US20050245866A1

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Publication number: US20050245866A1
Application number: US11/159,773
Authority: US
Inventors: Gholam-Reza Azizi
Original assignee: Medtronic Vascular Inc
Current assignee: Medtronic Vascular Inc
Priority date: 1996-05-20
Filing date: 2005-06-23
Publication date: 2005-11-03
Also published as: US20020065507A1; AU2869799A; US20060265000A1; US6544276B1; US6986778B2; WO1999042157A2

Abstract

The present invention provides a method for exchanging catheters while containing emboli within a blood vessel such as a saphenous vein graft, coronary artery, carotid artery, or other similar vessels. A guidewire is inserted through the vasculature of a patient until it reaches a desired treatment site. A therapy catheter is then inserted over the guidewire until the distal end of the therapy catheter reaches the treatment site. The guidewire has a distally mounted balloon which is inflated to occlude the blood vessel. Then, the therapy catheter provides means for treating the vessel at the treatment site. After treatment, the therapy catheter is removed from the guidewire and exchanged with an aspiration catheter which rides over the guidewire until the distal end of the aspiration catheter reaches the treatment site. The aspiration catheter applies negative pressure to remove any emboli formed by the treatment procedure.

Description

RELATED APPLICATIONS

This application is a continuation-in-part of application Ser. No. ______, entitled LOW PROFILE CATHETER VALVE AND INFLATION ADAPTOR, filed Nov. 20, 1997 (Attorney Docket No. PERCUS.006CP1), the entirety of which is hereby incorporated by reference.

BACKGROUND OF THE INVENTION

1. Field of the Invention

The present invention relates to medical catheters used in treating saphenous vein grafts, coronary arteries, and other blood vessels, and more particularly, to a method for exchanging catheters during emboli containment in such vessels.

2. Description of the Related Art

Guidewires are conventionally used to guide the insertion of various medical instruments, such as catheters, to a desired treatment location within a patient's vasculature. In a typical procedure, the clinician forms an access point for the guidewire by creating an opening in a peripheral blood vessel, such as the femoral artery. The highly flexible guidewire is then introduced through the opening into the peripheral blood vessel, and is then advanced by the clinician through the patient's blood vessels until the guidewire extends across the vessel segment to be treated. Various treatment catheters, such as a balloon dilatation catheter for a percutaneous transluminal coronary angioplasty, may then be inserted over the guidewire and similarly advanced through vasculature until they reach the treatment site.

In certain treatment procedures, it is desirable to successively introduce and then remove a number of different treatment catheters over a guidewire that has been placed in a particular location. In other words, one treatment catheter is “exchanged” for another over a single guidewire. Such an exchange typically involves withdrawing the treatment catheter over the guidewire until the treatment catheter is fully removed from the patient and the portion of the guidewire which extends from the patient. The guidewire is then available to act as a guide for a different treatment catheter.

As can be readily appreciated, the withdrawal of treatment catheters over a placed guidewire may result in the guidewire being displaced from its position. To overcome this difficulty, the prior art has developed “anchorable” guidewires, which generally feature some structure on their distal ends to releasably secure the guidewire at a particular location in the patient for the duration of the medical procedure. One such anchorable guidewire is disclosed in U.S. Pat. No. 5,167,239 to Cohen et al., which discloses a hollow guidewire with an inflation, lumen and an expandable balloon on its end. The Cohen device includes a removable inflation manifold, and a check valve to maintain the balloon in the inflated state when the manifold is removed. The check valve apparatus used by the Cohen device is relatively bulky, and is described as having an outer diameter in its preferred embodiment of 0.0355 inches. Consequently, any treatment catheter intended to be inserted over the Cohen device must have an interior guidewire lumen larger than the outer diameter of the Cohen valve, which for the preferred embodiment, requires an interior lumen with a diameter of more than 0.0355 inches. Cohen also does not address the problem of emboli containment.

As is readily appreciated by those of skill in the art, increasing the interior lumen size of a treatment catheter results in an increase in the outer diameter of the treatment catheter. However, many blood vessels where it is desirable to apply catheter treatment are quite narrow. For example, the left coronary arteries are blood vessels having diameters ranging from 2 to 4 mm, and are susceptible to plaque. Similarly, saphenous vein grafts (SVG) and the carotid arteries are also quite small and susceptible to plaque, and could not practically be treated by larger diameter devices.

Human blood vessels often become occluded or completely blocked by plaque, thrombi, other deposits, emboli or other substances, which reduce the blood carrying capacity of the vessel. Should the blockage occur at a critical place in the circulatory system, serious and permanent injury, or even death, can occur. To prevent this, some form of medical intervention is usually performed when significant occlusion is detected.

Coronary heart disease is an extremely common disorder in developed countries, and is the leading cause of death in the U.S. Damage to or malfunction of the heart is caused by narrowing or blockage of the coronary arteries (atherosclerosis) that supply blood to the heart. The coronary arteries are first narrowed and may eventually be completely blocked by plaque, and may further be complicated by the formation of thrombi (blood clots) on the roughened surfaces of the plaques. Myocardial infarction can result from atherosclerosis, especially from an occlusive or near occlusive thrombi overlying or adjacent to the atherosclerotic plaque, leading to death of portions of the heart muscle. Thrombi and emboli also often result from myocardial infarction, and these clots can block the coronary arteries, or can migrate further downstream, causing additional complications.

Various types of intervention techniques have been developed which facilitate the reduction or removal of the blockage in the blood vessel, allowing increased blood flow through the vessel. One technique for treating stenosis or occlusion of a blood vessel is balloon angioplasty. A balloon catheter is inserted into the narrowed or blocked area, and the balloon is inflated to expand the constricted area. In many cases, near normal blood flow is restored. It can be difficult, however, to treat plaque deposits and thrombi in the coronary arteries, because the coronary arteries are small, which makes accessing them with commonly used catheters difficult.

Other types of intervention include atherectomy, deployment of stents, introduction of specific medication by infusion, and bypass surgery. Each of these methods are not without the risk of embolism caused by the dislodgement of the blocking material which then moves downstream. In addition, the size of the blocked vessel may limit percutaneous access to the vessel.

In coronary bypass surgery, a more costly and invasive form of intervention, a section of a vein, usually the saphenous vein taken from the leg, is used to form a connection between the aorta and the coronary artery distal to the obstruction. Over time, however, the saphenous vein graft may itself become diseased, stenosed, or occluded, similar to the bypassed vessel. Atherosclerotic plaque in saphenous vein grafts tends to be more friable and less fibrocalcific than its counterpart in native coronary arteries.

Diffusely diseased old saphenous vein grafts with friable atherosclerotic lesions and thrombi have therefore been associated with iatrogenic distal embolic debris. Balloon dilatation of saphenous vein grafts is more likely to produce symptomatic embolization than dilatation of the coronary arteries, not only because of the difference in the plaque but also because vein grafts and their atheromatous plaques are generally larger than the coronary arteries to which they are anastomosed. Once the plaque and thrombi are dislodged from the vein, they can move downstream, completely blocking another portion of the coronary artery and causing myocardial infarction. In fact, coronary embolization as a complication of balloon angioplasty of saphenous vein grafts is higher than that in balloon angioplasty of native coronary arteries. Therefore, balloon angioplasty of vein grafts is performed with the realization that involvement by friable atherosclerosis is likely and that atheroembolization represents a significant risk.

Because of these complications and high recurrence rates, old diffusely diseased saphenous vein grafts have been considered contraindications for angioplasty and atherectomy, severely limiting the options for minimally invasive treatment. However, some diffusely diseased or occluded saphenous vein grafts may be associated with acute ischemic syndromes, necessitating some form of intervention.

Furthermore, attempts heretofore have been made to treat occlusions in the carotid arteries leading to the brain. However, such arteries have been very difficult to treat because of the possibility of dislodging plaque which can enter various arterial vessels of the brain and cause permanent brain damage. Attempts to treat such occlusions with balloon angioplasty have been very limited because of such dangers. In surgical treatments, such as endarterectomy, the carotid artery is slit and plaque is removed from the vessel in the slit area. Such surgical procedures have substantial risk associated with them which can lead to morbidity and mortality.

In other procedures, such as in angioplasty and in the treatment of peripheral arteries and veins, there is the possibility that the guide wires and catheters used in such procedures during deployment of the same may cause dislodgement of debris or emboli which can flow downstream and cause serious damage, such as stroke, if they occlude blood flow in smaller vessels. Moreover, when treating aneurysms, coils or other objects deployed to fill the aneurysm may break free and become lost downstream. Thus, in summary, embolization and migration of micro-emboli downstream to an end organ is a major concern of cardiologists during catheterizations.

Accordingly, what is needed is an exchange method for use during treatment of narrow blood vessels such as the carotid arteries, coronary arteries and saphenous vein grafts. Specifically, what is needed is a method which allows an exchange of catheters while a distal occluding device is deployed to perform treatment within the vessel and to contain emboli produced, created, or used during the treatment procedure. Furthermore, because a distal occluding device may block the flow of blood to vital organs, it is desirable that the exchange be performed quickly and easily in order to minimize the time that the blood vessel is occluded.

SUMMARY OF THE INVENTION

The present invention satisfies the above needs by providing a method for exchanging catheters during an emboli containment procedure. As described herein, the term “emboli” may refer to any debris, particles, or other objects found, created or placed in a blood vessel. “Emboli containment” may refer to emboli removal, neutralization, disintegration, minimization, or simply to preventing emboli from moving downstream. In essence, “containment” refers to any procedure which reduces the deleterious effects that emboli may have on the patient. The preferred exchange method is particularly useful in angioplasty and similar procedures in smaller blood vessels such as the coronary or carotid arteries or in saphenous vein grafts. The exchange method described herein can be accomplished rapidly to minimize the time that a treated blood vessel is occluded for treatment.

For example, in most angioplasty procedures, a guidewire is first introduced into the vasculature of a patient until the distal end of the guidewire is near the occlusion or stenosis. The guidewire preferably bears a distal occlusion device, such as a balloon, filter, coil, or combination of these elements. The occlusive device is preferably activated prior to performing therapy to remove or reduce an occlusion or stenosis, to provide a working area and to prevent particles and debris produced during therapy from migrating downstream. The occlusive device may completely or partially occlude the vessel.

In order to perform an exchange over the guidewire catheter, the catheter must be made such that the occlusive device remains activated in order to minimize particles from going downstream. Furthermore, the proximal end of the guidewire must have a low profile to accommodate other catheters which are to be advanced over the guidewire. In one preferred method, a therapy catheter is advanced over a proximal end of the guidewire to the site of the plaque or lesion. After deploying the occlusive device on the end of the guidewire, therapy is performed on the lesion by the therapy device. One preferred therapy device is a dilatation catheter which compresses the lesion against the walls of the vasculature. In addition to dilatation balloon catheters, other forms of therapy may be used to dislodge, disintegrate, or neutralize the plaque. One method is to provide an ultrasonic catheter which targets the plaque and destroys it using shock waves. Another method is to use a vibration delivery catheter, which causes the plaque to break up due to a vibrating wire. Another method uses a drug delivery catheter provided over the guidewire, which provides fluids to dissolve the plaque. Other types of therapy include radiation therapy.

After treatment of the plaque by an appropriate therapy method, emboli often remain in the working area. The therapy catheter can then be removed and exchanged with an emboli removal catheter, such as an aspiration catheter for aspirating the emboli from the working area. The aspiration catheter can then be exchanged with another therapy catheter, such as a catheter bearing a stent which is deployed onto the lesion for maintaining the opening of the blood vessel.

The present invention in a preferred embodiment allows for the rapid and easy exchange of catheters by deploying the occlusive device in stages. For instance, when a guidewire with a distal occlusion balloon is used, the balloon is inflated only when there is danger of emboli moving downstream. Thus, if treatment of the stenosis consists of a dilatation procedure and deployment of a stent, the occlusion balloon will be inflated for a first inflation period during which the dilatation balloon works on the plaque, the dilatation catheter is exchanged with an aspiration catheter, and the aspiration catheter removes emboli from the vessel. After aspiration, the occlusion balloon can safely be deflated to allow blood flow for a period to organs downstream. An exchange can then be performed with another therapy catheter, such as a stent deploying catheter, and the occlusion balloon is reinflated for a second inflation period to deploy a stent to the location of the stenosis. By employing an exchange method with vessel occlusion occurring in stages, the time that blood flow is occluded in the vessel decreases, thereby minimizing the risks to the patient and presenting significant advantages over known technology. The speed of exchange is also improved by using an adaptor which allows for easy and quick handling of the guidewire for inflation and deflation.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1A is a schematic view of a patient undergoing treatment by a preferred aspect of the exchange method of the present invention.

FIG. 1B is a perspective view of a human heart with a saphenous vein graft.

FIG. 2 is an enlarged perspective view of the proximal end of the guidewire shown inFIG. 1A, particularly showing an exchange method between a therapy catheter and an aspiration catheter.

FIGS. 3A is a perspective view of an over-the-wire therapy catheter having a dilatation balloon on its distal end and guidewire inserted into a saphenous vein graft in accordance with a preferred aspect of the present invention, with the vein graft shown partially cut away.

FIG. 3B is a perspective view of a guidewire inserted into a saphenous vein graft after the therapy catheter ofFIG. 3A has been removed, with the vein graft shown partially cut away.

FIG. 3C is a perspective view of an over-the-wire aspiration catheter and a guidewire inserted into a saphenous vein graft after an exchange with the therapy catheter ofFIG. 3A has been performed, with the vein graft shown partially cut away.

FIG. 3D is a perspective view of an over-the-wire stenting balloon and a guidewire inserted into a saphenous vein graft after an exchange with the aspiration catheter ofFIG. 3C has been performed, with the vein graft shown partially cut away.

FIG. 4 is a side view of a guidewire inserted into a saphenous vein graft, the guidewire having a radiopaque marker for targeting by an external shock wave generator, with the vein graft shown partially cut away.

FIG. 5 is a side view of a vibration delivery catheter and a guidewire inserted into a saphenous vein graft, with the vein graft shown partially cut away.

FIG. 6 is a side view of a drug delivery catheter and a guidewire inserted into a saphenous vein graft, with the vein graft shown partially cut away.

FIG. 7 is a side view of an aspiration catheter and a guidewire inserted into an artery being treated for an aneurysm, with the artery shown partially cut away.

FIG. 8 is a chart showing the inflation times of a distal occlusion balloon for 24 patients being treated in a preferred aspect of the exchange method of the present invention.

FIG. 9 is a side view of a catheter incorporating the low profile valve in a preferred aspect of the present invention.

FIG. 10 is an enlarged view of the proximal portion of the catheter ofFIG. 10 showing an exterior view of the catheter segment featuring the low profile valve in a preferred aspect of the present invention.

FIG. 11A is a longitudinal cross-sectional view of the catheter segment ofFIG. 10 showing the low profile valve in the open position.

FIG. 11B is a longitudinal cross-sectional view of the catheter segment ofFIG. 10 showing the low profile valve in the closed position.

FIG. 12 is a longitudinal cross-sectional view of an alternative embodiment, showing the low profile valve in the closed position.

FIG. 13 is a longitudinal cross-sectional view of the embodiment ofFIG. 12 showing the low profile valve in the open position.

FIG. 14 is a longitudinal cross-sectional view of an alternative embodiment of the low profile valve, depicting the valve in the open position

FIG. 15 is a longitudinal cross-sectional view of the embodiment ofFIG. 14 depicting the valve in the closed position.

FIG. 16 is a perspective view of an inflation adaptor used to manipulate the low profile valve in a preferred aspect of the present invention.

FIG. 17A is a perspective view of the interior of the inflation adaptor ofFIG. 16.

FIG. 17B is a perspective view of a catheter with a sealing member and alignment indicia being positioned in the inflation adaptor ofFIG. 17A.

FIG. 17C is a perspective, view of an inflation adaptor attached to a syringe system.

FIG. 17D is a side view of an aspiration catheter attached to a syringe system.

FIG. 18 is an end view of an alternative embodiment of the inflation adaptor.

FIG. 19 is a cross-sectional view of the inflation adaptor ofFIG. 18 along lines19-19.

FIGS. 20 and 21 are exploded views of alternative embodiments of the low profile valve in a preferred aspect of the present invention.

FIG. 22 is an alternative embodiment of the valve in a preferred aspect of the present invention featuring a built in spring bias.

FIGS. 23A and 23B are longitudinal cross-sectional views of the catheter proximal end ofFIG. 22 showing the valve in the closed and open position, respectively.

FIG. 24 is a perspective view of an alternative embodiment of an inflation adaptor used to manipulate the low profile valve in a preferred aspect of the present invention.

FIG. 25 is a perspective view of the interior of the inflation adaptor ofFIG. 24.

FIGS. 26A and 26B are top views of the inflation adaptor ofFIGS. 24 and 25, illustrating the latch locking mechanism.

FIGS. 27A-27C are schematic cross-sectional views of the adaptor ofFIG. 24 which illustrate the cam locking door mechanism which provides mechanical advantage to the adaptor locking latch.

FIGS. 28A-28C are close-up views of an embodiment of the adaptor having a sliding top panel biased by a spring mechanism.

FIGS. 29 and 30 are cross-sectional views of a proximal section of a catheter having an alternative embodiment of the valve in a preferred aspect of the present invention.

FIG. 31 is a side-elevational view in section of one embodiment of a catheter apparatus incorporating a preferred aspect of the present invention for treating occluded vessels.

FIG. 32 is a side-elevational view in section similar toFIG. 31 but showing the apparatus inFIG. 31 with the expansion member (in this case, a self-expandable seal) deployed.

FIG. 33 is a side-elevational view in section of another embodiment of a catheter apparatus incorporating a preferred aspect of the present invention for treating occluded vessels.

FIG. 34 is a view similar toFIG. 33 but showing the expansion member (in this case, a self-expandable seal) deployed.

FIG. 35 is a side-elevational view in section of another embodiment of a catheter apparatus incorporating a preferred aspect of the present invention for treating occluded vessels.

FIG. 36 is a view similar toFIG. 35 but showing the expansion member deployed and the sleeve completely removed.

FIG. 37 is a schematic, longitudinal cross sectional view of an embodiment in which a membrane only partially surrounds a braid used as the expansion member.

FIGS. 38A and 38B show end views of unperforated and perforated membranes, respectively.

FIG. 39 is a schematic, longitudinal cross sectional view of an embodiment in which a braid without a membrane is used.

FIG. 40 is a schematic, longitudinal cross sectional view of an embodiment in which a filter-like mesh is used as the expansion member.

FIG. 41 is a schematic, longitudinal cross sectional view of an embodiment in which a slotted tube is used as the expansion member.

FIG. 42 is a perspective view of the slotted tube used in the embodiment ofFIG. 41.

FIG. 43 is a schematic, longitudinal cross sectional view of an embodiment in which a coil is used as the expansion member, and the proximal end of a membrane surrounding the coil adjoins the coil.

FIG. 44 is a schematic, longitudinal cross sectional view of an embodiment in which a coil is used as the expansion member, and the proximal end of a membrane surrounding the coil adjoins a sheath that surrounds both first and second elongate members.

FIG. 44A is an embodiment similar to that shown inFIG. 44 in which resistive heating is used to expand the expansion member, with current being conducted through wires being attached to either side of the expansion member. The expansion member as shown is partially deployed.

FIG. 44B is an embodiment similar to that shown inFIG. 44A in which resistive heating is used to expand the expansion member, with current being conducted through a wire being attached to the distal end of the expansion member and through a coating on the first elongate member. The expansion member as shown is partially deployed.

FIG. 45 is a schematic, side cross sectional view of an embodiment in which a plurality of ribbons are used as the expansion member.

FIG. 45A is an embodiment similar to that shown inFIG. 45 in which a warm solution passes between the first and second elongate members to transfer heat to the expansion member, causing it to expand. The expansion member as shown is partially deployed.

FIG. 45B is an embodiment similar to that shown inFIG. 45A in which a warm solution passes through the first elongate member to transfer heat to the expansion member, causing it to expand. The expansion member as shown is partially deployed.

FIG. 45C is an embodiment similar to that shown inFIGS. 45A and 45B, in which a warm solution passes through one or more lumens in the first elongate member to transfer heat to the expansion member, causing it to expand. The expansion member as shown is partially deployed.

FIG. 46 is a schematic, side cross sectional view of an embodiment in which a plurality of ribs are used as the expansion member.

FIG. 47 is an isometric view of an embodiment of the invention in which a pull wire is used to deploy a plurality of non-self-expanding ribbons surrounded by a membrane.

FIG. 48 is a side partial sectional view of the embodiment ofFIG. 43 in which the ribbons are in their relaxed, undeployed position.

FIG. 49 is a side elevational view of the embodiment ofFIG. 47 in which the ribbons are deployed, and the membrane makes a seal with the vessel.

FIGS. 50A and 50B show longitudinal and end perspective views, respectively, of a locking mechanism used with a wire that deploys an expansion member.

FIG. 50C is a perspective view of the locking mechanism ofFIGS. 50A and 50B, further showing an adaptor for utilizing the locking mechanism.

FIG. 51A is a perspective view of an alternative locking mechanism used with a wire that deploys an expansion member.

FIG. 51B is a perspective view of the alternative locking mechanism ofFIG. 51A, further showing an adaptor for utilizing the locking mechanism.

FIGS. 52A, 52B,52C, and52D show, respectively, a braid, a filter-like mesh, a slotted tube, and a plurality of coils, which can be used as alternative expansion members in place of the ribbons in the embodiment ofFIG. 47.

DESCRIPTION OF THE PREFERRED EMBODIMENTS

I. Exchange Method During Emboli Containment

The method discussed herein allows for the rapid exchange of catheters during angioplasty and similar procedures. In particular, the preferred method of the present invention is adapted for use in the treatment and removal of an occlusion in a blood vessel in which the occlusion has a length and a width or thickness which at least partially occludes the vessel's lumen. Thus, the catheters of a preferred aspect of the present invention are effective in treating both partial and complete occlusions of the blood vessels. As used herein, “occlusion” includes both partial and complete occlusions, stenoses, emboli, thrombi, plaque and any other substance which at least partially occludes the vessel's lumen.

The method and apparatus of the present invention preferably can be used in any vessel of the body where the pressure is at least 0.2 psi at any stage of the heart pumping cycle, and more preferably, is about 1.2 psi, with a flow rate of at least 10 cc per minute. The method and apparatus are particularly suited for use in removal of occlusions from saphenous vein grafts, coronary and carotid arteries, and in other non-branching vessels having similar pressures and flow where a suitable working area can be created. Although the present invention will be described in connection with a saphenous vein graft, it should be understood that this application is merely exemplary, and the method can be used in other blood vessels as well. For example, it will be appreciated that the described method can also be applied to coronary arteries, carotid arteries, or any other arteries or veins where treatment and containment of emboli is desired.

A. The Preferred Treatment Method

In one preferred aspect of the present invention, a catheter orguidewire10 is inserted into thehuman body1 through agroin insertion site3, as shown inFIG. 1A. Theguidewire10 is passed through thefemoral artery5 and into the blood vessel network until it reaches the intended treatment site, which, as shown inFIG. 1B, is asaphenous vein graft2. Thegraft2 is used to bypass one of the occludedcoronary arteries4, and connects theaorta6 to the coronary artery at a location distal theocclusion8. Fluoroscopy is typically used to guide the guidewire and other devices to the desired location within the patient. The devices are frequently marked with radiopaque markings to facilitate visualization of the insertion and positioning of the devices within the patient's vasculature.

Thecatheter10 used for the preferred method is shown inFIGS. 9-11B. As described in further detail below, thecatheter10 comprises atubular body18 having a central lumen40 extending between aproximal end12 and adistal end14. Aninflation port22 is provided near theproximal end12 of the tubular body, which allows inflation fluid to pass through central lumen40 to a distally mounted occlusive device, such as aballoon20. A sealingmember30 is inserted to the lumen40 at opening23 of the tubular body. This sealing member extends into the lumen40 and plugs theinflation port22 to maintain balloon inflation, as described in more detail with respect toFIGS. 11A and 11B below.

FIG. 2 shows an enlarged view of the proximal end of theguidewire10 with sealingmember30 inserted therein. Both theguidewire10 and the sealingmember30 have substantially the same diameter, thereby allowing a catheter or guidewire having at least one inner lumen to pass over the two. This inner lumen can be made small to have substantially the same diameter as the outer diameter of the guidewire and sealing member. In the preferred embodiment, the outer diameter of thetubular body18 and the sealingmember30 is about 0.014 inches. Therefore, catheters having a lumen with a diameter as small as 0.014 inches may be exchanged over theguidewire10.

FIG. 2 also illustrates an exemplary exchange method. Where guidewire10 carries a first treatment catheter such as atherapy catheter50 having adilatation balloon52, thistherapy catheter50 can be slid off the proximal end of theguidewire10 and sealingmember30. Then, a second treatment catheter such as anaspiration catheter60 may be slid over the proximal ends of the sealingmember30 and theguidewire10 toward the treatment location. Further details regarding this exchange are described below.

1. Insertion of the Guidewire

FIGS. 3A-3D show more explicitly a preferred method of containing and aspirating embolic material while performing a balloon angioplasty and stenting therapy.FIG. 3A shows a lesion orplaque42 on the walls of asaphenous vein graft2. A catheter orguidewire10 is advanced into the blood vessel to a point distal of thelesion42. The method of a preferred aspect of the present invention can effectively be carried out using a number of guidewires or catheters that perform the function of occluding the vessel and allowing for the slidable insertion of various other catheters and devices. The term “catheter” as used herein is therefore intended to include both guidewires and catheters with these desired characteristics. As described in further detail below, the catheter has an occlusive device, such as an inflatable balloon, filter or other mechanical occlusive device, attached at its distal end. The occlusive device should be capable of preventing the migration of particles and debris from the working area, either through total or partial occlusion of the vessel. Note that the occlusion of the vessel need not be complete. Substantial occlusion of the vessel can be sufficient for purposes of the present invention.

Theguidewire10 should be sized so as to be slidable with respect to the therapy, aspiration or other catheters to be inserted over the guidewire. When the guidewire is properly positioned inside the vessel, the occlusive device at the distal end of the guidewire is actuated to occlude the vessel distal to the existing lesion to create a working area. With the occlusive device effectively blocking the flow of emboli downstream, various catheters may be exchanged over theguidewire10 to treat the vessel without the risk of emboli flowing downstream and cutting off blood flow to vital organs.

In non-bifurcated areas of the blood vessels, it has been discovered that fluid from the proximal portion of the same vessel acts as an infusion source. One therefore need only occlude the distal portion of the vessel to create a working area surrounding the occlusion and allow blood to flow from the proximal portion of the vessel into the working area. It should be noted that, as used herein, “proximal” refers to the portion of the apparatus closest to the end which remains outside the patient's body, and “distal” refers to the portion closest to the end inserted into the patient's body. Thus, the embodiment described above only provides an occlusive device distal to the working area.

However, an embodiment is also contemplated wherein the working area is defined by occlusive devices located both proximal and distal to thelesion42. In this embodiment, a guide catheter having a single lumen is first introduced into the patient's vasculature through an incision made in the femoral artery or vein in the groin and used to guide the insertion of other catheters and devices to the desired site. This guide catheter carries an occlusion balloon or other occlusive device to occlude the vessel proximal to thelesion42. Following insertion of the guide catheter, a second catheter is inserted through the guide catheter and past the site of the occlusion. This second catheter serves as the exchange catheter or guidewire over which various catheters may be advanced and removed.

2. Therapy Catheter/Aspiration Catheter Exchange

As shown inFIG. 3A, once theguidewire10 is in place, a therapy catheter may then be delivered to the site of the occlusion. The therapy catheter can employ any number of means for treatment, including a balloon catheter used to perform angioplasty, a catheter which delivers a stent, a catheter for delivering enzymes, chemicals, or drugs to dissolve or treat the occlusion, an atherectomy device, or a laser or ultrasound device used to ablate the occlusion.

Thetherapy catheter50 of the preferred embodiment includes adilatation balloon52 located on the distal end of an elongatetubular body54. Thetubular body54 has alumen56 extending from a proximal end to the distal end of the tubular body which is sized to override theguidewire10 until thedilatation balloon52 reaches the point of thelesion42. Onceballoon52 is in place, theocclusion balloon20 onguidewire10 is inflated to at least partially block blood flow. Then, thedilatation balloon52 is inflated to compress theplaque42 against the walls of the blood vessel. This inflation has the effect of dislodging some plaque and creating emboli48 (shown, inFIG. 3B) in the working area.

In the preferred method, after treatment by thetherapy catheter50 is completed, the therapy catheter is completely removed from the body by sliding the therapy catheter over theguidewire10 in a proximal direction away from the lesion and out of the body, leaving only theguidewire10 as shown inFIG. 3B. A rapid exchange is then performed and, as illustrated inFIG. 3C, anaspiration catheter60 is deployed over theguidewire10. The term “aspiration catheter” includes any device which creates an area of fluid turbulence and uses negative pressure and reverse flow to aspirate fluid and debris, and includes those devices which create a venturi effect within the vessel.Aspiration catheter60 as shown inFIG. 3C is an elongate tubular body having a lumen extending from a proximal end to a distal end. It should be noted that any particles which break free during therapy and aspiration procedures will be kept at the site of the procedure within the working area by the occlusive device occluding the distal portion of the vessel in combination with the blood pressure coming from the proximal portion of the vessel. The debris is prevented from migrating elsewhere, and remains localized for removal by aspiration. Further details regarding aspiration catheters are described in assignee's pending application entitled ASPIRATION SYSTEM AND METHOD, application Ser. No. ______, filed Feb. 19, 1998 (Attorney Docket No. PERCUS.022CP1), the entirety of which is hereby incorporated by reference. Once aspiration is completed, theballoon20 may be deflated to resume blood flow through the vessel.

Preferably, the procedure described above is perform twice using a predilatation catheter and a dilatation catheter. The predilatation catheter is a first therapy catheter which is advanced over the proximal end of theguidewire10 to the point of thelesion42. The balloon on the distal end of the predilatation catheter has a first inflation diameter designed to perform a first treatment to thelesion42. The predilatation catheter is then exchanged with an aspiration catheter to aspirate emboli formed by the first treatment, while the occlusion balloon remains inflated. After aspiration, theocclusion balloon20 is deflated to allow blood to flow to organs downstream, and then reinflated after exchange of the aspiration catheter for the dilatation catheter. This second therapy catheter has a dilatation balloon with a larger inflation diameter than the first dilatation balloon so as to further compress theplaque42 against the vessel walls. Once this treatment is completed, the second therapy catheter is exchanged with the aspiration catheter for removing emboli from the blood system.

Further exchanges of therapy catheters having successively larger dilatation balloons with aspiration catheters are also contemplated by the present invention, with each exchange occurring while the distal occlusion balloon is inflated. Moreover, it is not always necessary to follow treatment with a therapy catheter with an exchange for an aspiration catheter. Therapy catheters can be exchanged with other therapy catheters to perform further treatment in the blood vessel before an exchange with an aspiration catheter is made.

3. Stent Catheter Exchange

In the preferred method of the present invention, following treatment of the lesion and aspiration by one or more sequences as described above, theocclusion balloon20 is deflated to resume blood flow to the vessel. Another catheter exchange is performed whereby the aspiration catheter is removed from theguidewire10 and exchanged with a deployment catheter carrying a stent. As shown inFIG. 3D, the deployment device may be acatheter70 carrying aballoon72 holding anangioplasty stent74. Once thecatheter70 reaches the point of lesion, theocclusion balloon20 is reinflated to prevent any particles dislodged by the stenting process from migrating downstream. Theballoon70 is then inflated to expand the stent to its working diameter, and is sized to implant the stent into the vascular wall. Plastic deformation of the stent prevents it from collapsing once the balloon has been deflated and removed from the patient. Further details regarding stents are contained in assignee's pending application entitled STENT POSITIONING APPARATUS AND METHOD, application Ser. No. 08/744,632, filed Nov. 6, 1996, the entirety of which is hereby incorporated by reference. After the stent is in place, an exchange may be performed between thedeployment catheter70 and theaspiration catheter60 to remove any debris formed by the stenting process. After aspiration, theocclusion balloon20 is deflated and the aspiration catheter is removed.

B. Alternative Exchange Methods

The method described above is merely exemplary, and it should be recognized that the catheter exchange method may utilize a variety of exchanges of different types of catheters while emboli are being contained. The term “therapy catheter” is meant to include any of a number of known devices used to treat an occluded vessel. For example, a catheter carrying an inflatable balloon for use in balloon angioplasty can be delivered to dilate the occlusion. Thermal balloon angioplasty includes the use of heat to “mold” the vessel to the size and shape of the angioplasty balloon. Similarly, an intravascular stent can be delivered via a balloon catheter and deployed at the site of the occlusion to keep the vessel open. Cutting, shaving, scraping or pulverizing devices can be delivered to excise the occlusion in a procedure known as atherectomy. A laser or ultrasound device can also be delivered and used to ablate plaque in the vessel. Various thrombolytic or other types of drugs can be delivered locally in high concentrations to the site of the occlusion. It is also possible to deliver various chemical substances or enzymes via a catheter to the site of the stenosis to dissolve the obstruction. The term “therapy catheter” encompasses these and similar devices.

FIG. 4 shows an alternative embodiment employing a distal occlusion catheter for use in directing shockwaves to disintegrate theplaque42. Thecatheter10 comprises aradiopaque marker44 located proximal to thedistal balloon20. Themarker44 is used to locate theplaque42 for targeting by externalshock wave generator46. After inflation of the balloon, theshock wave generator46 is focused onto theplaque42 by use of the radiopaque marker to disintegrate the plaque.

After treatment of the plaque by the shock wave generator, anaspiration catheter60 as described inFIG. 3C may be slid over theguidewire10 for aspirating the emboli created by the shock wave treatment. Alternatively, the shock wave treatment may be performed with theaspiration catheter60 already advanced over theguidewire10. In such an embodiment, a radiopaque marker may either be placed on the guidewire or aspiration catheter itself for targeting the location of the plaque. Furthermore, the method described above may be implemented using ultrasounds for focusing of the shock wave generator to the plaque. For instance, a target balloon on a catheter may be advanced over the guidewire to the location of the lesion and inflated with air. Air provides a medium with a significantly different acoustical impedance than body tissue. This results in good ultrasound visualization for targeting the lesion. This catheter is then exchanged with an aspiration catheter for removing emboli from the vessel. Further exchanges with a stent deployment catheter or other types of therapy catheters may be performed as described above.

FIG. 5 shows another alternative therapy method for treating theplaque42. Avibration delivery catheter80 is advanced over theguidewire10 to a position adjacent thelesion42. The vibration delivery catheter is preferably a monorail catheter having two

lumens

82 and84,lumen82 serving as a passageway through which theguidewire10 passes, andlumen84 serving as a passageway for a waveguide or coupling member in the form of awire86. Theguidewire lumen82 as shown inFIG. 5 is located only on the distal end of the vibration delivery catheter. However, thelumen82 can be made to extend the entire length of thecatheter80 if desired. One end ofwire86 contacts thelesion42, while the other end extends out of the free end ofcatheter80 outside the body of the patient and is attached to atransducer88. With theocclusion balloon20 inflated, by activating the transducer thewave guide86 is caused to act on thelesion42 with transverse and longitudinal motion of the end of the wave guide to machine away or disintegrate thelesion42. Exchanges may be performed following this treatment with the aspiration, therapy or other catheters as described above.

FIG. 6 shows an alternative therapy method wherein adrug delivery catheter90 is advanced overguidewire10 to dissolve theplaque42. Thecatheter90 is preferably a monorail catheter having two

lumens

92 and94, thelumen92 riding over theguidewire10. Thedrug delivery lumen94 extends from aproximal end96ato adistal end96b, with thedistal end96bpositioned adjacent the lesion to be treated. At the proximal end, aninfusion port97 is provided for deliveringdrugs99 to the location of the lesion. Preferable materials for use in dissolving thelesion42 are TPA (tissue plasminogen activator) available from Genentech, Inc., or pro-urokinase, available from Abbott Laboratories. Also at the proximal end, anaspiration port98 is provided for removing emboli created by the procedure. Alternatively, the drug delivery catheter may be exchanged with a separate aspiration catheter for performing emboli containment. After dissolution of thelesion42, exchanges may be made with stent carrying catheters or other catheters as described above.

The exchange method as described in a preferred aspect of the present invention is not applicable solely to procedures dislodging emboli. Rather, the present exchange method also applies to any situation wherein a distally occluding device prevents the migration of undesired particles downstream. For instance, as shown inFIG. 7, an aneurysm of an artery is shown, wherein abulge162 is found inartery160.Guidewire10 carryingdistal occlusion balloon20 is advanced through the vessel such that theballoon20 is located distal to thebulge162. Theballoon20 is inflated so that various treatment and/or aspiration catheters may be exchanged to perform treatment on the aneurysm. In treating aneurysms, one preferred method is to fill thebulge162 withembolization elements164. Thedistal occlusion balloon20 is necessary because some of these particles may break free and migrate downstream. An exchange is also desired for treating aneurysms because deployment ofparticles164 must be done sequentially, with subsequent catheters delivering more and more embolization elements to fill162. Thus, a catheter exchange over theguidewire10 is desirable for rapidly filling thebulge162 while thedistal occlusion balloon20 is inflated. An exchange is further desired to advance an aspiration catheter into the vessel to remove any particles that may have come loose while treating the aneurysm.

C. Exchange Methods Over Alternative Occlusive Devices

Although the embodiments described above refer to a distally occluding balloon to prevent emboli from migrating downstream, other methods for occluding the blood vessel may be used while performing the exchange method described in a preferred aspect of the present invention. With respect to all of these methods, the, proximal ends of the expansion members are sized to allow an exchange of catheters over the catheter or guidewire bearing the expansion member. These methods as briefly discussed herein are described in further detail below in the section entitled “Expansion Members.”

InFIGS. 35-36, a catheter apparatus is shown having a self-expanding sealing mechanism. As shown inFIG. 35, thecatheter apparatus1781 comprises a guidingcatheter1782 with a self-expandingsealing mechanism1791 mounted ondistal end1784. Thesealing mechanism1791 is enclosed by anelongate sleeve1796 having acollar1801 mounted on theproximal extremity1797 ofsleeve1796. Thecollar1801 serves as a mechanism for retracting the sleeve to uncover self-expandingsealing mechanism1791 after the catheter has been deployed to permit the self-expandingsealing mechanism1791 to expand and form a seal with the vessel adjacent the stenosis to be treated.Sleeve1796 may be completely removed, as shown inFIG. 36, to permit catheters with inner lumen diameters substantially the same as the outer diameter of the guiding catheter to be exchanged over the catheter. The various types of occlusive devices provided at the distal end of these catheter apparatuses and their manner of operation are more particularly described below with respect toFIGS. 31-46.

The preferred exchange method of the present invention may also be performed over catheters or guidewires employing non-self-expanding or mechanically deployed sealing mechanisms. As shown inFIGS. 47-51B, described in further detail below, a pull wire device may be utilized for deploying an occlusive mechanism to a blood vessel while still maintaining a low profile at the proximal end of the device to allow for an exchange. As shown inFIG. 49, one pull wire device comprises anelongate member1166 over which therapy, aspiration and other catheters may be advanced and removed. At the proximal end of the device, arotatable handle1180 is attached to a lockingmember1184. Thewire1140 is pulled byhandle1180 from its configuration shown inFIG. 50A until the lockingmember1184 clears the proximal end ofelongate member1166, at whichpoint member1184 is rotated to the configuration shown inFIG. 50B to hold thewire1140 taut. Thehandle1180 and lockingmember1184 are dimensioned to be substantially the same size as theelongate member1166, which preferably has an outer diameter of 0.014 inches, such that other catheters may be advanced and removed over the elongate body166 without interference from thehandle1180 or lockingmember1166.

FIG. 51A shows an alternative pull wire mechanism wherein aspacer1194 is placed between ahandle1190 andelongate body1166 to pullwire1140 and deploy the sealing mechanism. Because thehandle1190 and thespacer1194 have the same diameter as theelongate body1166, the exchange method as described above may be performed over theelongate body1166 with catheters having relatively small inner diameters.

D. Speed of Exchange

The method described by a preferred aspect of the present invention is particularly advantageous in that it allows for a rapid exchange of catheters to reduce the time that a blood vessel is occluded by a balloon or other occlusive device.FIG. 8 shows experimental results for 24 patients undergoing percutaneous transluminal coronary angioplasty (PTCA) and subsequent stenting treatments in saphenous vein grafts. More particularly,FIG. 8 shows the inflation durations ofocclusion balloon20 during the treatment procedure, i.e., the time that theballoon20 is inflated to occlude the vessel. The preferred method minimizes the times that the occlusion balloon is inflated by conducting the treatment in stages. For instance, a first stage, corresponding to a first inflation time, may comprise a sequence of therapy and aspiration treatments. After occlusion balloon inflation, a therapy catheter carrying a dilatation balloon may be used to compress the lesion. Exchanges with subsequent therapy catheters may then be performed, as long as end organs positioned downstream can tolerate the loss of blood due to blockage by the occlusion balloon. At the end of this first stage of treatment, the therapy catheter positioned on the guidewire is exchanged for an aspiration catheter. After aspiration is completed, the balloon is deflated.

Second and third inflation durations as indicated inFIG. 8 may similarly correspond to subsequent sequences of therapy and aspiration treatments. After the occlusion balloon is deflated and the first sequence ends, the aspiration catheter is exchanged for another therapy catheter. Once the second therapy catheter is in place, the occlusion balloon is reinflated and the lesion is treated in the same manner as described above. Alternatively, the second and third inflation durations may refer to a therapy catheter which deploys a stent. In this embodiment as well, the occlusion balloon is not inflated until the aspiration catheter has been exchanged with the stent deploying catheter. By performing the treatment in such a manner, the amount of time that blood flow is blocked in the treated vessel is minimized.

Thus, the inflation durations as shown inFIG. 8 generally represent the amount of time it takes to perform a therapy treatment using one or more therapy catheters exchanged over the guidewire, exchange the therapy catheter for an aspiration catheter, and aspirate emboli. As shown inFIG. 8, the mean time to accomplish this procedure was about 150 seconds.FIG. 8 also shows a general reduction in inflation durations frompatient1 topatient24 as the clinician improved in performing the exchange over time. Accordingly, in a preferred aspect of the present invention, providing a rapid exchange method for use during emboli containment allows the clinician to quickly perform a treatment procedure while minimizing the risk to the patient due to blockage of blood flow.

The preferred method also reduces the treatment time by providing thecatheter10 with a side-access inflation port22, as shown inFIG. 9. To inflate theocclusion balloon20, theguidewire10 is preferably inserted into an inflation adaptor, as described below with respect toFIGS. 16-19,24-28C. By providing theinflation port22 on the side of theguidewire10, the adaptor can easily be attached to the guidewire and quickly inflate or deflate theballoon20 by a simple movement such as movingactuator220, as shown inFIG. 16. This in turn reduces the amount of time that theballoon20 occludes a treated blood vessel.

Furthermore, use of an adaptor makes the catheter much easier to handle. Because theguidewire10 is so small, it may difficult to handle by clinicians. By using an adaptor, however, the clinician need only insert the wire into the adaptor, close the adaptor, and actuate the adaptor, as described in further detail below.

Additionally, as shown inFIG. 17C, anadaptor200, described in further detail below, is preferably attached to alow volume syringe294 and ahigh volume syringe295. Anextension line293 is attached to fitting210 to allow fluid flow to and fromadaptor200.Low volume syringe294 is provided for accurate inflation ofballoon20. More particularly, low volume syringe is provided so that inflation can be performed safely and quickly.High volume syringe295 is provided for rapid deflation ofballoon20. By using this syringe system, inflation and deflation ofballoon20 through an adaptor can be performed quickly and efficiently. Further details regarding a syringe system are described in assignee's pending application entitled SYRINGE AND METHOD FOR INFLATING LOW VOLUME CATHETER BALLOONS, application Ser. No. ______, filed Feb. 19, 1998 (Attorney Docket No. PERCUS.023CP1), the entirety of which is hereby incorporated by reference.

Moreover, by providing an access port on the side of thetubular body18, theport22 can be made with a large cross-section to increase the amount of fluid passing through the port. This in turn decreases the time necessary for inflating or deflatingballoon20. In addition, as described in more detail below, the use of a side-access port allows for more efficient opening and closing of theport22. Preferably, a sealingmember30 moves slidably withintubular body18 to plug and unplugport22. Becausemember30 remains attached to thecatheter10 even when theport22 is open, the operator never has to remove the sealing member. Accordingly, the sealing member is always in place, thereby reducing the time that it takes to open orclose inflation port22.

The speed of exchange is also increased by using an aspiration catheter with a high volume syringe. As shown inFIG. 17D,aspiration catheter60 is attached to anaspiration line296, connecting theaspiration catheter60 with ahigh volume syringe297. The high volume syringe allows rapid aspiration of emboli from the treated vessel, thereby reducing the time that theocclusion balloon20 must be inflated. Further details regarding aspiration are disclosed in the above-referenced application entitled ASPIRATION SYSTEM AND METHOD.

E. Diagnostic Methods

The preferred exchange method of the present invention is also applicable to diagnostic methods. In one preferred aspect of the present invention, a method is provided wherein emboli found or created in the body are removed from the body for diagnostic testing. A guidewire with a distal occlusive device is inserted into the body to a point distal of plaque. A therapy catheter is advanced over the guidewire to the location of the plaque. After the distal occlusion device is deployed, a therapy treatment, such as inflation of a dilatation balloon or any other means as described above, is performed to break up the plaque and produce emboli. The therapy catheter is then exchanged with an aspiration catheter while the occlusion device remains deployed, and the aspiration catheter removes the particulate matter for analysis.

In the procedures conducted on the 24 patients described above inFIG. 8, particulate matter was retrieved in all but 1 of 23 procedures and 45 of 48 aspirations. Mean particle size was 168 μm (range 8 to 3,427 μm) in the major axis, 80 μm (range 6 to 815 μm) in the minor axis, with an area of 32,117 μm²(range 42 to 4,140,000 μm²). Particulate material consisted predominantly of cholesterol clefts, lipid-rich macrophages, fibrous caps, necrotic core and fibrin material. Atherosclerotic material in the precipitate sections was quantified as maximal in 5 aspirates, moderate in 9, minimal in 26, and none in 3.

Vein graft aspirate was collected in tubes containing EDTA-citrate buffer and treated with 1% saporin to lyse interfering red blood cells. The remaining material was fixed in 10% neutral buffered formalin or glutaraldehyde and processed for light microscopy and scanning electron microscopy, respectively. Immunohistochemical staining was performed in some cases to confirm the presence of foam cells, smooth muscle cells and endothelial cells. A semiquantitative analysis of particulate bulk was performed. Particulate matter examined by scanning electron microscopy was measured in its major and minor access and the resultant two dimensional area, calculated. This suspended particulate matter may play a role in the pathogenesis of distal emoblization, no-reflow, infarction, and morbidity and mortality following vein graft intervention.

Tables 1 and 2 below show the results of quantitative analyses performed on vein graft aspirates. Table 1 shows the frequency of acellular plaque material in vein graft aspirates. Table 2 shows the frequency of cellular plaque material in vein graft aspirates. Values are expressed as the frequency of positive samples per case. Numbers in parentheses represent the percentage of positive samples.

TABLE 1


Frequency of Acellular Plaque Material in Vein Graft Aspirates.

	Necrotic	Cholesterol		Plaque
Samples	Debris	Clefts	Collagen	Hemorrhage

PTCA
	15/15 (100)	8/15 (23)	4/15 (27)	3/15 (20)
Stent 1	15/18 (83)	6/18 (33)	6/18 (33)	4/18 (22)
Stent 2	7/7 (100)	4/7 (57)	1/7 (14)	1/7 (14)

TABLE 2


Frequency of Cellular Plaque Material in Vein Graft Aspirates.

Samples	Foam Cells	Smooth Muscle Cells	Platelet Aggregates

PTCA
	14/15 (93)	0/15 (0)	2/15 (13)
Stent 1	17/18 (94)	0/18 (0)	4/18 (22)
Stent 2	6/7 (86)	0/7 (57)	2/7 (29)

II. Inflatable Guidewire Apparatus

One preferred embodiment for a catheter for use in the preferred method is shown inFIG. 9. InFIG. 9, there is depicted acatheter10 incorporating the low profile valve in a preferred aspect of the present invention. Although illustrated in the context of a simple occlusion balloon catheter, having a single inflation lumen and a single inflatable balloon, it is to be understood that the low profile valve can be readily adapted to a wide variety of balloon catheters, including those having additional functionalities, structures, or intended uses. For example, the low profile valve could be easily adapted to catheters having expandable members other than occlusion balloons, such as therapeutic dilatation balloons. Furthermore, the low profile valve may also be incorporated into catheters having two or more lumens. The manner of adapting the low profile valve to catheters having these various functionalities, structures, or intended uses will become readily apparent to those of skill in the art in view of the description which follows.

Catheter

10 generally comprises an elongate flexibletubular body18 extending between aproximal control end12 and a distalfunctional end14.Tubular body18 has a central lumen40 which extends between ends12 and14. Lumen40 has anopening23 atproximal end12, and is sealed fluid tight atdistal end14. The length oftubular body18 may be varied considerably depending upon the desired application. For example, wherecatheter10 is to be used as a guidewire for other catheters in a conventional percutaneous transluminal coronary angioplasty procedure involving femoral artery access, lengths oftubular body18 in the range of from about 120 to about 300 centimeters are preferred, with a length of about 180 centimeters often being used. Alternately, for a different treatment procedure, not requiring as long a length oftubular body18, shorter lengths oftubular body18 may be provided.

Typically,tubular body18 will have a generally circular cross-sectional configuration with an outer diameter within the range of from about 0.010 inches to 0.044 inches. Optimally, in most applications wherecatheter10 is to be used as a guidewire for other catheters, the outer diameter oftubular body18 ranges from 0.010 inches to 0.038 inches, and preferably is 0.020 inches in diameter or smaller, more preferably 0.014 inches in outer diameter or smaller. The diameter of lumen40 will be dictated, in part, by the outside diameter oftubular body18. For example, wheretubular body18 has an outer diameter of 0.014 inches, central lumen40 may have an inner diameter of from about 0.008 inches to about 0.010 inches. The diameter of lumen40 should be large enough to incorporate the low profile valve described below, and large enough to permit sufficient fluid passage for balloon inflation.

Noncircular cross-sectional configurations of lumen40 can also be adapted for use with the low profile valve described in a preferred embodiment of the present invention. For example, triangular rectangular, oval, and other noncircular cross-sectional configurations are also easily incorporated for use with present invention, as will be appreciated by those of skill in the art. The manner of adapting the valve of the present invention will become readily apparent in view of the description which follows.

In the preferred embodiment, thetubular body18 functions as a guidewire, and thus,tubular body18 must have sufficient structural integrity, or “pushability,” to permitcatheter10 to be advanced through vasculature to distal arterial locations without buckling or undesirable bending oftubular body18. It is also desirable fortubular body18 to have the ability to transmit torque, such as in those embodiments where it may be desirable to rotatetubular body18 after insertion into a patient. A variety of biocompatible materials, known by those of skill in the art to possess these properties and to be suitable for catheter manufacture, may be used tofashion tubular body18. For example,tubular body18 may be made of stainless steel, or may be made of polymeric materials such as nylon, polyamide, polyimide, polyethylenes, or combinations thereof. In one preferred embodiment, the desired properties of structural integrity and torque transmission are achieved by formingtubular body18 out of an alloy of titanium and nickel, commonly referred to as nitinol. In a more preferred embodiment, the nitinol alloy used to formtubular body18 is comprised of about 50.8% nickel and the balance titanium, which is sold under the trade name Tinel (TM) by Memry Corp. It has been found that a catheter tubular body having this composition of nickel and titanium exhibits great flexibility and improved kink resistance in comparison to other materials. One preferred embodiment oftubular body18 is disclosed in our copending application entitled HOLLOW MEDICAL WIRES AND METHODS OF CONSTRUCTING SAME, application Ser. No. 08/812,876, filed on Mar. 6, 1997, the entirety of which is incorporated herein by reference.

Thedistal end14 ofcatheter10 is provided with an atraumaticdistal tip16, and aninflatable balloon20, as illustrated inFIG. 9.Inflatable balloon20 may be made from any of a variety of materials known by those of skill in the art to be suitable for balloon manufacture. For example,inflatable balloon20 may be formed of materials having a compliant expansion profile, such as polyethylene or latex. In one preferred embodiment, whereinflatable balloon20 is to be used as an occlusion balloon, it is preferably formed of a block copolymer of styrene-ethylene-butylene-styrene (SEBS), sold under the trade name C-Flex™. One preferred embodiment of a C-Flex occlusion balloon is disclosed in our copending application entitled BALLOON CATHETER AND METHOD OF MANUFACTURE, application Ser. No. ______, filed on Feb. 19, 1998 (Attorney Docket No. PERCUS.010CP1), the entirety of which is incorporated herein by reference. Alternately, in those embodiments whereinflatable balloon20 is to serve as a dilatation balloon, it may be formed of materials having a noncompliant expansion profile, such as polyethylene terephthalate.Inflatable balloon20 may be attached totubular body18 in any manner known to those of skill in the art, such as heat bonding or through use of adhesives.

As shown inFIG. 9,catheter10 is provided with a side-access inflation port or opening22 formed intubular body18 at a point several centimeters distal from opening23.Inflation port22 is in fluid communication with central lumen40 extending throughtubular body18. A fill hole (not shown) is formed intubular body18 within the region enclosed byinflatable balloon20, such that fluid passing throughinflation port22 and into lumen40 may inflateballoon20. Conversely, aninflated balloon20 can be deflated by withdrawal of fluid fromballoon20, through lumen40, and out of side-access inflation port22.

The low profile valve may be used with catheters such as that described above, all well as with different catheters having different structures. In one preferred embodiment, the low profile valve comprises a sealing member which is movably positioned within the inner lumen of a catheter. The catheter has an inflation port, which, in some embodiments, is also an opening to the inner lumen at the proximal end of the catheter. An inflatable balloon is positioned on the distal end of the catheter, which is in fluid communication with the lumen and inflation port. The sealing member is inserted through the proximal opening into the lumen, with a portion of the sealing member extending outwardly from the proximal end of the catheter. The portion of the sealing member inserted into the lumen has a sealer portion which forms a fluid tight seal with the inner lumen to prevent fluid from passing past the sealer portion.

By application of a pushing or pulling force on the extending sealing member portion, the sealing member may be partially advanced within or withdrawn from the lumen, thereby moving the sealer portion within the lumen. In this manner, the sealer portion may be positioned within the lumen either proximally or distally of the inflation port. When the sealer portion is positioned proximally of the port, the valve is in the “open” position. When the valve is open, an unrestricted fluid pathway is established between the inflation port and the balloon, such that an external pressurized fluid source may be connected to the inflation port to inflate the balloon, or if the balloon is already inflated, the balloon may be deflated by application of a vacuum to the inflation port to withdraw fluid from the balloon. When the sealer portion is positioned distally of the inflation port, the valve is in the closed position, as the fluid tight seal between the lumen and the sealer portion prevents fluid from passing either to or from the balloon through the inflation port. Furthermore, when the valve is closed after balloon inflation, the fluid tight seal created by the sealer portion maintains the balloon in the inflated state in the absence of an external fluid source, by preventing the pressurized fluid within the balloon from escaping.

Referring toFIGS. 10, 11A and11B, there is depicted one embodiment of the low profile valve of the present invention, as used with the catheter ofFIG. 9.Catheter10, as described above, has a side-access inflation port22 which is in fluid communication with central lumen40, and through which fluid may be introduced to inflateballoon20. Central lumen40 has anopening23 atproximal end12. A sealingmember30 is inserted into lumen40 throughopening23. Sealingmember30 may be partially advanced within or withdrawn from lumen40 by the application of a longitudinal force on sealingmember30 directed toward or away fromproximal end12, respectively.

Sealingmember30 comprises amain shaft33, a tapering region31, and awire32. Sealingmember30 may be formed as solid piece out of suitable metals, such as stainless steel, nitinol and the like. For example, sealingmember30 may be formed as a solid cylindrical piece, and then be coined down at points along its length to form tapering region31 andwire32. Alternately, one or more of themain shaft33, tapering region31, orwire32 may be formed separately, and then attached to the other piece(s) by conventional means, such as soldering, to form sealingmember30. Polymeric materials, such as Delron™, nylon, and the like, may also be used to form sealingmember30, either as a solid piece, or as separate pieces which are later joined to form the sealing member.

Although not required, in one preferred embodiment,main shaft33 has an outer diameter no larger than the outer diameter of thecatheter tubular body18. Thus, if the outer diameter oftubular body18 is 0.014 inches, the diameter ofmain shaft33, and thus the largest diameter of sealingmember30, is no larger than 0.014 inches. Furthermore, it is also preferred thatmain shaft33 extend proximally from opening23 by a distance of at least several centimeters to facilitate the application of longitudinal forces onmain shaft33 to manipulate the position ofwire32 in lumen40. Moreover, aftercatheter10 has been fully inserted into a patient, an extendingmain shaft33 advantageously functions much like a conventional guidewire extension, providing a starting point for the clinician to insert other catheters overmain shaft33 andcatheter10.

The combined length ofcatheter10 and extendingmain shaft33 may be varied considerably at the point of manufacture, and may be adapted to the requirements of the other catheters which are to be used withcatheter10 andmain shaft33. For example, wherecatheter10 is to be used as a guidewire for other catheters in an “over-the-wire” embodiment, it is preferred that the total length ofcatheter10 with extendingmain shaft33 be about 300 centimeters. Alternately, whencatheter10 is to be used as a guidewire for other catheters in a single operator embodiment, or “RAPID-EXCHANGE” embodiment, it is preferred that the total length ofcatheter10 with extendingmain shaft33 be about 180 centimeters. As can be readily appreciated, the individual lengths ofcatheter10 and extendingmain shaft33 can be varied considerably and yet still achieve the overall desired combined length. For example, acatheter10 having a length of 180 centimeters can be provided with an extendingmain shaft33 having a length of 120 centimeters, to achieve the 300 centimeter total desired length for over-the-wire embodiments.

In another embodiment, where it is undesirable to have a long main shaft extending proximally fromcatheter10, a main shaft extending proximally only several centimeters may be provided. The shorter main shaft may be provided with an attachment (not shown), which is adapted to releasably secure longer extensions to the main shaft, such that it can also be used to facilitate the use ofcatheter10 as a guidewire for other catheters.

It is preferred thatmain shaft33 have a larger diameter than the other portions of sealingmember30, to make it easier to apply moving forces to sealingmember30. Thus, a tapering region31 may be disposed betweenmain shaft33 andwire32, to transition the outer diameter of sealingmember30 from the larger diameter ofmain shaft33 to the smaller diameter ofwire32. For the embodiment illustrated inFIGS. 9-11B, it iswire32 which is slidably inserted throughopening23 and into lumen40. Accordingly, the outer diameter ofwire32 must be less than the inner diameter of lumen40, so thatwire32 may be slidably accommodated therein. Moreover, in those embodiments where the end ofwire32 extends distallypast inflation port22 when the valve is in the open position, the gap between the outer diameter ofwire32 and the inner diameter of lumen40 must be sufficiently large so as not to significantly restrict the flow of fluid passing through lumen40 to or frominflation port22. Optimally, to facilitate the sliding ofwire32 within lumen40 and to permit inflation fluid flow,wire32 is from about 0.001 inches to about 0.004 inches smaller in outer diameter than the inner diameter of lumen40.

In a preferred embodiment,wire32 andcatheter10 are provided with positive stops to prevent the withdrawal ofwire32 from the proximal end ofcatheter10. For the embodiment depicted inFIGS. 11A and 11B, this consists of a pair of cooperating annular rings mounted onwire32 and lumen40, respectively. A first annular ring34 is coaxially and fixedly mounted onwire32 at a point onwire32 contained within lumen40. A second corresponding fixed annular ring35 projects inwardly from the interior surface of lumen40 nearproximal end12. The inner diameter of the opening of annular lumen ring35 is slightly larger than the outer diameter ofwire32, so as not to restrict the movement ofwire32 within lumen40. However, the outer diameter of annular wire ring34 is greater than the inner diameter of the opening of ring35, such that rings34 and35 cooperate to preventwire32 from being withdrawn from the proximal end ofcatheter10.

Rings34 and35 may be formed of any material which may be attached to wire32 and lumen40, respectively, and which possesses sufficient structural rigidity to act as a stop. Examples of suitable materials are metals and various hard polymers, such as stainless steel and Teflon™. In one preferred embodiment, wherewire32 andtubular body18 are both formed of nitinol, rings34 and35 are also formed of nitinol and are soldered to wire32 and the inner surface of lumen40, respectively.

As will be appreciated by those of skill in the art, cooperating stopping structures other than those described herein may also be used to prevent full withdrawal ofwire32 fromcatheter10. For example, annular ring34 may be replaced by one or more protrusions extending radially outwardly fromwire32, which are also adapted to cooperate with ring35 to prevent withdrawal ofwire32. Alternately, annular ring35 might be replaced by crimpingtubular body18 slightly to restrict movement of ring34 to points proximal of the crimp.

A lumen sealer portion36 is coaxially and fixedly mounted onwire32. Sealer portion36 is positioned onwire32 at a point distal to ring34, such that by partial withdrawal ofwire32 fromcatheter10, as depicted inFIG. 11A, sealer portion36 is capable of being positioned within lumen40 at a point proximal toinflation port22. Sealer portion36 is also located onwire32 at a point such that whenwire32 is fully inserted into lumen40, as depicted inFIG. 11B, sealer portion36 either fully coversinflation port22, or is located within lumen40 at a point distal toinflation port22. The leading edge36aand trailing edge36bof sealer portion36 are preferably tapered, so that the edges of sealer portion36 do not catch uponinflation port22 when sealer portion36 passes byport22.

It is preferred that sealer portion36 form a fluid tight seal with the outer diameter ofwire32 and the inner diameter of lumen40, such that fluid in lumen40 is prevented from flowing past sealer portion36. In the embodiment illustrated inFIGS. 11A and 11B, this is achieved by providingwire32 with a sealer portion36 that firmly contacts the entire inner circumference of a section of lumen40 along a substantial portion of the length of sealer portion36. The fit between the outer surface of sealer portion36 and the inner surface of lumen40 is tight, such that a fluid tight seal is created which prevents fluid from passing past sealer portion36. However, sealer portion36 must be capable of being moved within lumen40 upon movement ofmain shaft33, tapering region31, andwire32. Thus, the fit between sealer portion36 and lumen40 must not be so tight as to prevent movement of sealer portion36 in lumen40 upon application of sufficient longitudinal force onmain shaft33. Moreover, the fluid tight seal created by the fit between lumen40 and sealer portion36 must be maintained as sealer portion36 is moved back and forth within lumen40.

Sealer portion36 must also be capable of maintaining a seal at fluid pressures conventionally used to inflate catheter balloons, and should be capable of maintaining a seal at pressures which exceed conventional inflation pressures. Preferably, sealer portion36 is capable of maintaining a seal at pressures up to about 10 atmospheres, more preferably pressures up to about 30 atmospheres, and most preferably at pressures up to about 60 atmospheres. Sealer portion36 is also preferably capable of undergoing multiple valve-opening and valve-closing cycles without losing the structural integrity required to form seals capable of withstanding pressures of from about 10 atmospheres to about 60 atmospheres. Optimally, sealer portion36 is capable of undergoing at least 10, and preferably at least 20, valve-opening and closing events and still be capable of maintaining a fluid tight seal at a pressure of 10 atmospheres.

In one embodiment, the desired properties of sealer portion36 are attained by forming sealer portion36 out of an extruded polymeric tubing. Pebax™ tubing having an inner diameter of 0.008 inches and an outer diameter of 0.017 inches, and a hardness of 40 durometers, is first necked by heating the extruded tubing to a temperature of between 210 and 250 degrees Fahrenheit. Tube pieces of about 0.5 mm in length are then cut from the larger tubing. The cut Pebax™ tubes are then placed on a nitinol wire having an outer diameter of about 0.006 inches, and are heated and shaped to recover a tube that has an outer diameter of between 0.010-0.011 inches. The adhesive Loctite 4014™ may then be used to bond the heat-shaped Pebax™ tubing to the nitinol wire. When the adhesive dries, the leading and trailing edges of the bound Pebax™ seal may be trimmed, leaving an annular lumen contact length of about 0.010 inches (0.25 mm). The wire bearing the Pebax™ sealer portion may then be inserted into the opening of a nitinol catheter having a lumen with an inner diameter of about 0.0096 inches. Sealer portions of this type have been observed to hold pressures of up to 30 atmospheres, and are capable of undergoing multiple valve-opening and closing events without significantly diminishing the seal strength.

As will be appreciated by those of skill in the art, different forms of Pebax™ starting materials may be used to form sealer portion36. For example, in another preferred embodiment, similar steps were used with a Pebax™ tube having similar dimensions but a hardness of 70 durometers, to create a sealer portion.

It is contemplated by the present inventors that methods and materials other than those described above may be used to make a lumen sealer portion having the desired properties. For example, materials other than Pebax™, silicone, latex rubber, C-Flex™, Nusil™ and gels, which are known to possess adequate surface properties to function as a sealer portion, and also be lubricous enough to be moved within lumen40, may also be used to form sealer portion36. In addition, sealer portion36 may be attached to wire32 by alternate means, such as by integrally molding sealer portion36 towire32, dip forming sealer portion36 towire32, as well as other means of attaching a polymeric material to a wire known to those of skill in the art.

Other embodiments of sealer portion may not create a completely fluid tight seal between the sealer portion and the inner lumen at balloon inflation pressures. In these embodiments, however, the sealer portion creates a seal which prevents substantially all inflation fluid flow past the sealer portion, such that the inflatable occlusive device is maintained in an almost fully expanded state for extended periods of at least one minute, preferably 2 or more minutes, more preferably at least 10 minutes, and optimally at least 20 minutes or longer, and still be capable of providing clinically effective occlusion of any emboli particles in the blood vessel during this time period.

In a preferred embodiment, there is provided movement-force increasing structure, to increase the force required to move sealer portion36 from the valve-closed to the valve-open position. Structure of this type advantageously minimizes the risk of an accidental opening of the valve, and subsequent balloon deflation, during a medical procedure. In the embodiment illustrated inFIGS. 11A and 11B, this is achieved by providing a biasing spring37, which surroundswire32 between stops34 and35. Spring37 exerts a force on stop34, pushing it, and thuswire32 and sealer portion36, in the distal direction, so that sealer portion36 forms a fluid tight seal by either coveringport22 or by being positioned within the lumen at a point distal toport22. Consequently, in the absence of a competing force, spring37 maintains sealer portion36 in the valve-closed position. Sealer portion36 may be moved proximally to the valve-open position by application of a longitudinal force onmain shaft33 directed proximally fromend12 of sufficient magnitude to overcome the force of spring37. Optimally, spring37 is selected so that the force that must be applied tomain shaft33 to overcome the force of spring37 is from about 0.3 to about 1.0 pound-foot. In alternative embodiments, the movement force increasing structure may comprise waves introduced into the wire just proximal of the sealer portion, as described below, which also may require 0.3 to 1.0 pound-foot of force to overcome.

Referring toFIGS. 12 and 13, there is illustrated in alternative embodiment of the valve of the present invention. The alternative embodiment comprises acatheter110 which may have features which are substantially identical, in materials, structure, and function, as the catheter described in connection withFIGS. 9-11B.Catheter110 has aproximal end112, and a distal end (not shown) to which is mounted an expandable member, such as an inflatable balloon. Acentral lumen140 extends withintubular body118 between the proximal and distal ends. Anopening123 tolumen140 is present at theproximal end112 ofcatheter110.

A sealingmember130 is inserted intolumen140 throughopening123, as described previously. Sealingmember130 comprises asealer portion136, awire132,

annular rings

134 and135, andsupport member150. Sealingmember130 may be formed out of materials and by methods as described previously.

As illustrated inFIGS. 12 and 13, the outer diameter ofwire132 is less than the inner diameter oflumen140, such that sealingmember130 is slidably insertable intolumen140. Furthermore, alumen sealer portion136 is coaxially and fixedly mounted to wire132 near the distal end ofwire132.Sealer portion136 forms a fluid tight seal with the outer diameter ofwire132 and the inner diameter oflumen140, such that fluid introduced intolumen140 throughopening122 is prevented from flowingpast sealer portion136 at normal balloon inflation pressures of 1 to 3 atmospheres for occlusive devices, and as much at 10 atmospheres or more for other types of balloons.Sealer portion136 may be provided withleading edge136aand trailingedge136b, both tapered, to facilitate movement of sealingportion136 proximally and distally ofinflation port122.Sealer portion136 forms a fluid tight seal by firming contacting the entire inner circumference of a section oflumen140 along a substantial portion of the length ofsealer portion136. As described previously,sealer portion136 prevents substantially all fluid flow past the seal created bysealer portion136, and the movement ofsealer portion136 proximally and distally ofport122 may be used to effect the valve-open and valve-closed positions.

Cooperating positive stops, consisting of

hollow cylinders

134 and135 are provided to prevent withdrawal of sealingmember130 fromlumen140.Hollow cylinder135 is attached to the inner surface oflumen140 by adhesives, soldering, crimping, or by other means known to those of skill in the art, such that the proximal portion ofhollow cylinder135 extends withinlumen140, and is secured therein, and the distal portion ofcylinder135 extends fromproximal end112.Cylinder135 has a lumen (not shown) extending therethrough. The diameter of the cylinder lumen is larger than the outer diameter ofwire132, so that movement ofwire132 is not restricted. A secondhollow cylinder134, preferably of shorter length, is placed overwire132 and is fixedly mounted towire132, by soldering, or other means, at a point distal tocylinder135. The outer diameter ofcylinder134 is less than the inner diameter oflumen140, so as not to restrict the movement ofwire132 withinlumen140. However, the outer diameter ofcylinder134 is greater than the inner lumen diameter ofcylinder135, so that

cylinders

134 and135 act as cooperating stops, to preventwire132 from being withdrawn fromlumen140.

Cylinders

134 and135 may be formed of any material which may be attached towire132 andlumen140, respectively, and which possesses sufficient structural rigidity to act as a stop. Examples of suitable materials are metals and various hard polymers, such as stainless steel, Teflon™, and the like. In one preferred embodiment, wherewire132 andtubular body118 are both formed of nitinol,

cylinders

134 and135 are also formed of nitinol, and are soldered to wire132 and the inner surface oflumen140, respectively.

The distal portion ofcylinder135 extending fromproximal end112 is inserted intosupport member150.Support member150 comprises atubular body158 having an outer diameter and inner lumen diameter which are approximately the same astubular body118. Consequently, because the outer diameter ofcylinder135 is less than the inner lumen diameter ofsupport member150, the extending portion ofcylinder135 is slidably disposed within thesupport member150 inner lumen.

Wire

132 extends proximally fromcylinder135 withinsupport member150, as shown inFIGS. 12 and 13. A segment ofwire132 withinsupport member150 is secured to supportmember150 atpoint152.Wire132 may be secured to supportmember150 by any means known to those of skill in the art, including use of adhesives, crimping, soldering or welding. Becausewire132 is secured to supportmember150, the application of longitudinal forces onsupport member150 results in movement of sealingmember130 withinlumen140, to open or close the valve, as described above with respect toFIGS. 9-11B. Advantageously, use ofsupport member150 protectswire132 from undesirable kinking or bending when sealingmember130 is moved.

As illustrated inFIGS. 12 and 13, sealingmember130 has movement-force increasing structure which increases the force required to move sealingmember130 withinlumen140. The movement-force increasing structure consists ofwaves138 formed inwire132 just proximal tosealer portion136.Waves138 contact the inner surface oflumen140, thereby increasing the frictional forces which must be overcome to movewire132 withinlumen140. In one preferred embodiment, wherewire132 is made of nitinol and has an outer diameter of 0.006 inches, and is inserted into a nitinol catheter which has aninner lumen140 with the diameter of about 0.010 inches, waves are formed onwire132 for one and one-half cycles with an amplitude of about 0.016 inches to increase the valve-opening movement force.

Referring toFIGS. 14 and 15, there is illustrated another embodiment of the present invention. Referring toFIG. 14, there is provided acatheter400 having atubular body418 and inflatable balloon (not shown) as described above.Catheter400 may be formed of materials and methods as described above, and may have structural aspects identical to those described previously, except where otherwise noted. In particular, as shown inFIGS. 14 and 15,catheter400 is not provided with a side-access port on the catheter tubular body, nor is there provided cooperating positive stops on the wire and lumen. Instead, the sealer portion may be fully withdrawn from the lumen. Once the sealer portion is removed, the proximal opening serves as an access port for attached devices to inflate or deflate the balloon. The sealer portion can be inserted through the proximal opening into the lumen after balloon inflation to maintain the balloon in the inflated state.

Catheter

400 has aproximal end412, and a distal end (not shown) to which is mounted an inflatable balloon. Acentral lumen440 extends withintubular body418 between the proximal and distal ends. Anopening423 tolumen440 is present at theproximal end412 ofcatheter400.

A sealingmember430 is inserted intolumen440 throughopening423. Sealingmember430 has amain shaft433, a taperingregion431, and awire432. Sealingmember430 may be formed of materials and by methods as described previously. As illustrated inFIGS. 14 and 15, the outer diameter ofmain shaft433 is less than the inner diameter oflumen440, such thatmain shaft433 is slidably insertable intolumen440. In addition, the outer diameters of taperingregion431 andwire432 are also smaller thanmain shaft433, and thuslumen440, such that taperingregion431 andwire432 are also slidably insertable inlumen440. A portion ofmain shaft433 preferably extends proximally fromend412, to facilitate application of moving forces upon sealingmember430 to movewire432 withinlumen440, as described previously.

As illustrated inFIGS. 14 and 15, sealingmember430 has movement-force increasing structure which increases the force required to move sealingmember430 withinlumen440. The movement-force increasing structure consists of

waves

438aand438bformed inwire432 near its distal end.

Waves

438aand438bcontact the inner surface oflumen440, thereby increasing the frictional force which must be overcome to movewire432 withinlumen440. In one preferred embodiment, wherewire432 is made of nitinol and has an outer diameter of 0.006 inches, and is inserted into a nitinol catheter which has aninner lumen440 with a diameter of about 0.010 inches, waves are formed onwire432 for 1½ cycles with an amplitude of about 0.016 inches to increase the valve-opening movement force.

Alumen sealer portion436 is coaxially and fixedly mounted onwire432.Sealer portion436 forms a fluid tight seal with the outer diameter ofwire432 and the inner diameter oflumen440, such that fluid introduced intolumen440 throughopening423 is prevented from flowingpast sealer portion436 whensealer portion436 is inserted intolumen440.Sealer portion436 forms the fluid tight seal by firmly contacting the entire inner circumference of a section oflumen440 along a substantial portion of the length ofsealer portion436, and may be formed of materials and by methods as previously described.

In some removable sealing member embodiments, the sealing member is not provided with a separate sealing portion, as described above. In these embodiments, the sealing member itself functions as a sealing portion which is inserted into the proximal opening to restrict fluid flow, and which may be partially or wholly removed to provide for a fluid pathway between the proximal opening and an expandable member on the distal end of the catheter. Preferably, the sealing members of these embodiments comprise a tapering rod, which at its distal end, has an outer diameter smaller than the inner lumen diameter of the catheter in which it is inserted as a plug, such that the distal end of the rod may be easily inserted into the catheter lumen through the proximal opening. The tapering rod increases in outside diameter at points proximal to the distal end. Consequently, one or more points of the rod have an outside diameter greater than the inner lumen diameter of the catheter in which it is inserted as a plug, such that by forcing the rod into proximal opening, the larger outer diameter of the rod forms a relatively fluid tight seal with the catheter lumen at the proximal opening of the catheter. An O-ring, or other polymeric structure, may be mounted in the inner lumen of the catheter at or near the proximal opening, to cooperate with the tapering rod in the creation of the seal. Thus, in this embodiment, the point where the seal is created does not move with respect to the catheter, but is instead stationary at or near the proximal opening of the catheter.

Referring toFIG. 20, there is depicted an alternative embodiment of the valve the present invention. The alternative embodiment is provided to acatheter500, formed of atubular body518 and having aproximal end512.Catheter500 has anopening523 at is proximal end, and alumen540 extending the length of the tubular body.Lumen540 is in fluid communication with an expandable member (not shown) mounted on the distal end oftubular body518. A side-access port522 is provided intubular body518 at a point distal toproximal end512.Catheter500 may have aspects identical, both in structure, dimensions, materials, and construction, to catheters described previously.

A sealingmember550 is positioned withinlumen540 nearproximal opening523 and side-access port522. Sealingmember550 is formed from a shorttubular body568, having alumen590, which is sealed atend562, but open at the other end. Sealingmember550 has, an outer diameter slightly larger that the inner diameter oflumen540, but smaller than the outer diameter oftubular body518, such that sealingmember550 may be tightly fit withinlumen540 throughopening523, to form a fluid tight seal over catheterproximal opening523. Cooperating stopping structures (not shown) may be provided to sealingmember550 andcatheter500 to prevent removal of sealingmember550 fromlumen540 at elevated pressures. Sealingmember550 may be formed out of the same materials astubular body518.

Tubular body

568 is provided with anopening572 extending therethrough.Opening572 is positioned ontubular body568 such thatopening572 is capable of aligning with side-access port522 when sealingmember550 is rotated withinlumen540, or is moved proximally or distally withinlumen540. Arotation element595, such as a perpendicular attachment, may be provided facilitate rotation of sealingmember550 withinlumen540. Other rotation elements, such as notches or grooves, may be used in place of the perpendicular attachment, as will be appreciated by those of skill in the art.

Sealingmember550 functions as a valve withincatheter500, controlling fluid flow through side-access port522. When sealingmember550 is rotated so thatport522 andopening572 are aligned, fluid may flow throughport522 throughlumen540 to inflate the occlusive device. Upon the desired inflation, sealingmember550 may be rotated, as for example by ninety degrees, or moved proximally or distally withinlumen540, such thatopening572 is no longer aligned withport522, andtubular body568 blocks fluid flow throughport522.

Shown inFIG. 21, is an alternative embodiment of the rotatable sealing member. Numerals corresponding to those of the embodiment ofFIG. 20 have been used to illustrate the similar structural aspects between the two embodiments. Sealingmember650 is identical in construction to the sealing member ofFIG. 20, except that sealingmember650 is somewhat larger, and is adapted to be slipped overtubular body618. The respective diameters oftubular body618 and sealingmember lumen690 are such that a fluid tight seal is created overlumen623. Side-access inflation port622 may be aligned withopening672, as above, by rotation or longitudinal movement, to provide fluid access to lumen640 throughport622.

In certain embodiments, it may be desirable for sealing

members

550 and650 to have a longer length, such that they may function as an extension for other catheters to be inserted over

catheters

500 and600. In these embodiments, sealing

members

550 and650 may be formed with longer tubular bodies, or be provided with attachments so that extension members may be releasably secured thereto.

Referring toFIGS. 22, 23A and23B, there is illustrated an alternative embodiment of the present invention featuring a self-closing valve. The alternative embodiment comprises acatheter700 having an elongate flexibletubular body718 extending between aproximal control end712 and a distal functional end (not shown), and having a balloon (not shown) as described previously.Tubular body718 hascentral lumen740 which extends between the proximal and distal ends.Lumen740 has anopening723 atproximal end712, and is sealed fluid tight at the distal end. A sideaccess inflation port722 is formed intubular body718 at a point distal ofopening723.Inflation port722 andlumen740 are in fluid communication with the distal inflatable balloon, as described previously.

Awire732 is inserted intoopening723, and is slidably disposed withinlumen740. Accordingly, the outer diameter of thewire732 must be less than the inner diameter oflumen740, so thatwire732 may be slidably accommodated therein. Asealer portion736 is coaxially mounted onwire732.Sealer portion736 is of similar type and construction to the sealer portion described in connection withFIGS. 9-11B.Sealer portion736 is positioned onwire732 at a point distal toinflation port722, and forms fluid-tight seal with the outer diameter ofwire732 and the inner diameter oflumen740, such that fluid introduced intolumen740 is prevented from flowingpast sealer portion736. Consequently, becausesealer portion736 is positioned withlumen740 distal toinflation port722,sealer portion736 is in the valve-closed position.

In the embodiment depicted inFIGS. 22-23B,tubular body718 is formed from a material having a certain degree of elasticity, such that if theproximal end712 oftubular body718 is secured to wire732 atpoint750, and a longitudinal force is applied totubular body718 in a direction distal to end712, the elasticity oftubular body718 results in the shifting ofinflation port722 in the distal direction. Moreover, slits711 may be formed intubular body718 nearproximal end712 to enhance the elastic response oftubular body718, thereby increasing the distal translocation ofinflation port722 upon application of an axial force totubular body718.Wire732 may be secured totubular body718 by any means known to those of skill in the art, such as adhesives, welding, soldering, or crimping.

In a preferred embodiment,tubular body718 is made out of nitinol, and has at least 8% elasticity whenlongitudinal slits711 are introduced at the proximal end. As can be observed inFIG. 23A, in the absence of any longitudinal force applied totubular body718,sealer portion736 is positioned withinlumen740 at a point distal toinflation port722, such that fluid may not pass throughport722 to inflate or deflate the balloon. However, if a longitudinal force is applied totubular body718 in the distal direction, and the proximal end oftubular body718 andwire732 are held in position, tubular body will stretch, as shown inFIG. 23B, andinflation port722 will be translocated in the distal direction so thatsealer portion736 will be located within the lumen proximally ofport722. This will establish an unrestricted fluid pathway betweeninflation port722 and the distal balloon, so that the balloon may be either inflated or deflated by passage of fluid throughport722. Upon removal of the longitudinal force, the elastic response oftubular body718 will result in proximal translocation ofinflation port722, andsealer portion736 will once again be in the valve-closed position.

Referring toFIG. 16 and17A, there is illustrated aninflation adaptor200 which may be used to inflate and to open and close the low profile valve depicted inFIGS. 9-13.Inflation adaptor200 comprises a housing having afirst half202 and asecond half204, which are preferably formed of metal, medical grade polycarbonate, or the like.

Halves

202 and204 are attached to one another by a pair ofhinges205 positioned on one of the lateral edges of each half, such that

halves

202 and204 may be separated or joined in a clam shell manner as depicted inFIGS. 16 and 17. Alocking clip230 secureshalf202 tohalf204 whileinflation adaptor200 is in use. Lockingclip230 may be provided with an angledleading edge235 to facilitate closing ofclip230 to secure

halves

202 and204 together.Springs209 may also be provided to facilitate opening ofadaptor200.

Agroove240 separatesfirst half202 fromsecond half204 when the halves are closed andclip230 is secured.Groove240 is of sufficient width to accept the proximal end of a catheter having the low profile valve, as described in detail above. A fitting210 is positioned onhalf202, to create aninflation passageway212 which terminates in opening285 on the interior surface offirst half202. Fitting210 is preferably a standard luer connector which may be attached to a variety of existing external pressurized fluid sources, although other types of fittings, such as tubings, quick connects, and Y-site connections, may be easily substituted for a luer fitting.

A seal comprising a pair ofgaskets280 is positioned around opening285 on the interior surfaces of

halves

202 and204.Gaskets280 are in alignment, such that when halves202 and204 are brought together and secured by lockingclip230, a fluid tight inflation chamber is created within the interior region defined bygaskets280. The fluid tight inflation chamber is in fluid communication with fitting210 viainflation passageway212, so that a pressurized inflation fluid may be introduced into the fluid tight inflation chamber by attaching an external pressurized fluid source to fitting210. Moreover,gaskets280 are preferably formed of resilient materials, such as silicone, C-Flex™ and Pebax™, so thatgaskets280 may form-fit over a catheter tubular body which extends across the lateral edges ofgaskets280, to create the fluid tight chamber.

Anactuator220 is positioned on the external surface ofhalf202. In the embodiment illustrated inFIGS. 16 and 17,actuator220 controls a cam which operates a slidingpanel283 on the interior surface ofhalf202. Slidingpanel283 moves back and forth along a line which bisectsopening285. When actuator220 is moved to a first position, slidingpanel283 moves toward opening285 along this line. When actuator220 is moved to a second position, slidingpanel283 moves away from opening285 along the same line. A corresponding slidingpanel284 is positioned onhalf204, such that

panels

283 and284 are aligned and move together when the position ofactuator220 is changed. To facilitate coordinated movement of

panels

283 and284, apin286, or such other similar engagement structure, may be provided to releasablysecure panel283 topanel284 when the adaptor is closed. The length of travel of

panels

283 and284 is preferably adjusted to provide the minimum sufficient distance to position the sealing member in the valve open or valve closed position, as desired.

Panels

283 and284 each have a roughenedsurface290, to facilitate the frictional engagement of

panels

283 and284 with the main shaft portion of the low profile valve. In a preferred embodiment,

panels

283 and284 are both made of silicone, and roughenedsurface290 comprisesteeth291 andgrooves292 formed on each of

panels

283 and284. Theteeth291 andgrooves292 cooperate, to permit the teeth of one panel to fit into the grooves of the opposite panel when the adaptor is closed.

For ease of understanding, the operation ofinflation adaptor200 to inflate the balloon of the catheter ofFIGS. 9-11B will now be described.Actuator220 is moved to the first position, so that sliding

panels

283 and284 are moved closer toopening285. Lockingclip230 is then undone, exposinggroove240.

Halves

202 and204 are then partially separated, andcatheter10, with theballoon20 deflated, is inserted into the inflation adaptor. As described previously,catheter10 has aninflation port22 located nearproximal end12, and amain shaft33 extending fromproximal end12.Catheter10, with the low profile valve in the closed position, is placed withingroove240 of partiallyopen adaptor200, andcatheter10 andmain shaft33 are placed within securing clips271 and272, such that when halves202 and204 are closed,inflation port22 will lie within the fluid tight inflation chamber created bygaskets280, and the extending portion ofmain shaft33, but notproximal end12, will rest between sliding

panels

283 and284. Analignment slot298 andoverlying shelf299 may be provided to facilitate alignment and prevent buckling or kinking of the catheter and sealing member during use.

As shown inFIG. 17B, in one embodiment,indicia260 are provided oncatheter10 andmain shaft33, which when aligned with indicia270 oninflation adaptor200, result in alignment ofinflation port22 with the fluid tight inflation chamber ofadaptor200, and alignment ofmain shaft33 with sliding

panels

283 and284, whencatheter10 and sealingmember30 are inserted intogroove240.Indicia260 and270 may take the form of markings, grooves or notches, or any other suitable means of aligning the valve with the inflation adaptor alignment indicia, may be provided. Preferably, the gap betweenindicia260 oncatheter10 andmain shaft33 is approximately equal to the space between clips271 and272, such that by placingindicia260 within clips271 and272,catheter10 andmain shaft33 are properly aligned withinadaptor200.

Indicia solely on the catheter tubular body may also be used to facilitate correct alignment. For example, two visible markings may be place on the catheter on either side of the catheter inflation access port. By inserting the catheter intolower half204 so that both of these markings are place withinlower half gasket280, the catheter inflation access port will be within the fluid tight inflation chamber created bygaskets280 when

halves

202 and204 are secured to one another.

Oncemain shaft33 andinflation port22 are properly aligned withinadaptor200, lockingclip230 is secured.Inflation port22 now lies within the fluid tight inflation chamber created bygaskets280, andmain shaft33 rests between sliding

panels

283 and284. The clinician may then attach an external pressurized fluid source to fitting210.

To inflateballoon20, the clinician moves actuator220 from the first position to the second position, thereby causing sliding

panels

283 and284 to move away from opening285. Becausemain shaft33 is firmly secured between

panels

283 and284, a longitudinal force directed away fromproximal end12 is applied tomain shaft33. The longitudinal force onmain shaft33 results inwire32 being partially withdrawn from lumen40, which causes sealer portion36 onwire32 to be moved to a position within lumen40 which is proximal ofinflation port22. The movement of sealer portion36 proximally ofinflation port22 opens the low profile valve, by establishing an unrestricted fluid pathway betweeninflation port22 andballoon20.

The external pressurized fluid source may then be activated, as for example by pushing the plunger on a syringe, such that pressurized fluid passes throughpassageway212 andopening285 into the fluid tight inflation chamber. The pressurized fluid then passes throughinflation port22 and lumen40, to inflateballoon20.

Inflated balloon

20 may be maintained in the inflated state, in the absence of the pressurized fluid source, by closing the low profile valve. This is accomplished by movingactuator220 back to the first position, thereby causing sliding

panels

283 and284 to move towardopening285. The moving panels apply a longitudinal force, directed towardproximal end12 tomain shaft33, causingwire32 to be further inserted into lumen40. Consequently, sealer portion36 is moved from a position, within lumen40 which is proximal toinflation port22 to a position in lumen40 which is distal toinflation port22. The fluid tight seal created by sealer portion36 traps the pressurized fluid within lumen40 andballoon20, thereby maintainingballoon20 in the inflated state. The external pressurized fluid source may then be deactivated and removed. Once the low profile valve is closed,inflation adaptor200 may be removed by unlockingclip230, and removingcatheter10 andmain shaft33 fromgroove240.

Referring toFIGS. 18 and 19, there is illustrated an alternative embodiment of an inflation adaptor especially adapted for manipulating removable low profile valves, although it may be used with side-access embodiments as well. Moreover, it should also be appreciated thatadaptor200 and similar type adaptors may also be used to manipulate removable valve embodiments.

Adaptor

300 comprises anouter sleeve320 formed of metal, medical grade polycarbonate, or similar such materials.Outer sleeve300 defines a taperinginner lumen350.Lumen350 tapers fromlarge diameter352 which is significantly greater than the outer diameter of the catheter tubular bodies inserted intolumen350, to asmaller diameter355, which is slightly larger the outer diameter of the catheter tubular body.Lumen350 is in fluid communication with aninflation passageway312 formed by fitting310, so that a pressurized inflation fluid may be introduced intolumen350. Releasable seals315 are positioned at each end oflumen350, such as to create a fluid tight inflation chamber withinlumen350 when a pressurized fluid source is attached. Releasable seals350 may comprise any type of seal known to those of skill in the are, such as Toughy Borst connectors, hemostatic valves, and the like. Releasable seals350 may also act to secure any catheters and sealing members inserted within thereleasable seal openings325

In use, a catheter and sealing member, such as that described in connection withFIGS. 14-15, is inserted intoopening325 afterseals315 have been opened. The catheter and sealing member are positioned underpassageway312, and the sealing member is removed from the proximal opening of the catheter. A fluid passageway is thereby created between the proximal catheter opening and the expandable member of the distal end of the catheter.Seals350 are closed to create a fluid tight chamber, and a vacuum and/or pressurized inflation fluid is applied, to inflate or deflate the balloon. After the desired inflation or deflation has occurred, the sealing member may be introduced into the proximal opening of the catheter tubular body to seal the lumen, either by hand or by a movable actuator (not shown).Seals350 may then be loosened, and theend access adaptor300 removed by sliding the adaptor off the end of the catheter and sealing member.

Referring toFIGS. 24-26B, there is illustrated an alternativeembodiment inflation adaptor800 which may also be used in conjunction with the low profile valves of the present invention, of the type depicted inFIGS. 9-13, to inflate or deflate catheter balloons.Inflation adaptor800 comprises a housing having afirst half802 and asecond half804, which are preferably formed of a medical grade polycarbonate. However, as will be appreciated by those of skill in the art, a great many other materials may by used to formadaptor800, including metals such as 300 series stainless steel and 400 series stainless steel, and polymeric materials such as Acrylonitrile-butadiene-styrene (ABS), Acrylics, and Styrene-acrylonitriles. Furthermore, the

individual halves

802 and804 may be manufactured in a variety of different ways. For example, where polymeric materials are used, it is preferable to use a mold to manufacture each of the halves. Moreover, in some embodiments, more than one molded piece may be used to form an individual half, with the various pieces being joined together by bonding or mechanical means to form a half. Alternately, as is known in the art, the individual halves can be formed through machining processes performed on larger blocks of the raw materials.

Halves

802 and804 are attached to one another by hinges806 positioned on one of the lateral edges of each half, through which a joiningpin805 is inserted, such that

halves

802 and804 may be opened or closed in a clam shell manner as depicted inFIGS. 24 and 25. Preferably, the cross-sectional angle formed by

halves

802 and804 in the open position, as shown inFIG. 25, is 90° or greater, and more preferably from 120°-180°, to facilitate insertion of a catheter intoadaptor800.

As shown inFIGS. 24 and 25, aplate832 is secured to the front portion ofhousing half804 by threescrews833.Plate832 is provided with two ormore pin receptacles834. Acam latch830 is mounted onplate832 and is secured thereto bypin831 which runs throughpin receptacles834 and a corresponding camlatch pin receptacles836, to form a hinge betweencam latch830 andplate832.Cam latch830 andplate832 may be made from any of the same variety of materials as

housing halves

802 and804, and for any particular embodiment, are preferably made of identical materials, although combinations of materials may also be used. Also, as is appreciated by those of skill in the art, the corresponding hinge structure provided byplate832 andcam latch830 may also be achieved by many other methods. For example,plate832 may be integrally molded withhousing half804 at the time of manufacture as a single piece, thereby eliminating the need forscrews833, but withcam latch830 mounted thereon as described above.

Cam latch

830 is designed to secure

halves

802 and804 together whenadaptor800 is in use, to assist in the creation of an the inflation seal as described above. Advantageously, by placing cam latch onhalf804 as shown, the adaptor interior is more accessible to the clinician during a procedure, and it is easier for the clinician to insert catheters intoadaptor800.Cam latch830 also serves the important function of preventing accidental opening of theadaptor800 during use. An important feature ofcam latch830 is the manner in which it cooperates withhousing half802 to create a releasable locking mechanism which applies great force to

halves

802 and804 upon closing, while at the same time using the principles of mechanical advantage to minimize the force the user must exert to closecam latch830. This is achieved by providinglatch830 with acammed surface838 and also providing the front edge ofhousing half802 with arounded lip837 to acceptcammed surface838, as shown in cross-sectional schematic form inFIGS. 27A-27C.

Referring toFIG. 27A, halves802 and804 have been brought together, withcam latch830 in its open position. Ascam latch830 begins to be closed, as shown inFIG. 27B,cammed surface838 contacts roundedlip837 and exerts a closing force thereon. Upon further closing, and to the fully closed position shown inFIG. 27C,cam latch830 acts as a lever, with the closing force betweencammed surface838 andlip837 being a function of the force of exerted by the user, the length of the lever (length of cam latch door), and the height of the cam surface, as defined by the following well known mathematical equation:

F_{u} = F_{c} \frac{H}{L}

F_u=User applied force
F_c=Closing force
L=length of lever (width of door)
H=height of can
However, as can be appreciated, because the lever length, which in the adaptor embodiment is the length ofcam latch830 in its closing direction, is much greater than the height of the cam created bysurface838 andlip837, the closing force exerted is always greater than the force the user exerts oncam latch830. Thus, very tight seals may easily be created by the clinician when the device is used.

Cam latch

830 is also preferably provided with ashelf835 to secure

halves

802 and804 together.Shelf835 is positioned onlatch830 at a point such that whenlatch830 is in its closed position,shelf835 firmlycontacts housing half802 along the side bearing hinges806. Preferably,shelf835 has an angled leading edge to facilitate closing oflatch830.

Agap840 separatesfirst half802 fromsecond half804 when the halves are closed and latch830 is secured.Gap840 is of sufficient width to accept the proximal end of a catheter having the low profile valve, as described in detail above, without crimping the catheter to impair its function. A fitting810 is positioned onhalf802, to create aninflation passageway812 which terminates in opening885 on the interior surface offirst half802. Fitting810 is preferably a standard luer connector which may be attached to a variety of existing external pressurized fluid sources, although other types of fittings, such as tubings, quick connects, and Y-site connections, may be easily substituted for a luer fitting.

A seal comprising a pair ofgaskets880 is positioned around opening885 on the interior surfaces of

halves

802 and804.Gaskets880 are in alignment, such that when halves802 and804 are brought together and secured bycam latch830, a fluid tight inflation chamber is created within the interior region defined bygaskets880. The fluid tight inflation chamber is in fluid communication with fitting810 viainflation passageway812, so that a pressurized inflation fluid may be introduced into the fluid tight inflation chamber by attaching an external pressurized fluid source to fitting810.Gaskets880 are preferably formed of resilient materials, such as silicone, C-Flex™ and Pebax™ or Kraton™, silicone, and other elastomeric materials, so thatgaskets880 may form-fit over a catheter tubular body which extends across the lateral edges ofgaskets880, to create the fluid tight chamber.

Anactuator820 is positioned on the external surface ofhalf802. In the embodiment illustrated inFIGS. 24-26B,actuator820 is a rotatable knob controlling a cam which operates a slidingpanel883 on the interior surface ofhalf802. As will be appreciated by those of skill in the art, however, a great many different actuating structures other than rotatable knobs and sliding panels may be used to achieve the movement of the catheter sealing members described herein. Furthermore, where catheter valves require rotational movement, such as those ofFIGS. 20 and 21, rotational actuating mechanisms may be provided as well.

Slidingpanel883 moves back and forth along a line which bisectsopening885. When actuator820 is moved to a first position, shown inFIG. 26A, slidingpanel883 moves away from opening885 along this line. When actuator820 is moved to a second position, as shown inFIG. 26B, slidingpanel883 moves toward opening885 along the same line. A corresponding slidingpanel884 is positioned onhalf804, such that

panels

883 and884 are aligned and move together when

halves

802 and804 are closed and the position ofactuator820 is changed.

In actual clinical practice, the movement of

panels

883 and884 results in the opening and closing of a catheter valve placed withinadaptor800. When actuator820 is moved to the position shown inFIG. 26A,

panels

883 and884 move away from opening885. This would result in the opening of the valve described in connection withFIGS. 9-13, as the sealer portion of the valve would be positioned proximally of the access port to establish a fluid pathway between the access port and the inflatable balloon at the distal end of the catheter. Conversely, whenactuator820 is moved to the position shown inFIG. 26B,

panels

883 and884 move towardopening885. This would result in the closing of the valve, as the sealer portion of the valve would be positioned distally of the access port, thereby preventing substantially all fluid flow between the access port and those portions of the catheter distal to the sealer portion. Preferably, detents (not shown) are provided on the actuator camming mechanism to provide the user with tactile and audible feedback when the panels are nearest or farthest from opening885 (i.e., catheter valve is closed or open, respectively).

Adaptor

800 is also preferably provided with a safety lock, to prevent accidental opening when the adaptor is being used and the catheter valve is open. As shown inFIGS. 26A and 26B, this may be achieved by providing an extendingflanged portion822 toactuator knob820. Whenactuator knob820 is in the valve open position, as shown inFIG. 26A, extendingflange822 extends overlatch830, preventing the latch from being opened. In the valve closed position, as shown inFIG. 26B, flange821 is rotated away fromlatch830, which may then be opened.

Panels

883 and884 each have a roughenedsurface890, to facilitate the frictional engagement of

panels

883 and884 and their coordinated travel with the moving portions of the low profile valve.

Panels

883 and884 may be made from any of a variety of polymeric or metallic materials, but must possess sufficient frictional force to engage and move the catheter sealing member without slippage. Consequently, depending on the type of catheter used, those of skill in the art may desire to select different materials for

panels

883 and884 to maximize the frictional forces between the panels and their intended use catheter. In a preferred embodiment, in which

panels

883 and884 are to engage a catheter sealing member made from stainless steel,

panels

883 and884 are both made of Kraton 90A™, and roughenedsurface890 comprisesteeth891 andgrooves892 formed on each of

panels

883 and884. Theteeth891 andgrooves892 cooperate, to permit the teeth of one panel to fit into the grooves of the opposite panel when the adaptor is closed. Furthermore, alternative cooperating structure, such as dimples and ridges, may also be used to coordinate travel of

panels

883 and884.

One problem that has been recognized with low profile valves is the phenomenon of plug walk-out. That is, after the valve has been placed in its closed position, with the sealer portion of the sealing member distal to the inflation access port, and the adaptor removed, the internal forces on the sealing member tend to cause very small portions of the sealing member to be pushed out of the catheter proximal end. Plug walk out is undesirable as it has an adverse impact on the ability of the sealed catheter to act as a guidewire for other devices. It has been found, however, the plug walk out can be minimized or eliminated if the sealing member is initially “overdriven”, or forced slightly further in the catheter, during the sealing step.

Advantageously,adaptor800 is provided with an overdrive system to overdrive a sealing member into a catheter. Referring toFIG. 25,panel884 travels back and forth withinhousing recess894 along a which bisectsopening885, as described above. Aspring809 is mounted inrecess894 and is attached to the wall ofrecess894 andpanel884.Spring809 is biased so as to pushpanel884 towardopening885, andforces panel884 against the wall ofrecess894 which is opposite to that which spring809 is attached.

Referring toFIGS. 28A-28C, there is shown the top portion ofhalf802 containingpanel883.Panel883 resides inhousing recess893, and travels back and forth along a line which bisectsopening885, as described above. The movement ofpanel883 is controlled byactuator820, as described above. An expandedspring888 is attached topanel883, as shown inFIGS. 28A-28C.Spring888 has a strength which exceeds that oflower spring809. In the adaptor open position, as shown inFIG. 25, expandedspring888 contacts the wall ofrecess893, and pushespanel883 away from the recess wall to create anoverdrive gap886, as shown inFIG. 28A.

When a catheter with a valve in a closed position is loaded intohalf804, and

halves

802 and804 are closed and latched, theteeth891 ofpanel883 contact the grooves ofpanel884. The superior spring force ofspring888 then forces spring809 to compress a small amount, such thatpanel884 no longer is forced against the recess wall, and now has an overdrive gap (not shown) approximately equal tooverdrive gap886. The actuator may then be engaged to drive

panels

883 and884 away from opening885 towardrecess walls893aand894a, respectively, thereby opening the valve mechanism. The inflatable balloon on the catheter may then be inflated as described above.

Upon closure of the valve, by rotatingactuator820 in the opposite direction,

panels

883 and884 are moved towardopening885 until the sealer portion of the sealing member is distal to the catheter inflation access port. Overdrive of the sealing member is then achieved whenactuator820 is adjusted so that

panels

883 and884 are forced against

recess walls

893band894b, as shown forpanel883 inFIG. 28C. That is, the force ofactuator820 overcomes the force ofspring888, and drives the sealing member into the catheter by a distance farther than it initially resided before the valve was opened, the distance being approximately equal to the width ofgap886. It has been found that by overdriving the sealing member to a closed position further than its initial closed position compensates for plug walk-out. Preferably, the sealing member is overdriven by a distance of about 0.020 inches.

Alternative overdrive mechanisms may be used for other adaptor embodiments. For example, rather than mountingspring888 onpanel883, the spring might be mounted in aslot wall893b, with a plunger (not shown) attached topanel883 and aligned with the spring. In its unforced state, the spring would exert force on the plunger, pushingpanel883 away from wall893ato createoverdrive gap896. However, as before, theactuator mechanism820 could be used to overcome the spring force in the valve closing cycle, thereby creating the overdrive. Numerous other overdrive mechanisms may also be employed, as will be appreciated by those of skill in the art.

As illustrated inFIG. 25,adaptor800 is also provided withimmovable pads870 on both

halves

802 and804.Pads870 function to secure the catheter withinadaptor800 when it is closed, and to prevent movement of the catheter during valve opening and valve closing procedures. Accordingly, the material used forpads870 is selected to have a high degree of frictional force with respect to the surface of the catheter body to whichpads870 will contact. A wide variety of polymeric and metallic materials are thus suitable to formpads870 such as Kraton™, C-Flex™ or Pebax™. In one embodiment,pads870 are integrally molded with

halves

802 and804 out of medical grade polycarbonate, and are intended to contact a catheter tubular body formed from nitinol.

It is also preferred thathalf804 be provided with guiding means to facilitate correct positioning of the catheter into the adaptor. For the embodiment illustrated inFIG. 25, these guiding means consist of two ormore clips896 to facilitate positioning of a catheter into the adaptor.Clips896 are provided withgrooves897 in which the catheter is inserted and secured prior to closure ofadaptor800.Clips896 may be formed of any material flexible enough to be capable of releasably securing the catheters to be used inadaptor800. In one preferred embodiment, clips896 are formed of C-Flex 70A™. Onhalf802, and aligned withclips896, there are providedrecesses895, to acceptclips896 when

halves

802 and804 are brought together and closed. Preferably, alignment indicia on the catheters to be used withadaptor800 coincide with the spacing ofclips896, so that by placing the catheter portion bearing the indicia directly inclips896, the catheter is properly inserted in the adaptor with its inflation access port contained in the fluid tight inflation chamber created bygaskets880 upon closure ofadaptor800. A projectingridge875 may also be provided to facilitate placement of the catheter, and direct its orientation during placement in the adaptor so that alignment is proper.

Alternately, other guiding means may be used as well. For example, clips896 may comprise one or more magnetic elements which cooperate with gold-plated stainless steel rings (or other plated ferromagnetic substances) incorporated into the catheter tubular body to guide the catheter into the correct alignment position.

In one preferred embodiment, as shown inFIG. 25,

halves

802 and804 are also provided with projecting

shelves

898 and899, respectively, which come together when

halves

802 and804 are closed to form a slot therebetween in which the catheter resides. Advantageously, the slot created by

shelves

898 and899 acts to provide reinforcement to a catheter used inadaptor800 during the valve opening and closing procedures, and helps to prevent buckling or kinking of the catheter tubular body when

panels

883 and884 are moved to open or close the catheter valve.

In clinical practice, there is a direct correlation between the distance thatpanel884 moves and the distance moved by the sealer portion of a catheter valve whenadaptor800 is used. Consequently, a controlled and known movement ofpanel884 over a set direction and distance results in a movement of the valve sealer portion in the same direction and for substantially the same distance. Thus, with a controlled movement adaptor such asadaptor800, there is no need to require a catheter having positive cooperating stops to prevent removal of the sealer portion from the catheter, as was described for the catheter ofFIGS. 9-13. The adaptor itself prevents accidental withdrawal of the sealer portion from the catheter, by precisely controlling the movement of the sealer portion within the catheter.

Accordingly, in one preferred embodiment,adaptor800 is used withcatheter900, which lacks positive cooperating stops, and is depicted inFIGS. 29 and 30.Catheter900 has atubular body918 and inflatable balloon (not shown) as described above.Catheter900 may be formed of materials and methods as described above, and may have structural aspects identical to those described previously, except where otherwise noted.

Catheter

900 has aproximal end912, and a distal end (not shown) to which is mounted an inflatable balloon. Acentral lumen940 extends withintubular body918 between the proximal and distal ends. Anopening923 tolumen940 is present at theproximal end912 ofcatheter900. A side-access port922 in fluid communication withlumen940 is provided ontubular body918.

A sealingmember930 is inserted intolumen940 throughcentral lumen opening923. Sealingmember930 has afirst region935 which has an outer diameter substantially the same as the outer diameter of theproximal end912 of catheter tubular body.Region935 has ataper934, reducing in diameter to asecond region933 which has an outer diameter less than the inner diameter oflumen940.Region933 tapers overlength931 to form aplug mandrel wire932. As a consequence,region933 and plugmandrel wire932 are slidably insertable into theproximal opening923 ofcatheter900 and may freely move withinlumen940. In one preferred embodiment,region935 has an outer diameter of about 0.013 inches,region933 has an outer diameter of about 0.0086 inches, and plug mandrel wire has a diameter of about 0.005 inches, withregion933 and plugmandrel wire932 being inserted into a catheter having acentral lumen940 with an inner diameter of about 0.009 inches.

The length of sealingmember region935 extending proximally ofcatheter900 may vary in length depending upon the intended use environment. For example, wherecatheter900 is to be used as a guide for other catheters in an “over-the-wire” embodiment, it is preferred that the total length ofcatheter900 and sealingmember region935 be about 300 centimeters. Alternately, wherecatheter900 is to be used in a single operator or rapid exchange embodiment, it is preferred that the total length ofcatheter900 andregion935 be about 180 centimeters. Accordingly, with a known catheter length and use environment, an appropriate length forregion935 may be chosen.

The elements of sealingmember930 may be formed of materials and by methods as described previously. For example,

regions

935 and933 and plugmandrel wire932 may all be made out of metals such a stainless steel. Alternately, combinations of materials may be used as well. For example, in some applications it may be desirable to manufacture

regions

935 and933 out of stainless steel, while manufacturingplug mandrel wire932 out nitinol. Furthermore, the various sealing member regions may be made from a single metal wire strand coined at various points to achieve the desired dimensional tolerances, or multiple segments may be joined together to form sealingmember930.

Where multiple segments are joined,region935,region933, and plugmandrel wire932 are attached to one another by any suitable means of bonding metal to metal, such as soldering, brazing, adhesives and the like. In one preferred embodiment, cyanoacrylate adhesives are used to adhere these various parts of sealingmember930 to one another.

As illustrated inFIGS. 29 and 30, the outer diameter of sealingmember region933 is less than the inner diameter oflumen940, such thatregion933 is slidably insertable intolumen940. In addition, the outer diameters of the taperedportions931 andwire932 are also small enough such that they too are slidably insertable inlumen940. However, the outer diameter ofregion935 is greater than theinner diameter940, and thus only a small portion of taperedportion934 of sealingmember930 betweenregion935 andregion933 is insertable intolumen940 throughopening923. Advantageously, this provides for a snug interference fit when sealingmember930 is fully inserted intocatheter900. This interference fit provides a frictional force which counteracts the tendency of the pressurized fluids and internal wire flexing in the catheter to push sealingmember930 out ofopening923.

As illustrated inFIGS. 29 and 30, sealingmember930 has movement-force increasing structure which increases the force required to move sealingmember930 withinlumen940. The movement-force increasing structure consists of

waves

938aand938bformed inwire932 near its distal end.

Waves

938aand938bcontact the inner surface oflumen940, thereby increasing the frictional force which must be overcome to movewire932 withinlumen940. In one preferred embodiment, wherewire932 is made of nitinol and has an outer diameter of about 0.005 inches, and is inserted into a nitinol catheter which has aninner lumen940 with a diameter of about 0.090 inches, waves are formed onwire932 for 1½ cycles with an amplitude of about 0.016 inches to increase the valve-opening movement force.

Alumen sealer portion936 is coaxially and fixedly mounted onwire932.Sealer portion936 forms a fluid tight seal with the outer diameter ofwire932 and the inner diameter oflumen940, such that fluid introduced intolumen940 through side-access port922 is prevented from flowingpast sealer portion936 whensealer portion936 is inserted intolumen940 distally of side-access port922.Sealer portion936 forms the fluid tight seal by firmly contacting the entire inner circumference of a section oflumen940 along a substantial portion of the length ofsealer portion936, and may be formed of materials and by methods as previously described.

As shown inFIG. 29,sealer portion936 is positioned proximally of side-access opening922, so that an unrestricted fluid passageway exists betweenport922 and the inflatable balloon at the distal end ofcatheter900. This is the valve open position described above. In this position,region933 is shown partially withdrawn from opening923. Referring toFIG. 30,sealer portion936 is positioned distally ofport922, so that fluid flow betweenport922 and the inflatable balloon at the distal end ofcatheter900 are substantially blocked. This is the valve closed position described above.

Catheter

900 is changed from the valve open position to the valve closed position by the movement of sealingmember930 and its various components. Preferably, the exact length of movement needed to changecatheter900 from the valve closed to the valve open position is built into the movement function of the adaptor used to manipulate sealingmember930 thereby opening and closing the catheter valve. In this regard, it is preferred thatcatheter900 be used with an adaptor such asadaptor800, which provides for such controlled precise movement.

The “stroke-length”, or overall movement in one dimension, of sealingmember930 required to open or close the valve may be varied depending upon the catheter requirements. When relying upon the inflation adaptor to control movement, however, it is important that the movement of the controlling elements of the adaptor be coordinated with those of sealingmember930. With respect toadaptor800, this is accomplished by selecting arecess893 dimension which precisely defines the distance that sealingmember930 is to travel to achieve the valve open and valve closed positions, without accidentally removing sealingmember930 from opening923. In one embodiment, whereaccess port922 is positioned 36 mm from opening923, a stroke length of 5.5 mm was found to be suitable.

III. Expansion Members

The expansion members discussed herein include braids, coils, ribs, ribbon-like structures, slotted tubes, and filter-like meshes. These expansion members may be partially covered or completely surrounded by a membrane or other covering to provide occlusion or sealing of the vessel. As used herein, “occlusion” or “sealing”, and the like, mean partial or complete blockage of fluid flow in a vascular segment, as it is sometimes preferable to allow perfusion. Moreover, such expansion members may be deployed by various mechanical means, electrical means or thermomechanical means, etc., as described herein. Expansion members that are deployed mechanically are preferably “spring-like” in nature, i.e. they are preferably resilient to facilitate their deployment or retraction.

A. Catheter Apparatuses and Self-Expanding Braids

One embodiment of a catheter apparatus incorporating the present invention for treating occluded vessels is shown inFIGS. 31 and 32. As shown therein, thecatheter apparatus1651 consists of aflexible elongate member1652 which is provided with proximal and

distal extremities

1653 and1654. Aconventional adaptor1656 is mounted on the proximal extremity and is provided with a Touhy-Borst fitting1657 which is in communication with a largecentral lumen1658 extending from theproximal extremity1653 to thedistal extremity1654. An aspiration fitting1661 is provided on theadaptor1656 as well as anirrigation fitting1662, both of which are in communication with thecentral lumen1658. However, it should be appreciated that if desired, separate lumens can be provided in the flexible elongate member652 for both of the

fittings

1661 and1662.

Self-expandingsealing mechanism1666 is mounted on thedistal extremity1654. This self-expandingsealing mechanism1666 can take any suitable form. For example, as shown it can consist of abraided structure1667 formed of a suitable shape memory material such as a nickel titanium alloy that will attempt to expand to a predetermined shape memory. Other than shape memory materials, other materials such as stainless steel, Elgiloy™, titanium or other materials can be utilized in thebraid1667 as long as they have the capability of expanding when the self-expanding seal mechanism is released. Also it should be appreciated that the self-expandingseal mechanism1666 can be comprised of an absorbent material which when it absorbs saline or blood expands to form a seal. Such seals can be readily accomplished because it is only necessary to form a seal of approximately 1.5 psi to prevent small particles from moving downstream.

In order to prevent abrasion of a vessel, it is desirable to cover thebraided structure1667 with a covering1668 of a suitable material such as a polymer or a biocompatible coating which extends over thebraided structure1667 and which moves with thebraided structure1667 as it expands and contracts. The polymer can be of a suitable material such as silicone, C-flex, polyethylene or PET which would form a good sealing engagement with the wall of the artery. The covering1668 may be perforated to allow perfusion.

A mechanism is provided for compressing the self-expandingsealing mechanism1666 so that the apparatus can be inserted into the vessel1481 and consists of anelongate sleeve1771 having proximal and

distal extremities

1772 and1773 and abore1774 extending from theproximal extremity1772 to thedistal extremity1773. Acollar1776 is mounted on theproximal extremity1772 of thesleeve1771 and is positioned near theadaptor1656. Thecollar1776 serves as a mechanism for retracting the sleeve as shown inFIG. 32 to uncover the self-expandingsealing mechanism1666 after the catheter has been deployed to permit the self-expandingsealing mechanism1666 to expand and form a seal with the arterial vessel adjacent the stenosis to be treated.

Another embodiment of a catheter apparatus for treating occluded vessels incorporating the present invention is shown inFIGS. 33 and 34. As shown therein, theapparatus1781 consists of a guidingcatheter1782 having proximal and

distal extremities

1783 and1784. As shown, thedistal extremity1784 is provided with a pre-formed bend of a conventional type. Aconventional attachment1786 is mounted on theproximal extremity1783. Self-expandingseal mechanism1791 is mounted on thedistal extremity1784 and is of the type hereinbefore described in connection with the embodiments shown inFIGS. 31 and 32. Asleeve1796 similar to thesleeve1771 of the previous embodiment is provided in the present embodiment for encasing the self-expandingseal mechanism1791 and for releasing the same after it has been disposed in an appropriate position within a vessel adjacent the occlusion to be treated. Thus, asleeve1796 is provided having proximal and

distal extremities

1797 and1798 and having abore1799 extending from the proximal extremity to the distal extremity which is sized so that it can receive theguide catheter1782. It is provided with acollar1801 on its proximal extremity which is adapted to be disposed outside the patient and which is adapted to be grasped by the physician for pulling thesleeve1796 proximally to uncover the self-expandingseal1791 after the apparatus has been deployed to permit the self-expansion of thesealing mechanism1791 to form a seal with the vessel wall as shown inFIG. 34.

In accordance with the hereinbefore described descriptions, it is apparent that the apparatus can be readily deployed and serve the same function as the main catheter. To accomplish this, theassembly1781 can be introduced into the femoral artery and the distal extremity advanced into the desired location in the arterial vessel. After it has been properly positioned, the physician can retract thesleeve1796 to permit the self-expandingseal mechanism1791 to expand and to form a seal with the wall of the arterial vessel to occlude the arterial vessel and interrupt the flow of blood in the vessel to provide a working space distal of the occlusion formed. This prevents small particles which may thereafter be dislodged from moving downstream. Since a central lumen is available, the therapeutic procedures hereinbefore described can be employed with the catheter apparatus shown inFIGS. 31-34.

Although the self-expanding sealing mechanism1666 (1791) can be deployed by retracting the sleeve1771 (1796) as previously described, the sealing mechanism can also be deployed by pushing the flexible elongate member1652 (guiding catheter1782) through the sleeve so that the sealing mechanism can expand. This may be the preferred way of deploying the sealing mechanism1666 (1791), if there is little clearance between the apparatus1651 (1781) and the vessel within which the apparatus resides, to reduce the risk of damaging the patient's vessel. As discussed below in connection with subsequent figures, the sealing mechanism1666 (1791) may alternatively comprise members such as a coil, a ribbon-like structure, a slotted tube, or a filter-like mesh. In each case, the sealing mechanism expands to partially or completely occlude the vessel in question, or alternatively, to anchor an intravascular device to the vessel.

Furthermore, although the embodiments described inFIGS. 31-34 are illustrated with anadaptor1656 orattachment1786, these may be easily removed to allow an exchange of catheters over the

member

1652 or1782. Such an embodiment is shown inFIG. 35. When retracting thesleeve1796 to deploy thesealing mechanism1791, thesleeve1796 may remain on themember1782, or may be completely removed as shown inFIG. 36. By removing the sleeve completely, the catheters exchanged over the guiding member can have a lower profile to allow insertion into smaller vessels.

B. Alternative Self-Expanding Members

Another embodiment using a braided structure is shown schematically inFIG. 37, in which aflexible elongate member1020 is disposed within asecond elongate member1024 such as a hypotube. Aself expanding mechanism1028 such as a braided structure is secured to the distal end of theelongate member1020, preferably within anindentation1032 ofmember1020. Thebraided structure1028 is only partially encapsulated by a preferablyelastomeric membrane1036 that makes a seal with the patient'svessel1040. (Alternatively, a coating such as a polymeric coating may be used in place of the membranes disclosed herein.) In this and the other embodiments, adhesive may be used to secure the self-expandingmechanism1028 and themembrane1036 to theelongate member1020. In the embodiment ofFIG. 37, thebraided structure1028 andmembrane1036 are designed to be asymmetrical, with more material being concentrated at the proximal side of thestructure1028. The braids of the embodiments disclosed herein may bestainless steel304 or400, superelastic or heat activated Nitinol, an iron base shape memory alloy, or a polymer base, such as polyethylene or polypropylene. They may be constructed, for example, by using standard equipment such as a braider.

Although the embodiment ofFIG. 37 shows theflexible elongate member1020 connected to aguidewire tip1044, other technologies for guiding the device through the patient'svessel1040 may be used in this and the other embodiments, such as a guidewire (either over the wire or single operator) or the exchange catheter method, as is well known in the art. Also, although not explicitly shown in the embodiment ofFIG. 37 and the other embodiments herein, these embodiments may include lumens, aspiration and irrigation fittings, and collars like those illustrated inFIGS. 31-34.

Themembrane1036 is preferably impervious to the flow of blood (FIG. 38A) for those applications not requiring perfusion, although aperforated membrane1036′ (FIG. 38B) havingnumerous holes1037 therein may be used in other applications to allow the passage of blood. Theholes1037 are preferably greater than 10 microns in diameter and may be up to 80 microns or more in diameter to permit the passage of blood cells (nominally 6-10 microns in diameter) through themembrane1036′ while blocking larger particulates such as emboli. Likewise, aperforated membrane1036′ may be used in the other embodiments disclosed herein. Antithrombogenic coatings can be used (e.g., heparin) to prevent thrombosis formation.

FIG. 39 shows an embodiment in which abraided structure1050 is not enclosed by a membrane. When thebraided structure1050 comprises, for example, a diamond mesh pattern in which adjacent wires are separated by about 10-80 microns, the braided structure permits the passage of red blood cells, while blocking the flow of matter that may be undesirable, e.g., emboli or other particulates that may be formed or dislodged during medical procedures. Thus, this embodiment is well suited for applications for which perfusion is required.

Alternative self-expanding media are shown inFIGS. 40 and 41. InFIGS. 40 and 41, a self-expanding filter-like mesh1060 and a self-expanding slottedtube1072, respectively, are surrounded by amembrane1062 that is preferably elastomeric. The filter-like mesh1060 (or slotted tube1072) andmembrane1062 are bonded or otherwise secured to aflexible elongate member1064, e.g., to an indentation therein. As with the other self-expanding media disclosed herein, the filter-like mesh1060 (or slotted tube1072) expands from its unexpanded state when theflexible elongate member1064 is pushed through asecond elongate member1066, or alternatively, when thesecond elongate member1066 is retracted over the firstelongate member1064. The filter-like mesh1060 (or slotted tube1072) then expands so that themembrane1062 forms a seal with the surroundingvessel1068. Aguidewire tip1070 aids in guiding the device through thevessel1068. The filter-like mesh1060 and slottedtube1072 are of a suitable shape memory material such as Nitinol or (304 or400) stainless steel. The filter-like mesh1060 is fibrous in nature, being somewhat analogous to steel wool. The slottedtube1072 has a lattice-like appearance. The slottedtube1072 may be constructed, for example, by irradiating a thin-walled tube with a laser beam to form holes in the tube in the shape of polygons such as oblong quadrilaterals. An unexpanded, slottedtube1074 is shown inFIG. 42.

FIG. 43 illustrates another embodiment, in which acoil1080 serves as the self-expanding mechanism. Thecoil1080 may be integrally formed with a firstelongate member1082 or be otherwise specially joined to it, e.g., by welding or brazing the coil to theelongate member1082. Thecoil1080 is surrounded by amembrane1084 that expands with the coil when it is pushed out of asecond elongate member1086, or alternatively, when thesecond elongate member1086 is retracted from thecoil1080. Thus, the membrane forms a seal with the surroundingvessel1090. Themembrane1084 may be attached directly to the firstelongate member1082, or to amember1088 such as a disk that is in turn secured to thecoil1080 or the firstelongate member1082. Aguidewire tip1092 for guiding the device through thevessel1090 may be attached to the firstelongate member1082 or to themember1088, if one is used.

An embodiment similar to that shown inFIG. 43 is illustrated inFIG. 44, in which themembrane1084 is secured at the proximal end to aseparate sheath1094. In this case, thesheath1094 and the firstelongate member1082 are extended together over and through, respectively, thesecond elongate member1086. Assembly may require preloading thecoil1080 through the distal end of thesecond elongate member1086.

Another embodiment that employs a self-expanding medium is shown inFIG. 45, in which a plurality ofribbons1100 make contact with amembrane1102 while they expand to urge the membrane towards the wall of thevessel1104 where it makes a seal. Theribbons1100 of this embodiment are preferably secured to a firstelongate member1106 at both ends of the ribbons, by, for example, gluing them in place. The ribbons may be 0.001-0.004″×0.005-0.020″×0.25-1.0″ strips of Nitinol, stainless steel, or Elgiloy™ which expand when urged out of thesecond elongate member1108. Aguidewire tip1110 may be used for guiding the device through the vessel and is preferably secured to the distal end of the firstelongate member1106.

FIG. 46 illustrates an embodiment similar to the one inFIG. 45, in whichribs1120 such as wires form a series of semicircular arcs when they expand. Theribs1120 are surrounded by amembrane1122 that expands with the ribs to form a seal with thevessel1124. The number ofribs1120 is preferably at least three. Theribs1120 are preferably attached directly to a firstelongate member1124 that is surrounded by asecond elongate member1126. Theribs1120 themselves are preferably made of a shape memory material such as Nitinol or stainless steel. Aguidewire tip1128 aids in guiding the device through thevessel1130.

As in the other self-expanding embodiments, the self-expanding mechanism1100 (1120) is in an unexpanded state when enclosed by the second elongate member1108 (1126), and expands when pushed or pulled beyond the second elongate member1108 (1126).

C. Non-Self-Expanding Embodiments

1. Heat Activated Embodiments

FIGS. 44A and 44B illustrate how electrical means can be used to generate heat to expand an expansion member. Afirst elongate member1082′ (and acoil1080′ which adjoins it,coil1080′ andmember1082′ being similar to their unprimed counterparts) is preferably made of heat activated Nitinol, an iron base shape memory alloy, or another material that expands when exposed to heat. As shown inFIG. 44A, low profile, low resistivity

electrical lines

1081 and1083 preferably pass either through or along the secondelongate member86 and are attached (e.g., soldered) to the firstelongate member1082′ on either side of thecoil1080′. When current is applied through theelectrical lines1081 and1083 (the power supply is not shown but is preferably outside the patient), thecoil1080′ heats up through resistive heating, and the coil expands to urge themembrane1084 to contact thevessel wall1090. Alternatively, as shown inFIG. 44B, the firstelongate member1082′ may have acoating1085 of gold or silver. In this embodiment, thecoated elongate member1082′ is used to pass current (with most of the current preferably being carried by thecoating1085, so that most of the energy is deposited, in thecoil1080′), with the circuit being completed with alow resistivity wire1087 that is preferably connected (e.g., soldered) to either thesecond elongate member1086 or thesheath1094. This principle of resistive heating to expand a expansion member can be applied to the other embodiments disclosed herein as well.

FIGS. 45A, 45B and45C illustrate how heat transfer using a liquid can deploy an expansion member. Theribbons1100′ are preferably made of heat activated Nitinol, an iron base shape memory alloy, or another material that expands when exposed to heat. In the embodiment ofFIG. 45A, awarm saline solution1107 is passed between the first and second

elongate members

1106 and1108 and then over themembrane1102, so that heat is transferred to theribbons1100′. As theribbons1100′ heat up, they expand, thereby urging themembrane1102 against thevessel wall1104. As illustrated inFIG. 45B, thewarm saline solution1107 may also be passed through the firstelongate member1106 and then throughholes1109 inmember1106 so that thesaline solution1107 more directly transfers heat to theribbons1100′. In this embodiment, one ormore holes1111 in the membrane1102 (distal to where the seal with thevessel wall1104 is made) may be used to allow thesaline solution1107 to flow away beyond theribbons1100′ after heat transfer to the ribbons occurs. As illustrated inFIG. 45C, thesaline solution1107 may also be passed through one or more closed loop coils orlumens1113 within the firstelongate member1106. In this way, theribbons1100′ and the patient's blood are not exposed directly to any solution. Using heat transfer can also be applied to the other embodiments disclosed herein, provided the expansion member is suitably constructed.

2. Mechanically Deployed Embodiments

Other non-self-expanding sealing mechanisms that can be used for occluding a vessel are described below. In the embodiment ofFIGS. 47-49, a firstelongate member1140, preferably a pull wire, is (when the device is completely assembled) attached to abrace member1144 that is in turn attached to afirst ring member1148. Adjoining thefirst ring member1148 and asecond ring member1152 are a plurality ofribbons1156 that extend, between the two ring members. Surrounding theribbons1156 is amembrane1160 that forms a seal with the patient'svessel1162 when the ribbons are expanded. Themembrane1160 is joined to at least one and preferably both of the ring members′1148 and1152. Themembrane1160 can be joined to only one of the

ring members

1148 and1152, for example, when themembrane1160 extends far enough in the longitudinal direction to permit the membrane to make a good seal with thevessel1162 when theribbons1156 are deployed.

To assemble the device, the first and

second ring members

1148 and1152, theribbons1156, and themembrane1160 are placed as a unit around asecond elongate member1166, which has a pair of

oppositely facing holes

1170 and1172. Thebrace member1144 is inserted through the

holes

1170 and1172 and secured to both thepull wire1140 and thefirst ring member1148. Further, thesecond ring member1152 is secured to thesecond elongate member1166. This Assembled configuration, with theribbons1156 in their longitudinal orientation, is illustrated inFIG. 48. As illustrated inFIG. 49, when thepull wire1140 is retracted, the ribbons1156 (shown in phantom) and themembrane1160 that surrounds them are urged towards thevessel1162, where the membrane makes a seal with the vessel. Theribbons1160 are preferably resilient enough so that they return to their longitudinal orientation when thepull wire1140 is released. The elasticity and resilience of thepull wire1140 also helps theribbons1156 return to their undeployed configuration. Aguidewire tip1171 may be used to assist in guiding the device to the desired location in thevessel1162.

A preferred way of retracting thepull wire1140 is shown inFIGS. 50A and 50B.FIG. 50A shows thepull wire1140, which is attached to thebrace member1144. Arotatable handle1180 is attached to a lockingmember1184 which in turn is fastened to thepull wire1140. When the lockingmember1184 clears thesecond elongate member1166 within which it resides (which is preferably outside the patient), the locking member and rotatable handle1180 may be oriented as illustrated inFIG. 50B to keep thepull wire1140 taught, thereby preventing the sealing mechanism from returning to its undeployed position. Thepull wire1140 may be made of stainless or nitinol and may have a diameter of 0.006-0.008 inches, for a catheter having an O.D. of 0.014″, for example.

An alternative to the deployment apparatus illustrated inFIGS. 50A and 50B is shown inFIG. 51A, in which ahandle member1190 is grasped by the clinician to retract thepull wire1140, thereby deploying the sealing mechanism. Once extended, the sealing mechanism preferably has the tendency to return to its undeployed position, which in the process pulls thepull wire1140 back into thesecond elongate member1166. This can be prevented by inserting aspacer member1194 between the handle member190 and thesecond elongate member1166. After the medical procedure is complete, and occlusion of the vessel is no longer required, thespacer member1194 can be removed and thepull wire1140 and the sealing mechanism returned to their respective undeployed positions. The device can then be removed from the patient.

Both pull wire mechanisms shown inFIGS. 50A and 51A are preferably engaged by use of an

adaptor

1186 or1196, as shown inFIGS. 50C and 51B, respectively. This

adaptor

1186 or1196 allows for easier control of the pull wire mechanism. InFIG. 50C, theknob1188 is adapted to connect to therotatable handle1180 and lockingmember1184. By turning and pulling theknob1188, thepull wire1140 may be retracted to deploy the sealing mechanism. InFIG. 51B, thehandle1198 can be grasped to pullhandle member1190 away from secondelongate member1166. This opens up a space between

members

1190 and1166 to allowspacer member1194 to be inserted through a window inadaptor1196 for holding thepull wire1140 taut. Once the pull wire mechanism is engaged, the adaptor in both embodiments may be removed to allow for an exchange over the proximal end of the pull wire devices.

Although the principle of using a non-self-expanding mechanism has been illustrated inFIGS. 47-49 with respect to deformable ribbons, other non-self-expanding mechanisms, as illustrated inFIGS. 52A-52D, can be employed in conjunction with thebrace member1144 and the first and

second ring members

1148 and1152. For example, instead of usingribbons1156, a non-self-expandingbraided structure1200 can be used, in which thebraided structure1200 adjoins first and

second ring members

1148 and1152 and is covered with amembrane1160 to form theunit1204 shown inFIG. 52A. Theunit1204 can be used in conjunction with anelongate member1166, abrace member1144, aguidewire tip1171, a firstelongate member1140 such as a pull wire, arotatable handle1180, and a lockingmember1184 to form a device analogous to the ribbon-based device ofFIG. 47. Alternatively, other mechanisms can be used for securing thepull wire1140, such as ahandle member1190 and aspacer member1194.

Other non-self-expanding mechanisms such as a filter-like mesh1208, a slottedtube1212, and coils1216 can be used to form

units

1220,1230, and1240 analogous to thebraided structure unit1204 as shown inFIGS. 52B, 52C and52D.

Units

1220,1230, and1240 can likewise be used to construct devices analogous to the ribbon-based device illustrated inFIGS. 47-51. Further, ifunit1204 is used without a membrane, it may assist in blood perfusion if thebraided structure1200 is suitably constructed. Alternatively, perforated membranes likemembranes1036′ ofFIG. 38B may be used to permit blood perfusion. Although theribbons1156, thebraided structure1200, the filter-like mesh1208, the slottedtube1212, and thecoils1216 must be actively deployed (e.g. with a pull wire1140), they are nevertheless similar to their self-expanding counterparts.

It should be understood that the scope of the present invention is not be limited by the illustrations or the foregoing description thereof, but rather by the appended claims, and certain variations and modifications of this invention will suggest themselves to one of ordinary skill in the art.