preferably should be well above body temperature (37 ° C), e.g. about 47 ° C.
- the alloy composition and the thermomechanical processing should be chosen to provide an A f below body temperature (37° C) and preferably below 25 ° C.
- the thermomechanical processing involves cold working the product and then thermally treating the cold worked product to generate the desired metallurgical structure. Usually, there will be a series of cold working steps with each cold working step followed by stress relieving heat treatment at a temperature between about 600° and about 800 ° C, typically about 675 ° C for about 15 minutes, to facilitate subsequent cold working.
- the final cold working step should effect a size reduction of at least about 10%, preferably about 20% to about 75%, and the final heat treatment should be selected to develop the desired housing properties.
- the composition should be at or near equiatomic Ni and Ti to form the binary NiTi composition, whereas, if the housing is to be in the austenite phase at body temperature, the nickel should be at or more than 50%. Significant amounts of alloying elements may be included to lower the A f to a temperature below body temperature.
- the housing is to be in a stable martensite phase at body temperature, the housing or one or more portions thereof should be heat treated after the final cold working step at a temperature between about
- the housing should be given a thermal treatment at a temperature of about 425 ° to about 600 ° C, preferably about 475 ° to about 550 ⁇ C.
- the alloy composition, the amount of final cold work and the processing during final thermal treatment may be adjusted to provide the desired phase at body temperature.
- the A f decreases as the temperature of the thermal treatment increases to a minimum at about
- the A f increases as the temperature increases to the temperature of recrystallization which is over 600 °C.
- the A f will increase with nickel above equiatomic amounts (50% of Ni and 50% Ti) and corresponding decreased amounts of titanium and alloying elements, and it will decrease with decreased amounts of nickel and increased amounts of other alloying components. While the compositional changes will change the values of A f they will not change the general relationship between A f and heat treatment temperature.
- a presently preferred composition for shape memory effects is 50.02% Ni and 49.98% Ti, and a presently preferred composition for stress induced pseudoelastic properties is 50.8% Ni and 49.2% Ti.
- the housing is a tubular member in a cold worked condition with one or more sections thereof heat treated to relieve stress.
- the heat treated sections develop increased overall housing flexibility which facilitates the advancement of the housing through tortuous passageways but the cold worked sections maintain the diametrical rigidity which maintains the circularity or other transverse cross-sectional shape of the internal housing chamber.
- the sections which have been heat treated are in the martensite phase at body temperature and usually have an A f well above body temperature.
- the housing is cold worked in the manner previously discussed and then the entire housing or a significant portion of the housing along its length is heated at a temperature above the A f minimum transformation temperature which will transform any martensite phase, which is relatively soft, to the austenite phase, which is relatively hard, while the housing is straight or in another desired configuration to generate the shape remembered.
- austenite transformation temperature refers to a temperature at which martensite phase transforms to austenite upon the application of heat. This temperature may range from the temperature at which the transformation is initiated, identified as A s , to the temperature at which the transformation is completed, identified as A f .
- a 50 12
- a substantial portion of the martensite present in the alloy has been transformed to the austenite.
- the A 50 is convenient to use because it is easily determined experimentally by DSC, which demonstrates a sharp reduction in the heat flow at the A 50 .
- the housing cools after the heat treatment the austenite phase will transform to the martensite phase which is stable at the lower temperature.
- the housing can be heated to a temperature above the A f temperature of the alloy of the housing to cause the martensite phase in the housing to transform to the austenite phase.
- the housing will transform to the configuration, e.g.
- the austenite phase Upon cooling the housing to body temperature after the transformation, the austenite phase reverts to the martensite phase but the housing remains in the straight or other desired configuration which the austenite phase remembered.
- a variety of heating means may be employed to heat the martensite phase to a temperature above the A f .
- resistive or inductive heating, RF or microwave heating or conductive heating as with a heated fluid may be used.
- the housing of the invention When the housing of the invention is employed in an atherectomy catheter, it has been found convenient to rely upon the frictional engagement of the cutting blade with the interior of the housing while the cutter is rotated within the housing chamber at a relatively high rate of speed (e.g. 2000 rpm) to raise the temperature of the housing sufficiently above the A f transformation temperature so that the housing, if deformed, will revert to the straight or other memory of the austenite phase.
- the composition and thermomechanical processing are selected so that the housing is in the austenite phase at operating temperature, e.g. body temperature, and has pseudoelastic characteristics at that temperature, i.e. exhibits a stress-induced austenite to martensite transformation which occurs over a relatively constant stress level.
- the strain is for the most part proportional to the applied stress in a conventional manner.
- the stable austenite phase begins a stress-induced transformation to the martensite phase which is unstable at the operating temperature but which is stable as long as stress is applied at the appropriate levels.
- the stress no longer increases but remains at a relatively constant plateau during the stress induced phase transformation to martensite while the strain continues to increase to about 8%.
- the stress- induced transformation of the austenite phase to the martensite phase is essentially complete. As the strain increases beyond about 8%, the strain again begins to rise in proportion to the applied stress.
- the housing of this embodiment preferably has an A f temperature less than body temperature to facilitate intracorporeal use.
- Fig. 1 is an elevational schematic view of an atherectomy catheter embodying features of the invention.
- Fig. 2 is an enlarged longitudinal cross-sectional view of the distal end of the catheter shown in Fig. 1.
- Fig. 3 is a transverse cross-sectional view of the catheter shown in Fig. 1 taken along the lines 3-3.
- Fig. 4 is a perspective view of cutter housing suitable for use in the catheter shown in Fig. 1 which has heat treated flexible cylindrical sections of the housing.
- Fig. 5 is a transverse cross-sectional view of the cutter housing shown in Fig. 4 illustrating the relative dimensions of the opening or window for receiving tissue to be removed.
- Figs. 6 through 10 are elevational and plan views of alternative housings.
- Fig. 1 1 is a graphical representation of the relationship between the final austenite transition temperature and the temperature of the thermal treatment given to a pseudoelastic NiTi alloy after cold working.
- Fig. 12 is a graphical representation of the stress-strain relationship of a pseudoelastic NiTi alloy.
- FIGs. 1-3 schematically depict an atherectomy catheter 10 embodying features of the invention.
- the catheter 10 includes a distal portion 1 1 having cutter head assembly 12, an elongated catheter shaft
- the cutter head assembly 12 has a cylindrical housing 17 formed of shape memory /pseudoelastic alloy with a side opening or window 18 and a cutting blade 19 which is slidably disposed within the inner chamber 20 of the housing 17 for both longitudinal and rotational movement.
- the cutting blade 19 movement, both longitudinal and rotational is effected by the flexible cable drive shaft 21 which is secured to the proximal end of the cutter blade.
- Inflatable positioning balloon 22 is secured to the exterior of the housing 17 on a side opposite to the window 18 so that, upon its inflation within the stenotic region of the patient's artery, the housing will be pressed against the stenotic material to cause some of it to enter into the inner chamber 20 where the cutter blade 19 can sever it from the rest of the stenotic material on the arterial wall.
- An inflation tube 23 is disposed within the outer tubular member 25 of the catheter shaft 13 and has a distal end spliced together with the proximal skirt 26 of the inflatable positioning balloon 22 to direct inflation fluid to the interior of the balloon.
- the distal skirt 27 of the balloon 22 is folded over and secured within the distal end of the housing as shown in Fig. 2.
- the proximal end of the rotator 29 is rotatably secured to the manifold assembly 15 so that the torquing cable
- the triple arm manifold assembly 15 on the proximal portion 14 of the catheter 10 generally includes a manifold body 33 and inflation arm 34 and a flush arm 35.
- the inflation arm 34 is in fluid communication with the inner lumen of the inflation tube 23 for delivery of inflation fluid to the interior of the balloon 22.
- the flush arm 35 is in fluid communication with the interior of the flexible drive shaft 21 for the cutter blade 19 and is adapted to direct irrigation or radiopaque liquid to the interior of the housing 17.
- the drive assembly 16 is interconnected to the drive shaft 21 for the cutter blade 19 by means of a splined connector 36 which is adapted to be inserted into the drive spline (not shown) of the drive assembly.
- the splined connector in turn is connected to an intermediate drive shaft 37 which is fixed in a driving relationship to the proximal end of the flexible drive shaft 21 .
- a finger actuated lever 38 is rotatably mounted onto the intermediate drive shaft 37 but is fixed thereto to prevent longitudinal movement relative to the intermediate drive shaft so that longitudinal movement of the finger actuated lever will cause the longitudinal movement of the cutter blade 19 within the housing 17.
- the operation of the drive assembly 16 is initiated by the actuation of switch 39 which will cause the rotation of the flexible drive shaft 21 and the cutter blade 19 secured thereto.
- Figs. 4 and 5 illustrate the flexible housing 17 of the present invention which has a plurality of heat treated cylindrically shaped tubular sections 40 to provide improved housing flexibility.
- the housing 17 is formed of a shape memory alloy of nickel and titanium and typically is 50% Ni and 50% Ti.
- the entire housing 17 is initially in a cold worked condition by drawing through a series of dies of decreasing diameters, with intermediate anneals between working steps.
- the cylindrically shaped tubular sections 40 with a length of about 0.01 to about 0.2 inch (0.254-5.1 mm) are heat treated, preferably with a laser beam (e.g. CO 2 or YAG laser) with a spot size of about 0.002 to about
- a laser beam e.g. CO 2 or YAG laser
- the power output of the CO 2 laser is about 1 to about 7 watts. It is difficult to determine the temperature at which the laser treated tubular sections are subjected, so it may be necessary to go through a trial and error procedure to optimize the laser treatment for a particular housing wall thickness, housing composition and thermomechanical processing.
- the size of the opening or window 18 in a wall portion of the housing 17 may vary. Generally, the cutout angle, shown best in Fig. 5, should range from about 80° to about 140 ° , and preferably about 90° to about 130° . It is contemplated that the atherectomy catheters will be offered with windows of various lengths to accommodate different sized stenoses.
- Fig. 6 depicts an alternative cutter housing 17 wherein tubular section 41 , which is more flexible than adjacent tubular sections
- Figs. 7 and 8 illustrate another embodiment of the invention wherein the housing 17 is provided with an elongated strip 50 in the martensite phase which is transformable to an austenite phase with a straight memory by the application of heat to raise the temperature of the strip to above the A f temperature. The rest of the housing is in a cold worked state.
- Figs. 9 and 10 illustrate yet another embodiment of the invention where the area 60 surrounding the opening 18 of the housing 17 is heat treated above the A f , which preferably is above body temperature, to develop an austenite phase with a straight memory. Should the housing become deformed during use, it may be heated above the A f to cause the formation of the austenite phase which returns to the shape remembered, which in this case is straight.
- the area immediately adjacent to the area which has been heat treated may have properties intermediate the cold worked and heat treated properties thereby providing additional variations in properties which may be found helpful in designing a housing with multiple locations with various properties.
- Fig. 1 1 is a graphical representation of the relationship between the A f of a NiTi alloy and the temperature at which the alloy is subjected to after cold working in the thermomechanical processing described herein. As shown, the A f decreases as the temperature of thermal treatment increases to a temperature of about 550 °C.
- the A f increases until the temperature rises to the recrystallization temperature of the alloy.
- the general shape of the graphical representation of the relationship remains essentially the same even though the composition of the alloy and the amount of cold work varies.
- Fig. 12 is a graphical representation of the stress-strain relationship of a pseudoelastic NiTi alloy. As indicated the strain is proportional to stress up to a strain of about 2%. At about 2% strain the austenite phase begins to transform to martensite and continues the transformation to completion over a constant stress region to a strain of about 5%. Beyond a strain of about 8% the deformation is elastic to about 15% when it becomes plastic. Upon reduction of the stress level the material first returns to a constant stress plateau where the martensite phase transforms back to the austenite. Upon completion of the transformation at about a 2% strain the strain returns to zero if no permanent deformation has occurred.
- An atherectomy catheter or other intracorporeal catheter with a flexible housing in accordance with the invention may be used in essentially the same manner of prior catheters, except for the notable difference that the characteristics of the housing can be changed within the patient's body by changing the temperature of the housing therein. If the housing is in the martensite phase at body temperature and the housing has been provided with a desired "remembered shape" at an austenite transformation temperature above body temperature, the housing may be heated within the body to a temperature at or above the
- a 50 of the shape memory alloy so that the housing will transform to essentially the shape remembered.
- the temperature of the housing can be reduced to a temperature at or less than the M 50 of the shape memory alloy.
- the temperature of the housing can be changed when the catheter is within the patient's body by a variety of suitable means.
- the temperature of the housing can be raised by resistance/ inductance heating with electrical conductors in contact with or formed integral with the housing.
- One convenient method of heating the housing with atherectomy catheters which have cutting elements within the housing which fictionally engage the housing is to move the cutting element within the inner chamber with sufficient velocity to raise the temperature of the housing to the desired level above body temperature.
- Other means of heating the housing within the patient's body include directing a fluid at elevated temperature through an inner lumen of the catheter which is in fluid communication with the interior of the housing. RF heating may also be employed as will be recognized by those skilled in the art.
- a fluid at a temperature less than body temperature may be directed through an inner lumen within the catheter to the interior of the housing. While the housing of the present invention has been described herein in terms of certain presently preferred embodiments directed to atherectomy catheters, those skilled in the art will recognize that it may be used in a wide variety of intracorporeal devices for performing diagnostic or therapeutic procedures within a patient's body lumen or body cavity. Various modifications and improvements can also be made to the invention without departing from the scope thereof.
Abstract
An elongated flexible housing for an atherectomy or other intracorporeal catheter which is formed of a shape memory alloy such as an alloy formed predominantly of NiTi intermetallic compound. The housing preferably has an inner chamber with a tissue cutter or other diagnostic or therapeutic system provided within the chamber to sever stenotic material which is urged into the chamber through an opening or window in the housing. In one embodiment the housing has at least one section which is relatively flexible with adjacent sections which are relatively stiff to provide an increase in the overall flexibility of the housing.
Description
FLEXIBLE HOUSING FOR INTRACORPOREAL USE
BACKGROUND OF THE INVENTION
This invention generally relates to a housing or other hollow device for intracorporeal use such as performing a therapeutic or diagnostic procedure within a body lumen or cavity within the housing. The housing is particularly useful with a catheter for removing tissue from a body lumen or cavity, such as the removal of atheroma from a patient's artery in an atherectomy procedure.
In typical coronary atherectomy procedures, a guiding catheter having a preshaped distal tip is percutaneously introduced into a patient's cardiovascular system through the femoral artery and advanced therein until the preshaped distal tip of the guiding catheter is disposed within the ascending aorta adjacent the ostium of the coronary artery in which the procedure is to be performed. The guiding catheter is twisted or torqued from the proximal end, which is outside the patient, to turn the distal tip of the guiding catheter so that it can be guided into the desired coronary ostium. An atherectomy catheter having a cutter head on its distal end is introduced into and advanced through the guiding catheter and out the distal tip thereof until the cutter head is properly positioned across the lesion to be treated. Once properly positioned, a positioning
balloon on one side of the cutter head is inflated with liquid at relatively high pressures (e.g., 3-6 atmospheres) to press the cutter head against the stenotic tissue to be removed so that such tissue will be urged into the interior chamber of the cutter head where a cutting blade severs the tissue from the artery wall. The positioning balloon is then deflated so that the atherectomy catheter can be repositioned, e.g. rotated, to remove additional tissue from the stenosis in essentially the same manner. When the procedure is completed, the positioning balloon is finally deflated and the catheter removed from the artery so that blood flow can resume through the artery. In commercially available atherectomy catheters such as the Simpson Atherocath®, which is available from the assignee of the present application, Devices for Vascular Intervention (DVI), the cutter blade is axially rotated a relatively high speeds, e.g. 2000 rpm while the blade is advanced from one end of the housing to the other in order to sever the stenotic tissue which is urged into the interior chamber.
Reference is made to U.S. Reissue Patent 33,569 (Gifford, III et al.), U.S. Patent 4,771 ,774 (Simpson et al.), and U.S. Patent 5,092,873 (Simpson et al.) which describe further details of atherectomy catheters and which are incorporated herein in their entirety by reference.
The cutter housing on most atherectomy catheters have been formed of high strength materials such as stainless steel. As a result, they have been rather stiff and this stiffness has been found to significantly restrict the ability of the atherectomy catheter to be advanced through tortuous arterial anatomy and to limit how far an atherectomy catheter can be advanced within a patient's arterial system. Softer, more flexible materials might be employed to form the cutter housing but when the housing is made of softer, more flexible materials, the housing can deform, e.g. kink, when being advanced through the shaped distal end of the guiding catheter or tortuous arterial anatomy so that the cutting blade within the housing cannot be properly moved within the inner chamber of the cutter housing for effective tissue removal. It
has also been found that, if the housing is too soft or becomes deformed in the procedure, the cutting blade frequently will not remain within the inner chamber of the cutter housing as it is advanced through the inner chamber to sever tissue, thereby preventing the completion of the procedure. Moreover, in the latter instance the excursion of a rotating cutting blade through a side opening or window in the cutter housing can cause serious damage to the arterial wall. If the cutting blade cannot be withdrawn back into the inner chamber of the cutter housing through the window, there can be difficulties in withdrawing the atherectomy catheter back into the guiding catheter, requiring the removal of both the atherectomy catheter and the guiding catheter. If both the guiding catheter and the atherectomy catheter must be removed, replacement catheters would have to be advanced through the patient's arterial system, increasing considerably the length and the cost of the atherectomy procedure.
What has been needed and has been heretofore unavailable is a relatively flexible cutter housing for an atherectomy catheter which allows for effective cutting operations, which maintains its shape and which retains the cutting blade within the inner chamber of the housing during the procedure. The present invention satisfies these and other needs.
SUMMARY OF THE INVENTION
The present invention is directed to an improved housing for intracorporeal use and particularly to a housing for a catheter adapted to remove tissue or other material from a body lumen or cavity, such as an atherectomy catheter for removal of atheroma from a patient's artery. The flexible housing in one aspect of the invention has an inner chamber adapted to facilitate performance of a diagnostic or therapeutic procedure and is formed of a shape memory alloy which may have pseudoelastic, sometimes called superelastic, characteristics. The alloy preferably contains a predominant amount of NiTi, an intermetallic
compound of nickel and titanium in a near equiatomic ratio of about 1 : 1 , to provide improved housing flexibility yet also provide sufficient housing strength to maintain the transverse shape of an inner chamber within the housing. The preferred alloy material of nickel and titanium is frequently called NITINOL, an acronym for Nickel Titanium aval Ordnance
Laboratory where it was initially developed. A suitable alloy composition includes about 30% to about 52% titanium, about 38% to about 52% nickel and additional alloying elements in amounts totaling not more than about 20% in the case of copper and not more than about 10% in the case of other alloying elements. The additional alloying elements may be selected from the group consisting of up to 3% each of iron, cobalt, chromium, platinum, palladium, zirconium, hafnium and niobium and up to - about 10% vanadium. Generally, the nickel level should be at least about 38%, but at nickel levels above 52% the alloy becomes too brittle to fabricate by cold working. Metallurgically, the alloy consists mostly of a
NiTi intermetallic compound and smaller quantities of other alloy constituents. In addition to the NiTi intermetallic, when nickel is in excess, Ni14Ti1 Ni3Ti2 or Ni3Ti may be formed and when titanium is in excess, Ti2Ni may be formed. As used herein all references to percent alloy compositions are atomic percent unless otherwise noted. The composition is selected within the above described ranges along with the thermomechanical processing variables for forming the flexible housing to provide a desired final austenite transition temperature (Af). For shape memory effects at or below body temperature the final austenite transformation temperature (Af) should range about 30° to about 60 ° C and preferably should be well above body temperature (37 ° C), e.g. about 47 ° C. For pseudoelastic characteristics at body temperature the alloy composition and the thermomechanical processing should be chosen to provide an Af below body temperature (37° C) and preferably below 25 ° C. The thermomechanical processing involves cold working the product and then thermally treating the cold worked product to generate the desired metallurgical structure. Usually, there will be a series of cold
working steps with each cold working step followed by stress relieving heat treatment at a temperature between about 600° and about 800 ° C, typically about 675 ° C for about 15 minutes, to facilitate subsequent cold working. The final cold working step should effect a size reduction of at least about 10%, preferably about 20% to about 75%, and the final heat treatment should be selected to develop the desired housing properties. Where all or part of the housing is to be in the martensite phase at body temperature, the composition should be at or near equiatomic Ni and Ti to form the binary NiTi composition, whereas, if the housing is to be in the austenite phase at body temperature, the nickel should be at or more than 50%. Significant amounts of alloying elements may be included to lower the Af to a temperature below body temperature.
If the housing is to be in a stable martensite phase at body temperature, the housing or one or more portions thereof should be heat treated after the final cold working step at a temperature between about
375 ° and about 600 ° C, preferably about 450°C to about 475°, to impart the desired shape memory effect to the entire' housing or one or more portions thereof. If the housing is to be in a stable austenite phase at or below body temperature, the housing should be given a thermal treatment at a temperature of about 425 ° to about 600 ° C, preferably about 475 ° to about 550 βC.
The alloy composition, the amount of final cold work and the processing during final thermal treatment may be adjusted to provide the desired phase at body temperature. Generally, the Af decreases as the temperature of the thermal treatment increases to a minimum at about
550 °C and then the Af increases as the temperature increases to the temperature of recrystallization which is over 600 °C. Compositionally, the Af will increase with nickel above equiatomic amounts (50% of Ni and 50% Ti) and corresponding decreased amounts of titanium and alloying elements, and it will decrease with decreased amounts of nickel and increased amounts of other alloying components. While the compositional changes will change the values of Af they will not change
the general relationship between Af and heat treatment temperature. A presently preferred composition for shape memory effects is 50.02% Ni and 49.98% Ti, and a presently preferred composition for stress induced pseudoelastic properties is 50.8% Ni and 49.2% Ti. Increasing amoun.ts of cold work generally decrease both the martensitic and austenitic transformation temperatures, the latter to a lesser extent than the former. In one preferred embodiment of the invention, the housing is a tubular member in a cold worked condition with one or more sections thereof heat treated to relieve stress. The heat treated sections develop increased overall housing flexibility which facilitates the advancement of the housing through tortuous passageways but the cold worked sections maintain the diametrical rigidity which maintains the circularity or other transverse cross-sectional shape of the internal housing chamber. In this embodiment, the sections which have been heat treated are in the martensite phase at body temperature and usually have an Af well above body temperature.
In another preferred embodiment of the Invention, the housing is cold worked in the manner previously discussed and then the entire housing or a significant portion of the housing along its length is heated at a temperature above the Af minimum transformation temperature which will transform any martensite phase, which is relatively soft, to the austenite phase, which is relatively hard, while the housing is straight or in another desired configuration to generate the shape remembered. As used herein the austenite transformation temperature refers to a temperature at which martensite phase transforms to austenite upon the application of heat. This temperature may range from the temperature at which the transformation is initiated, identified as As, to the temperature at which the transformation is completed, identified as Af. At the midpoint temperature, A50 = 12, a substantial portion of the martensite present in the alloy has been transformed to the austenite. The A50 is convenient to use because it is easily determined experimentally by DSC, which demonstrates a sharp reduction in the heat
flow at the A50. When the housing cools after the heat treatment the austenite phase will transform to the martensite phase which is stable at the lower temperature. In this case, should the housing become deformed within the patient's body, e.g. when advancing the housing through a patient's tortuous vasculature, the housing can be heated to a temperature above the Af temperature of the alloy of the housing to cause the martensite phase in the housing to transform to the austenite phase. The housing will transform to the configuration, e.g. straight condition or other desired configuration, which the austenite phase remembers. Upon cooling the housing to body temperature after the transformation, the austenite phase reverts to the martensite phase but the housing remains in the straight or other desired configuration which the austenite phase remembered. A variety of heating means may be employed to heat the martensite phase to a temperature above the Af. For example, resistive or inductive heating, RF or microwave heating or conductive heating as with a heated fluid may be used.
When the housing of the invention is employed in an atherectomy catheter, it has been found convenient to rely upon the frictional engagement of the cutting blade with the interior of the housing while the cutter is rotated within the housing chamber at a relatively high rate of speed (e.g. 2000 rpm) to raise the temperature of the housing sufficiently above the Af transformation temperature so that the housing, if deformed, will revert to the straight or other memory of the austenite phase. In yet another embodiment of the invention, the composition and thermomechanical processing are selected so that the housing is in the austenite phase at operating temperature, e.g. body temperature, and has pseudoelastic characteristics at that temperature, i.e. exhibits a stress-induced austenite to martensite transformation which occurs over a relatively constant stress level. During the initial application of stress to a housing in the austenite phase, the strain is for the most part proportional to the applied stress in a conventional manner. However, when the
housing strain reaches about 2%, the stable austenite phase begins a stress-induced transformation to the martensite phase which is unstable at the operating temperature but which is stable as long as stress is applied at the appropriate levels. At a strain above about 2% the stress no longer increases but remains at a relatively constant plateau during the stress induced phase transformation to martensite while the strain continues to increase to about 8%. At a strain of about 8%, the stress- induced transformation of the austenite phase to the martensite phase is essentially complete. As the strain increases beyond about 8%, the strain again begins to rise in proportion to the applied stress. At a strain from about 8% to about 15% the deformation of the martensite is elastic, but at a strain above about 15% the deformation of the martensite becomes plastic or permanent. The stress-induced martensite is unstable at the operating temperature, so when the applied stress is lowered, the strain is reduced to a region with a second plateau of relatively constant stress, lower than the first plateau of relatively constant stress, where the stress-induced unstable martensite phase transforms' back to the more stable austenite phase. If no permanent or plastic deformation has occurred to the housing, it will return to its initial shape when all the applied stress is removed. The housing of this embodiment preferably has an Af temperature less than body temperature to facilitate intracorporeal use. An example of the application of stress which would transform the austenite phase to the martensite phase might be when a housing having pseudoelastic properties passes through tortuous arterial passageways or through the tight curvature of the shaped distal end of a guiding catheter. The stresses on the housing causes the austenite phase to transform to the martensite phase, thereby allowing the housing to flex at relatively low and constant stress levels. However, when the stress is removed, the martensite phase reverts back to the stronger austenite phase which "remembers" its original shape or configuration which in this instance is preferably a straight condition.
These and other advantages of the invention will become more apparent from the following detailed description of the invention when taken in conjunction with the accompanying exemplary drawings.
BRIEF DESCRIPTION OF THE DRAWINGS
Fig. 1 is an elevational schematic view of an atherectomy catheter embodying features of the invention.
Fig. 2 is an enlarged longitudinal cross-sectional view of the distal end of the catheter shown in Fig. 1. Fig. 3 is a transverse cross-sectional view of the catheter shown in Fig. 1 taken along the lines 3-3.
Fig. 4 is a perspective view of cutter housing suitable for use in the catheter shown in Fig. 1 which has heat treated flexible cylindrical sections of the housing. Fig. 5 is a transverse cross-sectional view of the cutter housing shown in Fig. 4 illustrating the relative dimensions of the opening or window for receiving tissue to be removed.
Figs. 6 through 10 are elevational and plan views of alternative housings. Fig. 1 1 is a graphical representation of the relationship between the final austenite transition temperature and the temperature of the thermal treatment given to a pseudoelastic NiTi alloy after cold working.
Fig. 12 is a graphical representation of the stress-strain relationship of a pseudoelastic NiTi alloy.
DETAILED DESCRIPTION OF THE INVENTION
Figs. 1-3 schematically depict an atherectomy catheter 10 embodying features of the invention. The catheter 10 includes a distal portion 1 1 having cutter head assembly 12, an elongated catheter shaft
13 and a proximal portion 14 having a manifold assembly 15 and drive assembly 16 (shown in phantom).
As shown in more detail in Fig. 2, the cutter head assembly 12 has a cylindrical housing 17 formed of shape memory /pseudoelastic alloy with a side opening or window 18 and a cutting blade 19 which is slidably disposed within the inner chamber 20 of the housing 17 for both longitudinal and rotational movement. The cutting blade 19 movement, both longitudinal and rotational is effected by the flexible cable drive shaft 21 which is secured to the proximal end of the cutter blade.
Inflatable positioning balloon 22 is secured to the exterior of the housing 17 on a side opposite to the window 18 so that, upon its inflation within the stenotic region of the patient's artery, the housing will be pressed against the stenotic material to cause some of it to enter into the inner chamber 20 where the cutter blade 19 can sever it from the rest of the stenotic material on the arterial wall. An inflation tube 23 is disposed within the outer tubular member 25 of the catheter shaft 13 and has a distal end spliced together with the proximal skirt 26 of the inflatable positioning balloon 22 to direct inflation fluid to the interior of the balloon. The distal skirt 27 of the balloon 22 is folded over and secured within the distal end of the housing as shown in Fig. 2. A torquing cable 28, which is also disposed within the outer tubular member 25, is secured to the proximal end of the housing 17 and is provided with a rotator 29 fixed by its distal end to the proximal end of the torquing cable to rotate the cutter head assembly 12 so that cutter head assembly may be initially positioned or repositioned within the patient's artery during the atherectomy procedure. The proximal end of the rotator 29 is rotatably secured to the manifold assembly 15 so that the torquing cable
28 can be rotated by rotation of the rotator 29 without moving the manifold assembly.
Flexible nose cone 30, which has an inner coil 31 and outer jacket 32, is secured to the distal end of the housing 17 to prevent traumatic engagement with the artery wall when the catheter 10 is advanced through the patient's arteries.
The triple arm manifold assembly 15 on the proximal portion 14 of the catheter 10 generally includes a manifold body 33 and inflation arm 34 and a flush arm 35. The inflation arm 34 is in fluid communication with the inner lumen of the inflation tube 23 for delivery of inflation fluid to the interior of the balloon 22. The flush arm 35 is in fluid communication with the interior of the flexible drive shaft 21 for the cutter blade 19 and is adapted to direct irrigation or radiopaque liquid to the interior of the housing 17.
The drive assembly 16 is interconnected to the drive shaft 21 for the cutter blade 19 by means of a splined connector 36 which is adapted to be inserted into the drive spline (not shown) of the drive assembly. The splined connector in turn is connected to an intermediate drive shaft 37 which is fixed in a driving relationship to the proximal end of the flexible drive shaft 21 . A finger actuated lever 38 is rotatably mounted onto the intermediate drive shaft 37 but is fixed thereto to prevent longitudinal movement relative to the intermediate drive shaft so that longitudinal movement of the finger actuated lever will cause the longitudinal movement of the cutter blade 19 within the housing 17. The operation of the drive assembly 16 is initiated by the actuation of switch 39 which will cause the rotation of the flexible drive shaft 21 and the cutter blade 19 secured thereto. Further details of the drive assembly 16 can be found in U.S. Patent 4,771 ,774 which has been incorporated herein by reference. The drive assembly and atherectomy catheter of the structure described herein with a conventional cutter housing formed of stainless steel are available from the assignee of the present application
Devices for Vascular Intervention, Inc. (DVl), located in Redwood City, California.
Figs. 4 and 5 illustrate the flexible housing 17 of the present invention which has a plurality of heat treated cylindrically shaped tubular sections 40 to provide improved housing flexibility. In one embodiment the housing 17 is formed of a shape memory alloy of nickel and titanium and typically is 50% Ni and 50% Ti. The entire housing 17 is initially in a
cold worked condition by drawing through a series of dies of decreasing diameters, with intermediate anneals between working steps. The cylindrically shaped tubular sections 40 with a length of about 0.01 to about 0.2 inch (0.254-5.1 mm) are heat treated, preferably with a laser beam (e.g. CO2 or YAG laser) with a spot size of about 0.002 to about
0.010 inch (0.051-0.254 mm) in diameter to stress relieve or otherwise heat treat the cylindrically shaped sections. The power output of the CO2 laser is about 1 to about 7 watts. It is difficult to determine the temperature at which the laser treated tubular sections are subjected, so it may be necessary to go through a trial and error procedure to optimize the laser treatment for a particular housing wall thickness, housing composition and thermomechanical processing.
The size of the opening or window 18 in a wall portion of the housing 17 may vary. Generally, the cutout angle, shown best in Fig. 5, should range from about 80° to about 140 ° , and preferably about 90° to about 130° . It is contemplated that the atherectomy catheters will be offered with windows of various lengths to accommodate different sized stenoses.
Fig. 6 depicts an alternative cutter housing 17 wherein tubular section 41 , which is more flexible than adjacent tubular sections
42 and 43, extends longitudinally across the window 18.
Figs. 7 and 8 illustrate another embodiment of the invention wherein the housing 17 is provided with an elongated strip 50 in the martensite phase which is transformable to an austenite phase with a straight memory by the application of heat to raise the temperature of the strip to above the Af temperature. The rest of the housing is in a cold worked state.
Figs. 9 and 10 illustrate yet another embodiment of the invention where the area 60 surrounding the opening 18 of the housing 17 is heat treated above the Af, which preferably is above body temperature, to develop an austenite phase with a straight memory. Should the housing become deformed during use, it may be heated above
the Af to cause the formation of the austenite phase which returns to the shape remembered, which in this case is straight.
In Figs. 4 and 6-10 the area immediately adjacent to the area which has been heat treated may have properties intermediate the cold worked and heat treated properties thereby providing additional variations in properties which may be found helpful in designing a housing with multiple locations with various properties.
Fig. 1 1 is a graphical representation of the relationship between the Af of a NiTi alloy and the temperature at which the alloy is subjected to after cold working in the thermomechanical processing described herein. As shown, the Af decreases as the temperature of thermal treatment increases to a temperature of about 550 °C.
Thereafter, the Af increases until the temperature rises to the recrystallization temperature of the alloy. As previously indicated, the general shape of the graphical representation of the relationship remains essentially the same even though the composition of the alloy and the amount of cold work varies.
Fig. 12 is a graphical representation of the stress-strain relationship of a pseudoelastic NiTi alloy. As indicated the strain is proportional to stress up to a strain of about 2%. At about 2% strain the austenite phase begins to transform to martensite and continues the transformation to completion over a constant stress region to a strain of about 5%. Beyond a strain of about 8% the deformation is elastic to about 15% when it becomes plastic. Upon reduction of the stress level the material first returns to a constant stress plateau where the martensite phase transforms back to the austenite. Upon completion of the transformation at about a 2% strain the strain returns to zero if no permanent deformation has occurred.
An atherectomy catheter or other intracorporeal catheter with a flexible housing in accordance with the invention may be used in essentially the same manner of prior catheters, except for the notable difference that the characteristics of the housing can be changed within
the patient's body by changing the temperature of the housing therein. If the housing is in the martensite phase at body temperature and the housing has been provided with a desired "remembered shape" at an austenite transformation temperature above body temperature, the housing may be heated within the body to a temperature at or above the
A50 of the shape memory alloy so that the housing will transform to essentially the shape remembered. If the housing is in the austenite phase at body temperature and it is desired to transform the austenite phase to the lower strength martensite, e.g. when it is desired to have a more flexible housing such as when moving the housing through tortuous passageways, the temperature of the housing can be reduced to a temperature at or less than the M50 of the shape memory alloy. By allowing the housing to return to body temperature, the martensite transforms back to austenite and the shape of the housing returns to the remembered shape suitable for the procedure, e.g. straight.
The temperature of the housing can be changed when the catheter is within the patient's body by a variety of suitable means. For example, the temperature of the housing can be raised by resistance/ inductance heating with electrical conductors in contact with or formed integral with the housing. One convenient method of heating the housing with atherectomy catheters which have cutting elements within the housing which fictionally engage the housing is to move the cutting element within the inner chamber with sufficient velocity to raise the temperature of the housing to the desired level above body temperature. Other means of heating the housing within the patient's body include directing a fluid at elevated temperature through an inner lumen of the catheter which is in fluid communication with the interior of the housing. RF heating may also be employed as will be recognized by those skilled in the art. If it is desired to lower the temperature of the housing, a fluid at a temperature less than body temperature may be directed through an inner lumen within the catheter to the interior of the housing.
While the housing of the present invention has been described herein in terms of certain presently preferred embodiments directed to atherectomy catheters, those skilled in the art will recognize that it may be used in a wide variety of intracorporeal devices for performing diagnostic or therapeutic procedures within a patient's body lumen or body cavity. Various modifications and improvements can also be made to the invention without departing from the scope thereof.
Claims
1. An elongated catheter for insertion within a body lumen or cavity, comprising: a) a catheter shaft having proximal and distal ends and at least one inner lumen extending therein; and b) an elongated flexible housing mounted on a distal portion of the catheter shaft which is formed of a shape memory alloy and which has an inner chamber and which has an opening in a wall portion of the housing in communication with the inner chamber; and c) means disposed within the inner chamber for performing a diagnostic or therapeutic procedure within a body lumen.
2. The catheter of claim 1 including an inflatable positioning member mounted on the housing and having an interior in fluid communication with the inner lumen extending within the catheter shaft.
3. The catheter of claim 1 wherein the shape memory alloy consists predominantly of an intermetallic compound of nickel and titanium.
4. The catheter of claim 3 wherein the intermetallic compound contains approximately equiatomic amounts of nickel and titanium.
5. The catheter of claim 3 wherein the shape memory alloy includes an intermetallic compound of nickel and titanium of the formula Ni14Ti11 f Ni3Ti2 or Ni3Ti.
6. The catheter of claim 3 wherein the shape memory alloy includes an intermetallic compound of nickel and titanium of the formula Ti2Ni.
7. The catheter of claim 3 wherein at least a portion of the flexible housing is in a heat treated condition.
8. The catheter of claim 7 wherein the shape memory alloy is in a martensite phase at body temperature.
9. The catheter of claim 8 wherein the alloy has been thermomechanically processed to have a final austenite transformation temperature above body temperature so as to exhibit shape memory effects when heated to an austenite transformation temperature.
10. The catheter of claim 9 wherein the alloy has an austenite transformation temperature above body temperature."
1 1 . The catheter of claim 10 wherein the alloy has an A50 above body temperature.
12. The catheter of claim 1 wherein the catheter has treatment or diagnostic means within the inner chamber of the housing including a tissue removal system.
13. The catheter of claim 12 wherein a housing opening is located in one side of the housing and is adapted to receive tissue to be removed by the tissue removal system disposed within the inner chamber of the housing.
14. The catheter of claim 13 wherein an inflatable positioning balloon is disposed on a side of the housing opposite the housing opening.
15. The catheter of claim 1 wherein the housing has been finally cold worked at least 10%.
16. The catheter of claim 15 wherein a portion of the cold worked housing has been heat treated.
17. The catheter of claim 16 wherein the housing is a cylindrically shaped tubular member.
18. The catheter of claim 17 wherein the cylindrically shaped tubular member has at least one cylindrically shaped section along a length thereof which is formed of material softer than adjacent cylindrically shaped sections.'
19. The catheter of claim 18 wherein the cylindrically shaped section formed of softer material is in a martensite phase.
20. The catheter of claim 19 wherein a cylindrically shaped section adjacent the cylindrically shaped section formed of softer material is in a cold worked martensite phase which has not been significantly heat treated.
21. The catheter of claim 16 wherein at least a portion of the housing is in the austenite phase with an Af temperature at or below body temperature.
22. The catheter of claim 21 wherein the austenite phase exhibits a stress induced transformation to a martensite phase at body temperature.
23. The catheter of claim 17 wherein the heat treated section is in the martensite phase.
24. A housing for use within a patient's body lumen or cavity which is formed of a cold worked, shape memory alloy and which has at least one section thereof in a heat treated condition.
25. The housing of claim 24 wherein at least one heat treated section is in a martensite phase.
26. The housing of claim 24 in an elongated tubular shape with the inner chamber extending the length thereof.
27. The housing of claim 25 wherein at least one heat treated section is tubular in shape.
28. The housing of claim 24 wherein the shape memory alloy is predominately a NiTi intermetallic compound.
29. The housing of claim 28 wherein a heat treated section is in the martensite phase.
30. The housing of claim 29 wherein the martensite phase transforms to an austenite phase with a final austenite transformation temperature above body temperature.
31 . The housing of claim 30 wherein a heat treated section in the martensite phase extends along a substantial part of the housing length.
32. The housing of claim 31 wherein the martensite phase in the heat treated section extending a substantial part of the length of the elongated tubular housing is transformable to an austenite phase having a straight memory when heated to a final austenite transformation temperature above body temperature.
33. The housing of claim 32 wherein the transformation of the martensite phase to the austenite phase with a straight memory straightens the housing in the event the housing is deformed in use.
34. The housing of claim 30 wherein an opening is provided in a wall portion of the housing and the portion of the wall defining the opening is in a martensite phase which is transformable to an austenite phase with a straight memory by heating to a final transformation temperature above body temperature.
35. An atherectomy catheter comprising: a) a catheter shaft having proximal and distal ends and at least one inner lumen extending therein; b) an elongated flexible cutter housing mounted near the distal end of the catheter shaft which is formed of a shape memory alloy, which has an inner chamber extending therein and which has an opening in a wall portion of the housing in fluid communication with the inner chamber; and c) means disposed within the inner chamber for severing tissue within a patient's body lumen or cavity which is urged into the inner chamber through the opening in the wall portion of the housing.
36. The atherectomy catheter of claim 35 including means on a distal portion of the catheter to position the cutter housing within a body lumen or cavity.
37. The atherectomy catheter of claim 36 wherein the means to position the cutter housing is an expandable means secured to a side portion of the housing opposite the opening.
38. The atherectomy catheter of claim 37 wherein the expandable means is an inflatable member.
39. The atherectomy catheter of claim 35 wherein the means to sever tissue is a cutting blade slidably disposed within the inner chamber of the cutter housing so as to sever tissue which is urged into the inner chamber through the opening in the side portion of the housing.
40. The atherectomy catheter of claim 35 wherein the housing has at least one section thereof in a heat treated condition.
41. The atherectomy catheter of claim 42 wherein at least one heat treated section is in the martensite phase.
42. The atherectomy catheter of claim 40 wherein the housing is in an elongated tubular shape with the inner chamber extending the length thereof.
43. The atherectomy catheter of claim 41 wherein at least one heat treated housing section is tubular in shape.
44. The atherectomy catheter of claim 35 wherein the housing is formed of a shape memory alloy which is predominately a NiTi intermetallic compound.
45. The atherectomy catheter of claim 44 wherein a heat treated housing section is in the martensite phase.
46. The atherectomy catheter of claim 45 wherein the martensite phase transforms to an austenite phase with a final transformation temperature above body temperature.
47. The atherectomy catheter of claim 46 wherein a heat treated housing section in the martensite phase extends along a substantial part of the housing length.
48. The atherectomy catheter of claim 47 wherein the martensite phase in the heat treated housing section extending a substantial part of the length of the elongated tubular housing is transformable to an austenite phase having a straight memory when heated to a final austenite transformation temperature above body temperature.
49. The atherectomy catheter of claim 48 wherein the transformation of the martensite phase to the austenite phase with a straight memory in the heat treated housing section straightens the housing in the event it has become deformed in use.
50. The atherectomy catheter of claim 49 wherein the wall portion of the housing defining the opening therein is in a martensite phase which is transformable to austenite with a straight memory by heating to a final transformation temperature above body temperature.
51. The atherectomy catheter of claim 35 wherein the shape memory alloy exhibits stress induced transformation of martensite phase to austenite phase.
52. The atherectomy catheter of claim 51 wherein the shape memory alloy has a final austenite transformation temperature below body temperature.
53. An intracorporeal housing which has a chamber therein and which is made of a shape memory alloy with at least one significant portion of the housing being relatively flexible and at least one significant portion of the housing being relatively stiff.
54. The intracorporeal housing of claim 53 wherein the shape memory alloy contains substantial amounts of NiTi intermetallic compound.
55. The intracorporeal housing of claim 54 wherein the relatively stiff portion of the housing is in a cold worked condition and the relatively flexible portion is in a heat treated condition.
56. The intracorporeal housing of claim 55 wherein the relatively flexible portion is in a martensite phase.
57. The intracorporeal housing of claim 56 wherein the martensite phase is stable at body temperature.
58. The intracorporeal housing of claim 57 wherein the martensite phase is transformable by heating to a temperature above a transformation temperature to an austenite phase with a shape memory.
59. A method of making a flexible hollow member or housing for intracorporeal use comprising: a) forming a cold worked hollow body of shape memory alloy having an interior chamber extending therein; and b) heat treating at least one section of the cold worked hollow body to stress relieve the cold worked material therein and leaving at least one cold worked section in the hollow body.
60. The method of claim 59 wherein the hollow body is formed of a NiTi alloy.
61 . The method of claim 60 wherein the heat treated sections of the hollow body are in a martensite phase.
62. The method of claim 61 wherein the martensite phase is transformable to an austenite phase by heating to a temperature above body temperature.
63. The method of claim 62 wherein the martensite phase extends in a linear fashion along the length of the hollow body.
64. The method of claim 63 wherein the austenite phase has a straight memory.
65. In a method of performing an intracorporeal procedure within a patient's body lumen or cavity the steps including: a) providing an intravascular catheter comprising: a catheter shaft having proximal and distal ends and at least one inner lumen extending therein; an elongated flexible cutter housing mounted near the distal end of the catheter shaft which is formed of a shape memory alloy, which has an inner chamber extending therein and which has an opening in a wall portion of the housing in fluid communication with the inner chamber; and means disposed within the inner chamber of the housing for performing an intracorporeal procedure within a patient's body lumen or cavity; b) advancing the catheter within the patient's body to a location within the desired body lumen or cavity; c) adjusting a characteristic of the catheter housing at body temperature by changing the temperature of the housing within the patient's body; and d) returning the temperature of the housing to body temperature.
66. The method of claim 65 wherein the characteristic of the catheter housing is adjusted before an intracorporeal procedure is performed.
67. The method of claim 65 wherein the temperature of the housing is raised to a transformation temperature above body temperature at or above the A50 of the shape memory alloy.
68. The method of claim 67 wherein the shape memory alloy is in the martensite phase at body temperature.
69. The method of claim 65 wherein the temperature of the housing is lowered to a transformation temperature below body temperature at or below the M50 of the shape memory alloy.
70. The method of claim 69 wherein the shape memory alloy is in the austenite phase at body temperature.
71 . The method of claim 65 wherein the shape memory alloy comprises a predominant amount of nickel-titanium intermetallic compound.
72. In a method of performing an atherectomy procedure within a patient's artery, the steps including: a) providing an atherectomy catheter comprising: a catheter shaft having proximal and distal ends and. at least one inner lumen extending therein; an elongated flexible cutter housing mounted near the distal end of the catheter shaft which is formed of a shape memory alloy, which has an inner chamber extending therein and which has an opening in a wall portion of the housing in fluid communication with the inner chamber; and cutting means disposed within the inner chamber of the cutter housing for severing tissue urged into the inner chamber; b) advancing the catheter within the patient's body to a location within the desired artery; c) adjusting a characteristic of the catheter housing at body temperature by changing the temperature of the housing within the patient's body; and d) returning the temperature of the housing to body temperature.
73. The method of claim 72 wherein the temperature of the cutter housing is raised by frictional engagement with the cutter when it is advanced within the housing.
74. The method of claim 72 wherein the temperature of the cutter housing is raised by resistance or inductance heating.
75. The method of claim 72 wherein the temperature of the cutter housing is changed by fluid advanced through an inner lumen which is in fluid communication with the interior of the cutter housing.
76. The method of claim 75 wherein the temperature of the fluid advanced through the inner lumen in fluid communication with the interior of the cutter housing is above body temperature.
77. The method of claim 76 wherein the temperature of the fluid is at or above the A50 for the shape memory alloy.
78. The method of claim 75 wherein the temperature of the fluid advanced through the inner lumen in fluid communication with the interior of the cutter housing is below body temperature.
79. The method of claim 78 wherein the temperature of the fluid is at or below the M50 for the shape memory alloy.
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
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US08/088,930 US5514115A (en) | 1993-07-07 | 1993-07-07 | Flexible housing for intracorporeal use |
US08/088,930 | 1993-07-07 |
Publications (1)
Publication Number | Publication Date |
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WO1995001753A1 true WO1995001753A1 (en) | 1995-01-19 |
Family
ID=22214351
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
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PCT/US1994/007766 WO1995001753A1 (en) | 1993-07-07 | 1994-07-06 | Flexible housing for intracorporeal use |
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US (3) | US5514115A (en) |
WO (1) | WO1995001753A1 (en) |
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1994
- 1994-07-06 WO PCT/US1994/007766 patent/WO1995001753A1/en active Application Filing
-
1996
- 1996-01-23 US US08/590,206 patent/US5776114A/en not_active Expired - Lifetime
-
1997
- 1997-08-22 US US08/924,408 patent/US5948184A/en not_active Expired - Lifetime
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Cited By (2)
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---|---|---|---|---|
US6113615A (en) * | 1999-02-03 | 2000-09-05 | Scimed Life Systems, Inc. | Atherectomy burr including a bias wire |
US6299623B1 (en) | 1999-02-03 | 2001-10-09 | Scimed Life Systems, Inc. | Atherectomy burr including a bias wire |
Also Published As
Publication number | Publication date |
---|---|
US5776114A (en) | 1998-07-07 |
US5948184A (en) | 1999-09-07 |
US5514115A (en) | 1996-05-07 |
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