Catheter for dilating stenotic lesions

Abstract: A catheter for dilating stenotic lesions has an elongated body (I) with at least one lumen (12) extending therethrough. A tip (T), constructed of materials softer than the elongated body is attached to the distal end of the body. The tip segment has at least one lumen (14) passing therethrough which is in alignment with the lumen (12) in the elongated body. A guide is adapted to pass through the aligned lumens. A balloon (D) is connected to the distal segment of the elongated body over its outer periphery, thereby creating a balloon cavity (24) therebetween. At least one additional lumen (A) is provided in the elongated body in flow communication with the balloon cavity, for selective inflation and deflation thereof, with a contrast fluid.

Description: FIELD OF THE INVENTION The invention relates to the field of surgery, and more particularly to instruments for facilitating the performance of surgical procedures involving the flow of blood. This technique has been generally described as percutaneous transluminal angioplasty. BACKGROUND OF THE INVENTION Obstructive coronary artery disease is generally regarded as a serious health problem in the United States and most of the western world. When drug treatment fails or inadequately controls angina pectoris, coronary artery bypass graft surgery is generally used. In 1964 a translumenal coaxial catheter dilation method for dilating atheromatous lesions in peripheral arteries was introduced by Dotter and Judkins. This technique required sequential dilation of stenotic lesions and employed progressively larger dilating catheters. Subsequently in 1971 a "Fogarty balloon catheter" was used to perform translumenal arteriolplasty. Subsequently, Gruntzig employed earlier techniques using a single double lumen catheter with a nondistensible balloon segment at its tip which was positioned in the lumen at the stenotic segment of a peripheral artery. The elastic balloon segment was then inflated, resulting in compression of the atheromatous lesion in a manner perpendicular to the vessel, thus dilating the lumen. The balloon remained inflated for ten to fifteen seconds at seven atmospheres internal pressure and was then deflated. As a result, there was a significant reduction in complications due to endothelial damage, such as that caused by earlier known coaxial translumenal dilation technique and thus a marked improvement in vessel patency through the use of the Gruntzig catheter was achieved. In earlier designs, the amount of pressure which could be applied through a balloon type expander was limited and thus insufficient to dilate certain stenotic lesions. This shortcoming was due to the use of polyvinylchloride balloons which had structural limitations that limited internal pressures to approximately seven atmospheres. Other catheter designs resulted in a total cessasion of blood flow distal to the site of the treatment. Studies in living dogs with normal coronary arteries have shown that coronary translumenal angioplasty may be associated with brief, self-limited ventricular tachycardia. During the inflation of the balloon, distal coronary pressure falls to zero. Because of the lack of blood flow and the pressure distal to the treatment site the period of use such known catheters must be relatively short to prevent complications due to the lack of blood supply. This limitation on inflation time tended to reduce the success rate of the coronary translumenal angioplasty. The translumenal coronary angioplasty technique consists of a catheter system introduced via the femoral artery under local anesthesia. A preshaped guiding catheter is positioned into the orifice of the coronary artery and through this catheter a second dilation catheter is advanced into the branches of the coronary artery. The dilation catheter had an eliptical shape distensible balloon portion near its tip which could be inflated and deflated. After traversing the stenotic lesion of the coronary artery, the distensible portion was inflated with fluid which compressed the atherosclerotic material in a direction generally perpendicular to the wall of the vessel thereby dilating the lumen of the vessel. Peripheral arterial lesions treated by this technique have demonstrated that the atheroma can be compressed leaving a smooth luminal surface. Studies have shown that the patency rate two years following the dilation of the iliac and femoropopliteal atherosclerotic lesions was greater than seventy percent. Although guiding catheters are used in placement of angioplasty (dilation) catheters, the angioplasty catheter can be placed in a stenotic lesion using solely the wire guide if the lesion is proximately located to the point of entry in the body. The word "guide" as referred to in this application is directed to both wire guides and guiding catheters separately or as used in tandem. Typically a guide of appropriate size is advanced through the stenotic lesion and the balloon catheter is threaded over it and advanced to the area of the stenosis. Once the area of the stenosis is reached, the balloon in the catheter is inflated to a high pressure depending on the size of the balloon and the type of stenosis, and the pressure is held for a period of time. During the procedure the distal and proximal pressure is measured to evaluate the physiological conditions of the organ. More specifically, the pressure differential is measured after deflating the balloon and is used as an indication of the degree of dilation achieved. Past designs have employed a stiff catheter tip on the angioplasty catheter which often resulted in pulling the guide out of the stenoic lesion as the catheter was advanced toward the legion. Separately, in using the angioplasty catheter, it was often necessary to measure the pressure distal to the catheter. Past designs employed a guide closely fitting to the internal cross section of the distal lumen in the catheter thereby making it difficult to obtain adequate pressure measurements due to the large pressure drops involved as a result of the usage of close clearances. The pressure measurements were of the nature of a dynamic measurement, the accuracy and frequency response of which was greatly and adversely affected by the pressure drops within the catheter measurement lumen. It was frequently required that the guide be retracted and replaced in order to achieve accurate pressure measurement. The use of angioplasty catheters often made it necessary to infuse drugs or oxygenated blood, distal to the stenosis to provide adequate physiological function of the organ in question. Past designs did not provide for such a separate lumen to carry drugs necessary to prevent undue contractions of the arterial wall as a result of the insertion of the angioplasty catheter. To the extent such drugs were necessary to relax the arterial wall, the lumen through which the guidewire passed served the auxillary function of a drug injection port. However, usage of the same lumen for pressure measurement as well as infusion of drugs or other fluids impeded the ability to maintain continuous and accurate pressure measurements. Angioplasty catheters used in the past had relatively large catheter body diameters which tended to occlude the artery of concern causing reduced blood flow to the lesion or the organ it supplies. One such catheter is disclosed in U.S. Patent 4,323,071 (Fig. 4). Other catheters although using a tapered body, employed a rigid tip which, if the arterial path was particularly tortuous, tended to pull the guide wire from the stenosis. One such catheter is disclosed in U.S. Patent 4,413,989 (Fig. 8). Flexible tips attached to the distal end of an angiographic catheter have been used to inject radiopaque contrast or medicaments into the femoral artery as part of diagnostic or treatment procedures. Such deformable tips had the object of preventing punctures of the wall of the aorta and have been provided to have a larger cross-sectional profile than the catheter body to which they are attached. Some designs even featured means to inflate the deformable tip to increase the contact area between the tip and the body tissue to reduce the pressure per unit area applied to the tissue. One such design is disclosed in U.S. Patent 4,531,943. In past designs it was often difficult to estimate the location of the tip of the catheter. Prior designs employed the use of a gold band near the distal end of the catheter thereby making that portion of the catheter visible under an x-ray machine. However, because it was risky to attach such rings at the extreme distal end of the catheter, the extreme distal tip of the catheter was not visible under x-ray and often the physician performing the procedure had to guess as to its location. This shortcoming of past catheters has been addressed in the catheter of the present invention by the provision of a radiopaque tip. Known angioplasty catheters have dilation balloons attached to the catheter body by adhesives or by heat sealing. Most often, these balloons are made out of polyvinylchloride or irradiated polyethylene. Polyvinylchloride balloons are normally solvent or adhesive bonded to catheter bodies of the same material and polyethylene balloons are adhesive bonded or heat shrunk to catheter bodies of the same material, or a blend of polyethylene and polypropylene, so as to obtain catheter body stiffness. Most such catheters have relatively stiff tips at their distal end which often causes the preplaced guide to be pulled out of the lesion area during catheter advancement in tortuous arteries as well as intimal damage. Known catheters also contain relatively stiff bodies to carry the balloon adjacent the distal end of the catheter. The stiffness of the catheter body continues in the area of the balloon up to the distal end of the catheter. Known catheters contain balloon lumen bleed holes whereby air can be removed directly out of the balloon cavity and out of the catheter during the filling of the balloon. These additional lumens either in the form of small metal tubes or as a multilumen catheter tube, consumed valuable cross-sectional area of the catheter tube that otherwise could be used for other purposes such as pressure measurements. Known catheter designs have employed an inner and outer tube wherein the outer tube contains the balloon as an integral portion thereof or a separate balloon which is bonded to the outer tube. The annulus between the inner and outer tubes is used for inflation of the balloon. Known angioplasty catheters have been shipped in a sterilized condition to doctors and hospitals with the balloon in a deflated condition and having gas entrained therein. Prior to using such catheters, doctors or technicians had to inject a contrast fluid into the balloon to displace the gases therein. This procedure involved sequential filling and evacuation of balloon using a plunger connected to the proximal end of the catheter. Such catheters were shipped to doctors and hospitals with the balloon in a wing-folded condition. Essentially wing folding involved flatening of the balloon along the catheter body and folding the balloon over onto the catheter body in two segments which resemble wings coming from a fuselage. In the past, the catheters were wing-folded in the factory prior to shipment. However, in order to remove the entrained gases, the doctor or technician had to unfold the wings and fill the balloon with contrast fluid while evacuating gases therefrom. As a result the advantage of the balloon tending to retain its wing-folded position after shipment was lost. The doctor or technician after filling the balloon with contrast fluid had to again attempt to manipulate the balloon with his or her fingers to reachieve the wing-folded position which reduced the profile of the catheter. The catheter of the present invention addresses this problem by prefilling the catheter with contrast fluid and placing a sleeve over the balloon after it has been wing-folded. Accordingly, the advantage of the wing-folding is retained and the doctor merely removes the sleeve and the sterile catheter is ready for insertion, with the balloon in a low profile position. Document WO 87/00442 discloses a dilatation catheter or a balloon catheter assembly. The dilatation catheter has a balloon portion which expands when the catheter is pressurized, the catheter comprising: A shaft of elastomeric material reinforced with filaments, a portion of the shaft being capable when internally pressurized of the expansion in diameter to provide the balloon, the filaments of the balloon portion lying at an angle which is less than a predetermined critical angle relativ to the axis, whereby, when the balloon portion is expanded under pressure, expansion of the balloons stops when the filaments lie at the critical angle. The dilatation catheter further includes inner tube means coaxially disposed inside the shaft. Furthermore, GB-A-2 172 205 discribes a dilatation catheter wherein a shaft of the catheter comprises a tube of braided material having a uniform coating on the outer surface thereof. The catheter has a major portion of its length over which the braided material has more picks per unit length than it has over a minor portion whereby the said minor portion is inflatable in response to the application of an inflating fluid thereto, and said major portion is not. The shaft further comprises an inner tube of impervious elastic material located inwardly of the tube of braided material and extending over the length of the catheter, and/or the major and minor portions are coniguous and the outer coating is bonded to the tube of braided material. Moreover, document EP-A-0 260 711, a document according to Article 54(3) and (4) EPC discloses a catheter instrument for treating patients for aortic stenosis. An aortic valvuloplasty dilatation catheter according to this document comprises a multilumen catheter having a dilatation balloon and pressure sensing port means adapted for measuring pressure in the left ventricle of the heart. Furthermore, the balloon has a smaller and a larger balloon section with different inflating diameters. It is an object of the present invention to provide an angioplasty catheter which can be used to dilate a stenosis in progressively increasing dimensional increments. It is an object of this invention to provide in one embodiment a soft atraumatic catheter tip in which radiopaque fillers such as bismuth-oxychloride or bismuth-subcarbonate are incorporated. It is an object of the invention to provide in one embodiment a relatively soft catheter tip to minimize the tendency of the catheter to dislocate a guide out of a stenosis when the catheter is advanced in a tortuous path, and also minimize intimal damage. It is another object of this invention to provide in one embodiment a catheter tip which can be insert molded, heat bonded, or adhesive bonded to the relatively stiff catheter body proximal to it. It is a further object of this invention to use material such as nylon, polyvinylchloride, polyurethane, of different stiffnesses that are readily bondable using the aforementioned methods. It is a further object of this invention to provide in one embodiment an inner tube that is relatively large in its internal diameter and that is necked down in the region of the balloon and for several centimeters proximal to the balloon in order to provide a large lumen for pressure measurement. The catheter provides an improved frequency response without sacrificing the total overall outside diameter and maintaining a relatively small diameter in the region of the balloon thereby maintaining a low profile catheter design. It is a further object of this invention in one of its alternate embodiments to provide a bleed lumen to bleed gases out of the balloon wherein the lumen extends within the wall of the outer tube thereby avoiding sacrificing any of the catheter cross-sectional area for other lumens thereby allowing such other lumens to be of maximum cross-sectional area within a low profile catheter. It is a further object of this invention to provide, in one embodiment, an opening into the balloon cavity at its extreme distal end thereby facilitating the removal of gases during filling with contrast fluid. SUMMARY OF THE INVENTION The present invention comprises an angioplasty catheter having an elongated body, a balloon and means for inflation of a balloon, wherein said elongated body comprises an inner body member and an outer body member in a coaxial arrangement and wherein the angioplasty catheter is further characterised in that the inner and outer body member define an annulus between them for inflating the balloon, and said balloon has a plurality of stages of differing outside diameters when said balloon has been inflated, whereupon the same catheter can be used to dilate a stenosis in progressively increasing dimensional increments. The present invention further comprises an angioplasty catheter has an elongated body with at least one lumen extending therethrough. A tip, constructed of materials softer than the elongated body is attached to the distal end of the body. The tip segment has at least one lumen passing therethrough which is in alignment with the lumen in the elongated body. A guide is adapted to pass through the aligned lumens. A balloon is connected to the distal segment of the elongated body over its outer periphery, thereby creating a balloon cavity therebetween. At least one additional lumen is provided in the elongated body in flow communication with the balloon cavity, for selective inflation and deflation thereof, with a contrast fluid. Brief Description of the Drawings Figs. 1 to 7 and 10 show embodiments of catheters which illustrate some features that also apply to the invention. Figs. 8 and 9 are the only figures that show a catheter with a balloon according to the invention with several stages. Fig. 1 is a sectional elevational view of one a catheter showing some features of the present invention employing a coaxial design and having a tip with an outside shoulder. Fig. 2 is a sectional elevational view of the coaxial design as shown in Fig. 1 with an alternative balloon mounting. Fig. 3 is a sectional elevational view of the coaxial design of Fig. 1 showing an alternative mounting of the proximal end of the balloon. Fig. 4 is a sectional elevational view of an alternative mounting of the distal end of the balloon; Fig. 5 is a sectional elevational view of an embodiment, of the tip showing a spring embedded therein; --Fig. 6 is a schematic representation of an embodiment of an angioplasty catheter showing pressure measurement techniques using externally mounted transducers; Fig. 7 is a schematic representation of an embodiment of an angioplasty catheter illustrating placement of pressure sensing transducers on the catheter. Fig. 8 is a sectional view of the distal end of an angioplasty catheter according to the present invention illustrating a two stage balloon; Fig. 9 is a detailed sectional view of the area shown in the dashed circle in Fig. 8; Fig. 10 is a representation of an embodiment of an angioplasty catheter as shown in Fig. 1 illustrating several unique dimensional relationships therein.-- DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENT The catheter C of the present invention has several embodiments described hereinbelow and illustrated in the figures. Fig. 1 illustrates a coaxial design for a catheter having an inner body member I, an outer body member B. Annulus A is defined between inner body member I and outer body member B. A tip T is connected to inner body member I. A balloon D is connected to outer body member B on one end and adjacent the distal end 10 of inner body member I. As shown in Fig. 1, inner body member I has at least one lumen 12 therein and extending therethrough. Tip T has an axial lumen 14 which is aligned with lumen 12 when tip T is affixed to distal end 10 of inner body member I. As seen in Figs. 1 and 2, inner body member I extends beyond outer body member B. As previously stated, one of the objectives of the catheter C of the present invention is to provide for a low profile without, at the same time affecting the sensitivity of dynamic pressure measurements within the artery in question. To this end, lumen 12 has a relatively large cross-sectional area as shown by arrow 16 for substantially the entire length of the catheter. However, in order to avoid impeding the blood flow into the stenotic region in which the angioplasty procedure is to take place, it is desirable to have the distal end 18 of the catheter assembly C as small as possible to avoid interruption of blood flow. Accordingly, inner body member I has a tapered segment 20 which in effect necks down the cross-sectional area of lumen 12 from the section as shown by arrow 16 to a smaller cross-sectional area shown by 22. As shown in Fig. 1, balloon D, which is preferably constructed of polyethylene or polyester, has an elongated shape which defines an annular cavity 24 between the outer surface 26 of inner body member I and the inner surface 28 of balloon D. Cavity 24 is in flow communication with annulus A. Cavity 24 is capped off at its distal end 30 (Fig. 2) in one of several alternative methods. In the first alternative, balloon D has a distal neck 32 which is bonded, sealed or otherwise joined, using methods known in the art, to the outer surface 26 of inner body member I. Tip T has an internal mounting shoulder 34 (Fig. 2) which includes annular surface 36 and radial surface 38 adjacent thereto. Tip T is butted against the distal surface 40 of inner body member I as can readily be seen in Fig. 2. Tip T is secured to inner body member I, by methods known in the art on at least two adjacent surfaces: to wit, 36 and 38. Tip T can be further secured to the catheter C by connecting distal neck 32 of balloon D to radial surface 42 of balloon D. With the above-described arrangement, the distal end 18 (See Fig. 1) of the catheter C maintains a low profile as the outer surface 44 of balloon D at distal neck 32 is maintained substantially flush to the outer surface 46 of tip T. Alternatively, as shown in Fig. 1, tip T can have the same internal shoulder design 34 as illustrated in Fig. 2. In the alternative design shown in Fig. 1, tip T has an external mounting shoulder 48 which has a annular surface 50 and a radial surface 52 adjacent thereto. Distal neck 32 of balloon D is secured to annular surface 50 and radial surface 52 of tip T. The connection method illustrated in Fig. 1 provides additional security in mounting of tip T in that apart from contact between inner body member I and annular surface 36 and radial surface 38, of internal mounting shoulder 34, additional mounting points exist due to the bond between distal neck 32 and external mounting shoulder 48. It is to be understood that distal neck 32 can be secured to external mounting shoulder 48 by various means known in the art. Similarly, shoulder 34 can be secured to inner body member I by known means. The mounting method illustrated in Fig. 1 results in outer surface 44 of balloon D adjacent neck 32 being flush with outer surface 46 of tip T. However, due to the use of the external shoulder, the profile of catheter C as illustrated in Fig. 1 is slightly larger than the profile illustrated in Fig. 2. Fig. 4 illustrates yet another alternative embodiment for securing tip T to the distal end 40 of inner body member I. Tip T is preferably melt bonded to distal end 40 and has an outer periphery similar to outer surface 26 of inner body member I. Accordingly, outer surface 46 of tip T is aligned with outer surface 26 of inner body member I. The distal neck 32 of balloon D spans the melt bonded joint 76 between tip T and inner body member I. A tapered transition 78 is provided between outer surface 44 of balloon D and outer surface 46 of tip T, to avoid damage to the arterial wall during insertion and removal of the catheter C. The inner surface 28 of balloon D is preferably connected to both the outer surface 26 of inner body member I and the outer surface 46 of tip T by known methods. Alternatively, inner surface 28 may be joined solely to outer surface 46 although it may also contact surface 26. As a result, the proximal neck 32 secures tip T to inner body member I, annularly with tip T also connected to inner body member I along matched radial surfaces making up joint 76. The arrangement shown in Fig. 4 also presents a low profile for the catheter C while adding the advantages of a flexible tip to counteract the tendency of an otherwise stiff catheter to dislocate the guide from the stenosis where a particularly tortious arterial path must be negotiated to reach the stenosis. Experience has shown that distal neck 32 of balloon D can be fabricated to be 0,01cm (.004 inches) thick. The proximal end 54 (Fig. 2) of tip T can also be manufactured to the same thickness which results in a smooth transition between the balloon D and the tip T with a minimal increase in the profile of the catheter. In order to further decrease the profile of the catheter, and thus facilitate blood flow to the lesion when the distal end of the catheter is moved toward the stenosis, the proximal neck 56 of balloon D is secured to the inner surface 58 of outer body member B adjacent distal end 60 of outer body member B. A buffed and smoothened edge 62 is used adjacent outer surface 44 of balloon D adjacent distal end 60 of outer body member I. The use of the smoothed edge 62 which has a slight taper thereon, eliminates any sharp edges which could irritate or tear through the arterial wall on insertion or removal of the catheter C. As can readily be seen from examining Figs. 1 and 2 when balloon D is deflated, the maximum profile of the distal end 18 of catheter C is represented by the diameter of tip T (surface 46) as measured in a plane perpendicular to the longitudinal axis of catheter C. The flexibility of the catheter C may be adjusted in several ways. One way to affect the relative stiffness or the distal end 18 of catheter C, which extends from the distal end 60 of the outer body member B to the end of tip T, is to vary the length of proximal neck 56 of balloon D. The neck 56 can be varied from 1-60 mm, by example and not by way of limitation. Along the same lines, the overall length of tip T can be adjusted to affect the bendability of the assembly of the catheter C. Another way to affect the overall stiffness of the distal end 18 of catheter C is to prepare the formulation of inner body member I and tip T to varying hardnesses. Typically, by example and not by way of limitation, the tip T can be in the range of 50 to 90 A hardness as measured by the Shore method and can be made from a material such as nylon. The inner body member I, by example and not by way of limitation, can be made of a stiffer grade of nylon such as approximately 140 on the Rockwell scale. The relative hardnesses of the tip T and the inner body member I can be adjusted in conjunction with adjustments of the length of proximal neck as well as the overall length of tip T to achieve the desired stiffness of catheter C for a particular application. Typically, tip lengths can be in the range of one to thirty millimeters, by example and not by way of limitation although a range of 1-10 mm. is preferred. Similarly, proximal neck 56 can be provided in varying lengths in the range of one to six centimeters, by example and not by way of limitation. As an alternative way to modulate the relative stiffness of the distal end 18 of the catheter C, Fig. 5 illustrates the tip T in the embodiment illustrated in Fig. 3 with an embedded coil spring 80 mounted toward the most distal end 74 of tip T. As shown in Fig. 4, spring 80 circumscribes the lumen 14 extending through the tip T. The length and spring rate of spring 80 can be adjusted depending on the desired stiffness. However, the overall profile of the tip must be retained at a level as small as possible. It should be noted that when using spring 80 embedded in tip T an infusion lumen 70 as disclosed in Fig. 6 is generally not used. As seen in Figs. 1 and 2, annulus A has a substantially constant cross-section proximally and distally to tapered segment 20 on inner body member I. This is accomplished by a taper 64 on outer body member B adjacent to its distal end 60. Taper 64 is aligned with tapered segment 20 of inner body member I. A suitable contrast fluid (not shown) is inserted into annulus A from the proximal end of the catheter C (not shown) to fill up cavity 24 thereby inflating the balloon and exerting radial forces against the stenosis. The low profile of the catheter C of the present invention as shown in Figs. 1 and 2 is significant in permitting continual blood flow while the catheter C is inserted into an artery such as the coronary artery. The low profile of the catheter of the present invention presents an improvement over other known designs in that the low profile permits continued blood flow as the catheter C is inserted into the artery while at the same time, catheter C of the present invention permits sensitive pressure measurements during the angioplasty procedure. Since measurement of pressure is a dynamic type of measurement, it is significant not to increase the flow resistance in lumens 12 and 14. A substantially smooth wall in lumens 12 and 14 can reduce such resistance to flow. As shown Figs. 1 and 2, a guide must pass through aligned lumens 12 and 14. The necking down of lumen 12 to the cross-section depicted by arrow 22 acts to increase the flow resistance thereby tending to make pressure measurements more difficult. However, this section of lumen is of relatively short length and necessary in order to achieve the low profile nature of the distal end 18 of catheter C. Transitions 20 and 64 allow the cross-sectional area of lumen 12 to increase in size, measured in a proximal direction, as soon as is possible. As a result the overall flow resistance of lumens 12 and 14 is kept to a minimum which in turn increases the sensitivity of the requisite pressure measurements. At the same time, the cross-sectional area of annulus A remains constant up until proximal neck 56 of balloon D is mounted to the inner surface 58 of outer body member B. By maintaining the cross-sectional area of annulus A as large as possible, the resistance experienced by doctor or a technician in inflating balloon D is kept to a minimum. Fig. 3 represents an alternative mounting of the proximal end of the balloon to the distal end 60 of outer body member B. As shown in Fig. 3 the balloon inner surface 28 is mounted to the outer surface 66 of outer body member B adjacent its distal end 60. A vent lumen 68 is provided within the wall of outer body member B. As seen in Fig. 3, by providing vent lumen 68 in the wall of outer body member B, the cross-sectional areas of lumen 12 or annulus A remain uneffected. The presence of vent lumen 68 extending longitudinally into cavity 24 from proximal end of the catheter C (not shown) facilitates the purging of entrained gases within the balloon prior to insertion of the catheter C within the body. In order to use the catheter C, the entrained gases are purged from cavity 24 as well as annulus A by the injection of a contrast fluid. The contrast fluid (not shown) is injected with a syringe into annulus A. The contrast fluid flows into cavity 24 which is in flow communication with annulus A. By holding the distal end 18 of the catheter C in a vertical position with the tip T pointing towards the ground, and by further withdrawing the plunger of the syringe injecting the contrast fluid, the air or other entrained gases within cavity 24, due to the vacuum resulting from the withdrawal of the plunger (not shown) is drawn from cavity 24 through annulus A and out of the catheter C. The vent lumen 68 in the design of Fig. 3 further facilitates the purging of entrained gases. Experience has shown that with a proper amount of care, the entrained gases can also be effectively removed from cavity 24 without the use of vent lumen 68. However, the presence of lumen 68 streamlines the procedure. Although inner body member I and tip T have been shown with a unitary lumen 12 and 14, respectively, alternate constructions are within the purview of the invention. For example, inner body member I and tip T can have two aligned lumens. The first lumen accommodates a guide wire and/or a guiding catheter and is used to measure pressure through the catheter C in the zone distal to the stenosis. The adjacent lumen which is substantially parallel to the initial lumen can be used to infuse oxygenated blood and other fluids distal to the balloon. The infusion lumen 70 preferably exits radially from tip T proximal to the distal end of tip T as shown in Fig. 6. Lumen 70 may also exit at an acute angle to the longitudinal axis of tip T. As seen in Fig. 3, tip T can be further constructed to have a reducing taper 72 to further reduce the cross-sectional area tip adjacent its most distal end 74. In order to aid the performance of the angioplasty procedure, tip T can be made of a radiopaque material to allow close monitoring of its axial position in the arterial system of the body. The Catheter C of the present invention has a soft tip T which extends from the most distal end point 74 (Figure 3) to a point adjacent to the distal neck 32 of balloon D. The soft tip T is juxtaposed adjacent to the distal end 10 of inner body member I (Figure 3). The soft tip T reduces the tendency of an overly stiff catheter to pull out the guiding catheter from the coronary artery ostium and/or pull the guidewire from the stenosis when the angioplasty catheter C is advanced through a tortuous arterial passage. At the same time the distal end 10 of the inner body member I being relatively stiffer than the tip T provides the necessary rigidity for precise placement of the balloon D within the stenosis. Additionally, the relative stiffness of distal end 10 under Balloon D resists constriction of lumen 12 due to hydrostatic pressures exerted by an inflated balloon D. The resistance to lumen constriction is achieved in the catheter design as shown in Fig. 1, for example. One of the problems associated with catheters in prior use is the need to obtain accurate dynamic measurements of arterial pressure upstream and downstream of balloon D during inflation and after deflating of the balloon. The system previously employed is illustrated in Figure 6. As seen in Figure 6, there is a schematic representation of the angioplasty catheter C. A terminal fitting 200 includes a connection 202 and a transducer 204 which converts the upstream pressure, at a position indicated by arrow 206 to an electrical signal which shows the pressure on recorder 208. Similarly, another terminal fitting 210 allows fluid communication with the pressure in the artery 212 distal to balloon D. Arrow 214 represents a point at which the arterial pressure is measured downstream of balloon D through a fluid connection through terminal fitting 210. Transducer 216 converts the pressure measured at a point indicated by arrow 214 In the past, several problems were encountered in using the pressure measurement system illustrated in Figure 6. Frequently, to facilitate the use of the catheter C, the lead lines 218 and 220 were fairly lengthy. Lead lines 218 and 220 were frequently made from soft, compliant materials, which tended to affect dynamic pressure readings at the points indicated by arrows 214 and 206. Additionally, during the angioplasty procedure, blood or contrast media must be injected into connections 202 and/or 222 which requires temporary disconnection of the tubes. In the past, prior to insertion of the catheter, the long load lines 218 and 220 had to be flushed with a fluid to purge all air from such lines. Additionally, when blood or contrast media have to be injected through connections 202 or 222, such injection took place through fittings in lines 218 and 220. As the connections were temporarily removed during injection of blood or contrast media, entrapment of air into lines 218 and 220 was a potential problem. Thus, the doctor had to take time to insure that air was eliminated from lines 218 and 220 prior to connecting the lines 218, and 220 back to the catheter. The length of leads 218 and 220 coupled with the compliant wall of such lines also affected the sensitivity of dynamic pressure readings seen on the recorder 208. Figure 7 illustrates an improvement over the prior pressure measurement system shown in Figure 6. As seen in Figure 13, the guiding catheter 224 is equipped with a pressure transducer 226 mounted to its hub or adjoining "Y" connector and having a sensor exposed to the arterial pressure upstream of balloon D at a point illustrated by arrow 206. Transducer 226 can also be mounted to the body of catheter C without departing from the spirit of the invention. The angioplasty catheter C having the construction illustrated in Figur 1, by example, and not by way of limitation, has a transducer 228 mounted to the hub or "Y" connector of the PTCA catheter or alternatively, embedded in its wall with a sensing element exposed to the arterial pressure downstream of balloon D at a point indicated by arrow 214. Suitable wires, emerge through fittings 200 and 210, respectively. Wires 230 and 232 are then connected to recorder 208 to give a visual readout of the pressure between two points, upstream and downstream of the inflated balloon D. The inaccuracies in pressure measurement experienced by the system illustrated in Figure 6 and described above, are eliminated in favor of a more sensitive system, which more accurately tracks the pressure proximally and distally of balloon D during inflation. Additionally, with the system as illustrated in Figure 7, connections such as 222 or 202 can be closely mounted to terminal fittings 210 and 200 respectively so that drugs or blood can be infused with minimal risks of introduction of air into the catheter. Another aspect of the invention is perfusion of blood distally of an inflated balloon to reduce ischemic reactions downstream of the balloon. By perfusing blood, preferably from the renal vein of the patient during balloon inflation, ischemic manifestations during prolonged coronary dilations of the balloon D are adequately suppressed. Hemoperfusion allows a more adequate and more durable remolding (dilation) of coronary plaque during angioplasty. A suitable blood withdrawal apparatus in connected to the renal vein (not shown) and through a blood pump is directed into connection 222 as represented by arrow 234. Renal blood is preferred due to its high oxygen content. Using perfusion of renal blood, allows the balloon inflation time to be extended to five minutes or more. Without distal hemoperfusion, patients can experience chest pain and electrocardiographic signs of progressive significant ischemia at a period of over 60 seconds balloon inflation. In the past, only poor flow rates were achieveable through coronary dilation catheters. And as most PTCA procedures could be performed. without myocardial protection for 60 second balloon inflations efforts to provide distal profusion were abandoned. In a 1984 article in the Journal of the American College of Cardiology, Meier and Gruentzig, in an article entitled "Percutaneous Arterial Perfusion of Acutely Occluded Coronary Arteries in Dogs", described an experimental danine model in which a roller pump was used for as long as 150 minutes allowing flows of up to 100 ml/min. The incidence of hemolysis and thrombosis was considered unacceptable Other experiments involved selective injection of exogenous fluids for distal coronary perfusion during PTCA. Fluorocarbon emulsions were mildly successful in reducing ischemic manifestations during balloon inflation but were associated with a high incidence of ventricular fibrillation. Experiments have shown that with existing catheters available in the U.S. market, manufactured by USCI inflated up to ten atmospheres, pressures of 0,34 MPa to 0,52 MPa (50 to 75 psi) were sufficient to yield blood flow rates of 40 to 60 ml/min. The inflation of the balloon, at certain times, however causes collapsing of the through lumen of the catheter. Other commercially available catheters, such as those made by the ACS Company, however required pressures as high as 1,72 to 1,86 MPa (250 to 270 psi) to achieve the same flow rates. Infusion of 40 to 60 ml/min. of blood allows for adequate suppression of ischemic manifestations of left anterior descending coronary arterial occlusions. Relatively long term sub-selective coronary hemoperfusion can be used with patients with accute or impending myocardial infarction whether PTCA related or not. Such long term applications require catheters having as low as possible a resistance to blood flow along with automatic pumping equipment to provide reliable flows for prolonged periods. The resulting improvements in regional coronary blood flow would be immediate and dramatic. Chest pain would be reduced or eliminated, ST-T segment changes would be reduced or normalized. The patient's hemodynamic status and rhythm would also be stabilized. The use of long term hemoperfusion would offer patients the hope of undergoing angioplasty and/or surgery under semi-elective conditions. The use of oxygen rich renal blood allows for use of lower flow rates to prevent ischemia while being a low risk and non complicated method for withdrawal of blood as compared to use of arterial blood from a femoral artery. Thus lower pump pressures can be used with a properly designed catheter. Damage to the blood due to high operating pressures is reduced. Contamination or other complication which can arise by using a foreign blood as a source of the perfused blood is greatly reduced if not eliminated. In order to facilitate distal hemoperfusion with blood having hemocrit levels of about 30 - 50%, it is desirable to reduce the resistance to blood flow through lumen 12 (see Figure 1). To that end, it is desirable to maintain the following ratios: L 1 = The length given by arrow 224 in cm (inches) L 2 = The length given by arrow 248 in cm (inches) D 1 = The lumen inside diameter given by arrow 242 D 2 = The lumen inside diameter given by arrow 246 L 1 D 1 4 ≤ K L 2 D 2 4 K ranges from about 2-4 for blood having a 30-50% hemocrit level. It has also been found that a specific dimensional relationship between the diameters of lumen 12, in the positions of arrows 16 and 22, as well as the length of the distal end of the catheter (measured from tapered segments 20 and 64 to the distal tip 74) and the length of the catheter proximally to transitions 20 and 64, provides optimal conditions to facilitate distal perfusion at reduced resistance to flow. The variables just described are identified in Figure 10. The inside diameter D 1 of lumen 12 is indicated by arrow 242. The length L 1 is represented by arrow 244. The diameter D 2 of lumen 12 is represented by arrow 246. The length L 2 of the dlstal segment of lumen 12 represented by arrow 248. For human whole blood of Hemocrit level of 30-50% the dimensional relationships yielding the lowest pressure drop for catheters configured as shown in Fig. 10 is: ΔP (PSI) = 5.2 x 10 -10 L 1 D 1 4 + L 2 D 2 4 The figure 5.2x10-10 a constant for the blood as described above and includes a factor for justifying the units on both sides of the equation. Different values for this constant are used for other fluids. Q is the flow rate in cubic inches per min. Another improvement over angioplasty catheters previously in use in illustrated in Figure 8. PTCA catheters of known constructions or of the types Illustrated in Figure 1, can be employed with the multi-stage balloon D illustrated in Figure 14. The balloon may be formed to have two stages as illustrated in Figure 8 or a multitude of stages as desired. The advantage of using a multi-staged balloon is that the same catheter can be used to remold or dilate coronary plaque during angioplasty without the necessity of having to remove one catheter and inserting another having a larger balloon capable of dilating the plaque further than the prior catheter. Thus, in operation, as shown in Figure 14, the initial dilation of the plaque is done by placement the smaller stage 236 of the balloon D in the stenosis and dilating the plaque. The balloon D is then deflated and inserted further into the stenosis so that the distal stage 238 is inserted into the stenosis. The balloon is then reinflatad for further dilation of the coronary plaque. The ratios between the stages can be made to vary depending upon the anticipated application. The balloon can be provided with two stages or more, as desired, depending on the application. The dotted circle labeled 15 in Figure 8 is illustrated in the section shown in Figure 9. Figure 7, illustrates a coating of the entire catheter especially the balloon, with a combination silicone type 4159 from Dow Corning Company and heparin layer 240 as illustrated in Figure 9. The silicone adds to the lubricity of the catheter C and the heparin prevents the formation of clots. Heparin is interstitially placed within the silicone matrix and than made to adhere to the catheter C walls including the balloon D. Prior applications involved heparin coated catheters in combination with a polymer which did not provide lubricity. The combination of silicone and heparin yields both advantages simultaneously. The catheter is plasma treated in order to obtain a suitable bond of the silicone/heparin layer to the catheter material, which by example and not by way of limitation may be polyethylene.

Claims: An angioplasty catheter (C) having an elongated body, a balloon (D) and means for inflation of a balloon; said elongated body comprises an inner body member (I) and an outer body member (B) in a coaxial arrangement; wherein the inner and outer body member define an annulus (A) between them for inflating the balloon (D), and said balloon (D) has a plurality of stages of differing outside diameters when said balloon has been inflated; whereupon the same catheter (C) can be used to dilate a stenosis in progressively increasing dimensional increments. The catheter of claim 1, characterized in that said inner body member (I) comprises a tapered segment (20). The catheter of claim 1 or 2, characterized in that said outer body member (B) comprises a tapered segment (64). The catheter of any of claims 1 to 3, comprising: a first pressure-sensing element mounted to the catheter (C), said first element adapted to sense pressure in the vascular system or the patient's body cavity distally (214) of said balloon (D) and transmit a first electrical signal in relation thereto; a second pressure-sensing element mounted to the catheter (C), said second element adapted to sense pressure in the vascular system or the patient's body cavity proximally (206) of said balloon (D) and transmit a second electrical signal in relation thereto; signal conduction means (230, 232) mounted to the catheter (C) connected to said first and second pressure-sensing elements for conducting said first and second electrical signals from the proximal end of the catheter (C) located outside the patient's body. The catheter of any of claims 1 to 4, insertable over a guide, wherein: said elongated body has a proximal and distal segment, a tip (T), which defines at least one substantially smooth-bore lumen (14) extending therethrough, a lumen (12) in said body in flow communication with said lumen (14) in said tip (T) thereby allowing the catheter (C) to be advanced over a guide extending through said lumen (12, 14) in said body and in said tip (T); said balloon (D) is mounted in close proximity to the outer surface of said distal segment of said body defining a balloon cavity (24) therebetween, said balloon (D) has a proximal and distal neck, said balloon (D) is disposed substantially proximally to said tip (T), said distal neck of said balloon (D) is mounted adjacent to the juncture between said elongated tip (T) segment and said distal end of said distal segment of said body; and means within said body for selectively inflating and deflating said balloon (D) through said cavity (24). The catheter of claim 5, insertable over a guide, wherein said body being harder than said tip (T). The catheter of claim 5 or 6, wherein: the proximal end of said tip (T) has an adjacent internal mounting shoulder (34) circumscribing said lumen (14) extending therethrough; said shoulder (34) is mounted to the distal end (10) of said distal segment of said body; and the distal neck of said balloon (D) is connected directly onto the outer surface of said distal segment of said body adjacent to the proximal end of said tip (T) whereupon the outer surface of the distal neck of said balloon (D) is substantially longitudinally aligned with the outer surface of said tip (T). The catheter of any of claims 5 to 7, wherein: the proximal end of said tip (T) has an adjacent internal mounting shoulder (34) circumscribing said lumen (14) extending therethrough; said shoulder (34) is mounted to the distal end (10) of said distal segment of said body; and said tip (T) further comprising; an external mounting shoulder (48) adjacent its proximal end; and said distal neck of said balloon (D) is connected to said external shoulder (48) whereupon the outer surface of the distal neck of said balloon (D) is substantially aligned with the outer surface of said tip (T) adjacent the proximal end of said tip (T). The catheter of any of claims 5 to 8, wherein: said tip (T) is mounted to the distal extremity of said body thereby defining a joint therebetween; said tip (T) having an outer surface substantially in longitudinal alignment with the outer surface of said distal segment of said body; said distal neck of said balloon (D) is mounted over said aligned outer surfaces. The catheter of any of claims 1 to 9, wherein the balloon (D) has two stages of differing outside diameters (236, 238) when said balloon (D) is inflated. The catheter of any of claims 1 to 10, wherein said catheter (C) comprises a tip (T) of a radioopaque material. The catheter of any of claims 1 to 11, wherein the balloon (D) is coated with a combination of silicone and heparin. The catheter of claim 12, wherein the silicone is a silicone type 4159 from Dow Corning company.

Inventors: ANGELINI PAOLO, WIJAI BANDULA, ANGELINI, PAOLO, WIJAI, BANDULA
Applicants: SCIMED LIFE SYSTEMS INC, SCIMED LIFE SYSTEMS, INC.
Application year: 1988
Main classification: A61M29
IPC codes: A61M25, A61M29