Catheter tubing with improved stress-strain characteristics

Abstract

A medical tubing is disclosed which includes a first material extending between proximal and distal ends of the tubing and which defines a lumen of the tubing. The tubing also includes a second material extending between at least portion of the distance between the proximal and distal ends of the tubing and that is embedded in the first material. The second material is fractured. The first material is flexible and the second material is relatively rigid and brittle and the two materials combined to provide a medical tubing that exhibits strain softening behavior.

1 - 23 . (canceled)  
   
   
       24 . A method of manufacturing a medical tubing comprising the steps of: 
 co-extruding a first material having a first stiffness and a second material having a second stiffness to form a tubular shaft, the second stiffness being greater than the first stiffness;    cooling the first and second materials;    stretching the first and second materials; and    fracturing the second material.    
   
   
       25 . The method of making a medical tubing of  claim 24 , wherein the first material has a low flexural modulus and a high break elongation.  
   
   
       26 . The method of making a medical tubing of  claim 25 , wherein the low flexural modulus of the first material ranges from about 100 mPa to about 2,000 mPa.  
   
   
       27 . The method of making a medical tubing of  claim 25 , wherein the high break elongation of the first material ranges from about 100% to about 1,000%.  
   
   
       28 . The method of making a medical tubing of  claim 25 , wherein the low flexural modulus of the first material ranges from about 100 mPa to about 2,000 mPa and the high break elongation of the first material ranges from about 100% to about 1,000%.  
   
   
       29 . The method of making a medical tubing of  claim 24 , wherein the second material has a high flexural modulus and a low break elongation.  
   
   
       30 . The method of making a medical tubing of  claim 29 , wherein the high flexural modulus of the second material ranges from about 2,000 mPa to about 20,000 mPa.  
   
   
       31 . The method of making medical tubing of  claim 29 , wherein the low break elongation of the second material ranges from about 0.1% to about 10%.  
   
   
       32 . The method of making medical tubing of  claim 29 , wherein the high flexural modulus of the second material ranges from about 2,000 mPa to about 20,000 mPa and the low break elongation of the second material ranges from about 0.1% to about 10%.  
   
   
       33 . The method of making a medical tubing of  claim 24 , wherein the first material has a low flexural modulus and a high break elongation, and the second material has a high flexural modulus and a low break elongation.  
   
   
       34 . The method of making a medical tubing of  claim 33 , wherein the low flexural modulus of the first material ranges from about 100 mPa to about 2,000 mPa and the high break elongation of the first material ranges from about 100% to about 1,000% and the high flexural modulus of the second material ranges from about 2,000 mPa to about 20,000 mPa and the low break elongation of the second material ranges from about 0.1% to about 10%.  
   
   
       35 . A method of manufacturing and using a medical tubing comprising the steps of: 
 co-extruding a first material having a first stiffness and a second material having a second stiffness to form a tubular shaft, the second stiffness being greater than the first stiffness;    cooling the first and second materials;    cutting the tubular shaft;    inserting the tubular shaft into a vascular system of a patient;    stretching the first and second materials in vivo as the tubular shaft travels through the vascular system;    fracturing the second material in vivo;    performing a medical procedure using the tubing within the vasculature system; and    removing the tubular shaft from the vascular system of the patient.    
   
   
       36 . The method of making a medical tubing of  claim 35 , wherein the first material has a low flexural modulus and a high break elongation.  
   
   
       37 . The method of making a medical tubing of  claim 36 , wherein the low flexural modulus of the first material ranges from about 100 mPa to about 2,000 mPa.  
   
   
       38 . The method of making a medical tubing of  claim 36 , wherein the high break elongation of the first material ranges from about 100% to about 1,000%.  
   
   
       39 . The method of making a medical tubing of  claim 36 , wherein the low flexural modulus of the first material ranges from about 100 mPa to about 2,000 mPa and the high break elongation of the first material ranges from about 100% to about 1,000%.  
   
   
       40 . The method of making a medical tubing of  claim 35 , wherein the second material has a high flexural modulus and a low break elongation.  
   
   
       41 . The method of making a medical tubing of  claim 40 , wherein the high flexural modulus of the second material ranges from about 2,000 mPa to about 20,000 mPa.  
   
   
       42 . The method of making medical tubing of  claim 40 , wherein the low break elongation of the second material ranges from about 0.1% to about 10%.  
   
   
       43 . The method of making medical tubing of  claim 40 , wherein the high flexural modulus of the second material ranges from about 2,000 mPa to about 20,000 mPa and the low break elongation of the second material ranges from about 0.1% to about 10%.  
   
   
       44 . The method of making a medical tubing of  claim 35 , wherein the first material has a low flexural modulus and a high break elongation, and the second material has a high flexural modulus and a low break elongation.  
   
   
       45 . The method of making medical tubing of  claim 44 , wherein the low flexural modulus of the first material ranges from about 100 mPa to about 2,000 mPa, the high break elongation of the first material ranges from about 100% to about 1,000%, the high flexural modulus of the second material ranges from about 2,000 mPa to about 20,000 mPa and the low break elongation of the second material ranges from about 0.1% to about 10%.