# Patent

## Title
Thrombus removal system and process

## Abstract

A device capable of capturing and facilitating the removal of a thrombus in blood vessels (or stones in biliary or urinary ducts, or foreign bodies) uses a soft coil mesh with the aid of a pull wire or string to engage the surface of a thrombus, and remove the captured thrombus. The soft coil mesh is formed by an elongated microcoil element that forms the helical elements of a macrocoil element. The microcoil element provides a relatively elastic effect to the helical elements forming the macrocoil and allows for control of gripping forces on the thrombus while reducing non-rigid contact of the device with arterial walls. The use of multiple coil mesh elements, delivered through a single lumen or multiple lumens, preferably with separate control of at least one end of each coil, provides a firm grasp on a distal side of a thrombus, assisting in non-disruptive or minimally disrupted removal of the thrombus upon withdrawal of the device.

## Background
RELATED APPLICATION DATA
The present application is a continuation of U.S. patent application Ser. No. 11/356,321, filed Feb. 16, 2006, now U.S. Pat. No. 7,955,345, which is a continuation-in-part of U.S. patent application Ser. No. 11/097,354, filed Apr. 1, 2005, now U.S. Pat. No. 7,955,344.


BACKGROUND OF THE INVENTION
1. Field of the Invention
The present invention pertains to intravascular medical devices. More particularly, the present invention pertains to devices for isolating, capturing, and removing blood clots from a blood vessel. This same system may also be used to safely and effectively remove material from other cavities of the body, such as, for example, foreign bodies, or stones from the urinary or the biliary tracts.
2. Background of the Art
The present invention pertains generally to thrombus collection and removal. The process of thrombosis may produce a clot in a patient's vasculature. Such clots may occasionally be harmlessly dissolved in the blood stream. At other times, however, such clots may lodge in a blood vessel or embolize to a distal blood vessel where they can partially or completely occlude the flow of blood. If the partially or completely occluded vessel provides blood to sensitive tissue such as the brain or heart, for example, serious tissue damage may result.
When symptoms of vascular occlusion are apparent, such as an occlusion resulting in a stroke, immediate intervention is required to minimize tissue damage. One approach is to treat a patient with clot dissolving drugs, such as recombinant tissue plasminogen activator, streptokinase, or heparin. These drugs, however, do not immediately dissolve the blood clot and generally are useful only when administered within a short time period after onset of stroke symptoms.
Published U.S. Patent Application 2005/0038447 describes A medical device for removing clots from a blood vessel, comprising: a first longitudinally-oriented spine having a distal end; a pushing member coupled to the proximal end of the first longitudinally-oriented spine and extending proximally therefrom; and a clot-grabbing basket generally disposed between and coupled to the first longitudinally-oriented spine.
Published U.S. Patent Application 2004/0138692 discloses an embolus extractor, comprising: an elongated shaft having a proximal end and a distal end; first and second struts, each strut having a proximal end and a distal end coupled to the distal end of the shaft; the first and second struts having a first position and a second position, wherein in the first position, the distal ends and the proximal ends of the struts are spaced at a first distance, and in the second position the distal ends and the proximal ends of the struts are spaced at a second distance, the second distance being less than the first distance; and third and fourth struts, each strut coupled to one of the first and second struts via a proximal end and distal end.
Published U.S. Patent Application 2004/0098023 discloses a vasoocclusive device, comprising: a core member; and a fibrous structure carried by the core member, the fibrous structure comprises one or more strands of nanofibers. The vasoocclusive device may provide the fibrous structure in a product generated at least in part by an electrospinning process comprises the steps of: supplying a polymer solution through a needle; electrostatically charging the needle; electrostatically charging a metal plate that is placed at a distance from the needle, the metal plate having a charge that is opposite that of the needle, thereby sending a jet of the polymer solution towards the metal plate; and collecting the fibrous structure from the metal plate.
Published U.S. Patent Application 2004/0039435 discloses a self-expanding, pseudo-braided device embodying a high expansion ratio and flexibility as well as conformability and improved radial force. The pseudo-braided device is particularly suited for advancement through and deployment within highly tortuous and very distal vasculature. Various forms of the pseudo-braided device are adapted for the repair of aneurysms and stenoses as well as for use in thrombectomies and embolic protection therapy.
There are a variety of ways of discharging shaped coils and linear coils into a body cavity. In addition to those patents that describe physically pushing a coil out of the catheter into the body cavity (e.g., Ritchart et al.), there are a number of other ways to release the coil at a specifically chosen time and site. U.S. Pat. No. 5,354,295 and its parent, U.S. Pat. No. 5,122,136, both to Guglielmi et al., describe an electrolytically detachable embolic device.
A variety of mechanically detachable devices are also known. Various examples of these devices are described in U.S. Pat. No. 5,234,437, to Sepetka, U.S. Pat. No. 5,250,071 to Palermo, U.S. Pat. No. 5,261,916, to Engelson, U.S. Pat. No. 5,304,195, to Twyford et al., U.S. Pat. No. 5,312,415, to Palermo, and U.S. Pat. No. 5,350,397, to Palermo et al.
Various configurations have been used to remove calculi from the biliary or urinary system. See, for instance, U.S. Pat. No. 5,064,428. Additionally, devices having various configurations have been used to remove objects from the vasculature. For example, surgical devices comprising one or more expandable and collapsible baskets have been described for removing or piercing a thrombus in the vasculature. See, U.S. Pat. Nos. 6,066,149. 5,868,754 describes a three prong-shaped device for capturing and removing bodies or articles from within a vessel.
U.S. Pat. Nos. 5,895,398 and 6,436,112 to Wensel disclose a clot and foreign body removal device comprising a clot capture coil connected to an insertion mandrel within a catheter. The clot capture coil disclosed by Wensel is made out of a material with shape memory which allows it to be deformed within the catheter and then reformed to its original coil configuration when the coil is moved outside of the catheter lumen. The Weasel invention also provides for a biphasic coil which changes shape upon heating or passing an electric current, wherein the coil can be used to ensnare and corkscrew a clot in a vessel, which is then extracted from the vessel by moving the clot capture coil and catheter proximally until the clot can be removed. According to the Wensel invention, foreign bodies are similarly captured by deploying the coil distal to the foreign body and moving the clot capture coil proximally until the foreign body is trapped within the coil
Published U.S. Patent Application 2004/0225229 describes a device comprising a core wire having a distal end and a proximal end; a catheter shaft having a proximal catheter end, a distal catheter end and a lumen through which the core wire is passed such that the distal end of the core wire extends beyond the distal catheter end; a retrieval element disposed at the distal end of the core wire, the retrieval element movable from a radially contracted position to a radially expanded position; and a first stop element attached to the core wire, the first stop element configured to prevent over-expansion of the retrieval element.
Among commercial thrombus-removal systems are at least the following:

    
    
        1) The MERCI system of Concentric Medical that has a form of a corkscrew or helix spring. In this system, which may use a large 0.018 F microcatheter, the microcatheter tip is first positioned across the thrombus with the help of a guidewire after which the guidewire is exchanged with the system which is deployed distal and into the thrombus. The corkscrew shape of the device facilitates penetration into the thrombus. The thrombus can then be retrieved from the artery into a large 9 French guiding catheter, and removed from the patient's body.
        2) The In-Time system of Boston Scientific resembles a clam-shell when compressed, but once the microcatheter is placed through the thrombus and the device extended out of the microcatheter, it expands into 4 strings that form an oval, as with a rugby football. The system is then pulled back to engage and remove the thrombus from the blood vessel. This is similar to the disclosed structure in Published US Application 2004/0138692.
        3) Another system, known in the trade as a “lasso” is basically a simple catheter with a wire attached to its end. The wire makes a loop and enters back into the catheter (e.g., a large 0.018 F microcatheter). The operator changes the aspect of the loop by pulling on the wire. This system was originally conceived to catch foreign bodies.
        4) The Catch system of Balt is a stent closed on one end forming a basket that is deployed distal to the thrombus. The operator then pulls the system and retrieves the thrombus. This is similar to the structure in FIG. 7 of U.S. Pat. No. 6,805,684.

The above systems may have various practical and cost disadvantages. Although several of the commercial systems are designed to penetrate clot, this may in fact be impossible if the clot is made up of firm fibrin. The device may therefore not penetrate the clot but instead will slide over the thrombus. The process of engagement and retraction of a thrombus may also fractionate the clot, producing distal embolization. Currently available systems can also be difficult to guide or deploy at the site of the thrombus, or may be traumatic to the artery, and some systems are quite expensive. In addition, all these systems are bulky and cannot be safely and effectively used in small caliber blood vessels.

    
    


SUMMARY OF THE INVENTION
A device capable of isolating, capturing, and facilitating the removal of a thrombus in blood vessels (or stones in biliary or urinary ducts, or foreign bodies) uses a soft coil mesh with the aid of a pull wire to engage the surface of a thrombus, and remove the captured thrombus. The mechanical thrombectomy device is positioned by MRI or angiography guided percutaneous transluminal catheter delivery within the lumen of the blood vessel directly adjacent to the thrombus. The soft coil mesh is formed by an elongated microcoil element that forms the helical elements of a macrocoil element having an adjustable stiffness which provides reliable dynamic compliance matching with the viscoelastic properties of the thrombus undergoing removal. The microcoil elements further provide a relatively elastic effect to the helical element forming the macrocoil that allows for control of gripping forces on the thrombus while reducing non-rigid circumferential contact of the device with vessel endoluminal surfaces. The use of multiple coil mesh elements, delivered through a single lumen or multiple lumen catheters, preferably with separate control of at least one end of each coil, provides a firm grasp on a distal side of a thrombus, facilitating non-disruptive or minimally disruptive removal of the thrombus upon withdrawal of the device.
One aspect of the present invention is to provide a mechanical thrombectomy system that can reliably and safely navigate tortuous blood vessels to the site of an intracranial or extracranial thrombus.
A second aspect of the present invention is to provide a mechanical thrombectomy device that can reliably and securely entrap a soft or hard thrombus without fragmenting the thrombus or damaging the intima of the blood vessel.
A third aspect of this invention is to provide a mechanical thrombectomy device that is biocompatible, visible on both X-ray and MR imaging, and compatible with standard medical catheters.
A further aspect of this invention is to provide a mechanical thrombectomy device that can safely and completely remove thrombus of any density from any blood vessel in the human body.



BRIEF DESCRIPTION OF THE FIGURES
FIG. 1 shows a macrocoil with microcoils therein.
FIG. 1A shows the microcoil/macrocoil structure of the soft coil capture device described herein.
FIG. 1B shows the macrocoil loops constrained in a microcatheter, with a pull string attached to the distal tip of the macrocoil assembly which extends out of the microcatheter, and a pusher wire attached to the proximal end of the macrocoil assembly.
FIG. 2 shows the deployment of two separate microcatheters, each with a single macrocoil mesh element.
FIG. 2A shows the deployment of two separate microcatheters, each with a separate macrocoil mesh element, each macrocoil mesh element having separate end controls extending from each microcatheter. The two mesh elements are shown integrating on a distal side of a thrombus.
FIG. 2B shows the meshwork of the capture device in close contact with the distal portion of a thrombus within an artery.
FIG. 3 shows the capture device in a more extensively associated thrombus engaging position during the progression of the soft coil delivery.
FIG. 4A shows the capture device in a pre-capture position within an artery in a second mode of soft coil delivery, with the coil within a first microcatheter and an extraction wire or extraction string provided from a second microcatheter.
FIG. 4B shows the capture device of FIG. 4A with the macrocoil/microcoil element in a deployed position within an artery.
FIG. 5A shows the capture device in a format of providing two distinct macrocoil/microcoil systems.
FIG. 5B shows the capture device in a format of providing two distinct macrocoil/microcoil systems with separate extraction strings or separate retraction strings.
FIG. 6 shows a pneumatic delivery microcatheter delivery system with constrained coils within the catheter.
FIG. 7 shows a dual lumen catheter system deploying two macrocoil mesh elements, each with separate end controls of a mesh wire, which have entwined beyond a thrombus.
FIG. 7A shows a series of steps in which a dual lumen catheter is deploying two macrocoil mesh assemblies, each with separate end controls of the mesh wire in each lumen. The macrocoils have entwined and progressively encircle the thrombus as the microcatheter is withdrawn.



DETAILED DESCRIPTION OF THE INVENTION
The following description should be read with reference to the drawings wherein like reference numerals indicate like elements throughout the several views. The detailed description and drawings illustrate example non-limiting specific embodiments of the generic claimed invention.
FIG. 1 shows a structural material 2 that can be used as a soft coil capture element in the practice of the technology described herein. The material 2 has microcoils or microloops forming a continuing chain 6 of microcoils that form the macrocoil or macrohelix 10. The term ‘microcoil’ as used herein should not be confused with the RF or MRI responsive coils or microcoils that are used in the medical imaging art. The microcoils of the present invention are small coils compared to the macrocoils 10 which are large coils. The microcoils are made from the structural material (such as metal, polymeric or composite filament or wire) that forms the filaments, threads, fibers, or the like that are used to provide the microcoils that build into the macrocoils. The benefits of this material and the structure in which they perform will become apparent from the discussion herein.
The microcoils add a significant degree of dynamic compliance, effective elasticity, structural support and cushioning ability to the macrocoils. The microcoils elongate to give radial and circumferential elasticity to the material 2, without providing hard and large abrasive surfaces that might damage adjacent endoluminal surfaces of the blood vessels undergoing therapy, as would traditional coil or mesh structures. Upon removal of the macrocoil from the catheter, the macrocoil expands and retains microcoils along a length of the macrocoil. Furthermore, force is applied through the first wire on the distal end of the macrocoil thrombus engaging component adjacent to the catheter causes microcoils to bend towards the proximal end of the macrocoil thrombus engaging component and form loops.
FIG. 1B shows the attachment of the pull string 64 on the distal aspect of the macrocoil complex 10, and the attachment of the pusher (insertion) wire 67 on the proximal aspect of the macrocoil complex 10. The entire macrocoil complex 10 is constrained within the microcatheter 66.
FIG. 2 shows the deployment of two separate microcatheters 66a, each with a single macrocoil mesh element 2 passing between them. The macrocoil mesh element 2 extends over a thrombus 72 within the main catheter 50. The capture device 60 is shown, including the retraction string 64.
FIG. 2A shows the soft coil material 10 within an artery 50. The macrocoils 56 are shown with the entire length of the coil section 60 of the device being deployed in a slightly extended position beyond the thrombus 72. The pusher wires 67a and 67b stabilize the insertion ends 68a and 68b of the soft coil material 10. The push wires 67a and 67b tend to be thicker than the pull wires 64a and 64b as a matter of course, but they may be designed to be of the same or similar thicknesses, and the pull wires may be thicker than the push wires 67a and 67b. 
FIG. 2B shows the capture device 60 in an insertion position in initial contact with the distal portion of a thrombus 72 within an artery 50. A push wire 67b is shown in an exaggerated position, extending beyond its delivery microcatheter 66b. It is not necessary for the push (insertion) wire 67b to itself exit the microcatheter 66b, but only that it move so far forward as to assist the expulsion or deployment of the macrocoil material 10. The retraction wire or retraction string 64b has been shown in a position where it has pulled the material 10 into more intimate contact with the thrombus 72, with the two microcatheters 66a and 66b being themselves somewhat withdrawn from a position previously distal to the thrombus 72.
FIG. 3 shows a first mode of delivery of the system wherein the microcatheters 66a and 66b have been pulled past the thrombus 72 and then retracted, and the push wires 67a and 67b has been slightly extended beyond the microcatheters 66a and 66b (for illustrative and not essential purposes). The pulling wire 64b and the push wire 67b are sufficiently close together so that the entire length of the extended coil 60 is restrained, but the extended and somewhat retracted coil 60 encircles the major mass of the thrombus 72. The end of the pulling wires 64a and 64b have been retracted to pull the soft coil material 10 into a tangled engagement with the thrombus, engaging the thrombus 72 so that withdrawal of the microcatheter and the four wires 64a, 64b, 67a, and 67b will withdraw the thrombus 72 while enmeshed in the soft coil material. The entire enmeshing length 60 of the soft coil securely entrains the thrombus 72, and the soft coil material 10 assists in reducing breakage of the thrombus 72 and damage to the vascular walls.
FIG. 4A shows the system 100 delivered in a second delivery mode, with the microcatheters 106a and 106b passing the thrombus 72 mass. There is no push wire in this construction. Rather, there is a pull wire 112 deployed from microcatheter 106a so that the pull wire 112 is positioned in front of the restrained soft coil material 114 even while it is relatively in front of the thrombus 72. The insertion microcatheter has positioned an insertion or support element 110 which has been extended from the microcatheter 106a to deploy the soft coil material support element 114.
FIG. 4B shows that the pulling wire 112 has been extended (or retracted) slightly, causing the soft coil material 120 to deploy beyond the thrombus 72 and not yet enmesh the thrombus 72 within the soft coil material 120. By withdrawing the microcatheters 106a and/or 106b, and the two wires 116 and 110, the thrombus 72 can be first secured by the mesh 120 and then withdrawn from the vessel 50 with minimal damage to the vessel 50 and reduced breakage in the thrombus 72. The nature of the mixture of the microcoils and macrocoils causes a constriction of the material around the thrombus, without segmenting (cutting) the thrombus easily, and without providing a cage surface that is as potentially damaging to arterial walls as are other structures used for thrombus retrieval and capture.
The system is made of a 3D soft coil such that when the system gets deployed, it has the tendency to form a three dimensional mesh, with loops of macrocoils extending across the inner lumen of the blood vessel to assure that loops will be able to engage a thrombus when the loops are retracted. The ends of the coils may be attached on either its proximal end to a pusher wire and to its distal end to a very fine pull wire or visa versa. The entire system may be in a very thin format (although the size may vary depending upon the need for fit within particular arterial passages), and can fit into a 0.010 inch inner diameter microcatheter or smaller. Both the pusher wire attached to the macrocoils and the pull wire exit at the proximal end of the microcatheter and can be manipulated by the operator. First the microcatheter is positioned past the thrombus with the help of a microguidewire, preferably between the thrombus and the inner wall of the blood vessel. Once the distal end of the microcatheter lies beyond the thrombus (usually while it is in a distended state, fairly elongate and narrow), the microguidewire is exchanged for the thrombus retrieval system. The thrombus retrieval system is activated and deployed so that a significant portion of the entire length of coil (e.g., 1⁄5, 1⁄4 or one-third of the coil) is positioned distal to the thrombus. A remaining significant portion of the coil (using, by way of non-limiting examples of amounts, with one-third distal to or past the thrombus), such as at least 1⁄5, at least 1⁄4 or one-third or more of the coil length is wrapped around or co-distant with the thrombus and 1⁄4, 1⁄5 or one third or more is placed proximal to the thrombus. Once the coil is deployed with a significant portion at least at the distal end of the thrombus and more desirably a significant portion past the distal end of the thrombus, the operator pulls the thin distal pull wire, so that the mesh of coil loops that has formed around the thrombus or expanded beyond the thrombus retracts on itself and grabs securely the thrombus. The thrombus now can be pulled out of the artery by pulling the microcatheter, the pusher wire and the thin distal wire at the same time out of the artery.
Other advantages of the system (in addition to what has been described already) are its very small size so it can retrieve thrombus from very small arteries, its capacity to pull out the thrombus in one piece, and its softness, allowing manipulation without trauma to the vessel wall. Larger versions have the advantage of retrieving a very large thrombus in one piece. This system may be used in any vessel of the body for the retrieval of thrombus or other material like foreign bodies.
The distal end of the soft coil material (where the pulling wire is attached) may be limited in its ability to extend away from the proximal end of the soft coil material (where the push wire is attached) by using an internal connector, such as a thread, that attaches to both ends of the soft coil, and provides a physical limit to how far the coil may be distended.
Whatever the consistency of the clot, i.e., soft or hard, once the microcatheter has passed the clot, the distal mesh of coils when deployed will form a tight cap that should bring back at least a large part of the thrombus. The loops of the coil that surround the thrombus, producing a cocoon, will prevent the loss of parts of the thrombus if it breaks into pieces. The tendency of the system to break soft thrombus will depend on characteristics such as the soft coil material thickness, the microcoil thickness, the macrocoil thickness, density of the macrocoil, the 3D configuration of the macrocoils and the loop diameter of the coil. Even in the worst case envisioned, one could only deploy a distal and a proximal mesh or use a flow reversing system such as that in the MERCI system.
The pull wire functions to pull the distal tip of the macrocoil to facilitate the formation of a knot. If two macrocoils are used, a pull wire attached to each facilitates the formation of an even better knot. These knots are important to prevent the slippage of the macrocoils from the distal aspect of the thrombus during the removal process. After the macrocoils have been wound around the midportion and proximal aspects of the thrombus, the pull string is used to tighten the entire mesh network.
For a number of reasons, it may be desirable to capture and/or remove clots from the vasculature. The blood vessel can be essentially any vessel or even a duct of the urinary or biliary tracts. The device may include two or more longitudinal wires, for example a guidewire, a push wire and a pull wire, as well as other functional wires (e.g., conductive wires for other features provided with the device, such as a resistive wire to enable heating of the coils, if conductive/resistive. The basket member or region of soft coils is attached to or otherwise coupled with the wires. In general, the device (wires and soft coil material) can be advanced through the vasculature to a suitable location, for example past or adjacent to a clot, and expanded (when past or adjacent to the clot), so that the clot may be captured in the soft coils, upon operator action, and the captured clot can be removed from the vasculature.
The device may be configured to shift between a first generally collapsed configuration and a second generally expanded configuration, especially by the elastic memory of the coil material, and the guidance imposed by the at least two wires. In at least some embodiments, shifting between these configurations includes the longitudinal movement of one or both of the wires relative to one another. Movement of the Wires may occur in either the proximal or distal direction and, in the case of both wires moving, may be in the same or opposite directions. Shifting may also result in one or both of the wires moving somewhat laterally (especially with distally controlled wires on the coil material (e.g., with materials that bend when heated, or the like, and a heating element attached thereto) so that the wires become closer or move apart from one another.
Shifting between the collapsed and expanded configurations may occur in a number of differing manners. For example, the device or portions thereof may be made of a shape-memory material (such as nickel-titanium alloy or oriented coils) that can assume a pre-defined shape when unconstrained or when subjected to particular thermal conditions. According to this embodiment, the device can be manufactured to be “self-expanding” (when the longitudinal distension and restraint by the wires is removed) so that it can be delivered in a collapsed configuration, then shift to the expanded configuration when a constraint is removed (e.g., the distal ends of the two wires brought closer together) or when the device is subject to the natural thermal conditions within the blood vessel. Alternatively, shifting may occur by mechanically moving one or both of wires. Moving the wires may occur in a number of different ways such as by moving one or other of the wires attached to the distal or proximal end of the coil material on the device.
As described above, all or portions of the device (including but not limited to the coil materials and the wires) may be manufactured from polymeric, metallic, natural (e.g., gut wires), synthetic, or composite materials. Preferred materials tend to be polymeric, metallic, composite or mixtures or combinations of these materials. A conventional medical structural material such as nickel titanium alloy may be employed. However, any suitable material may be used including metals, metal alloys, polymers, etc. Some examples of suitable metals and metal alloys include stainless steel, such as 304V, 304L, and 316L stainless steel; linear-elastic or super-elastic nitinol or other nickel-titanium alloys, nickel-chromium alloy, nickel-chromium-iron alloy, cobalt alloy, tungsten or tungsten alloys, MP35-N (having a composition of about 35% Ni, 35% Co, 20% Cr, 9.75% Mo, a maximum 1% Fe, a maximum 1% Ti, a maximum 0.25% C, a maximum 0.15% Mn, and a maximum 0.15% Si), hastelloy, monel 400, inconel 825, or the like; or other suitable material.
Some examples of suitable polymers may include polytetrafluoroethylene (PTFE), ethylene tetrafluoroethylene (ETFE), fluorinated ethylene propylene (FEP), polyoxymethylene (POM), polybutylene terephthalate (PBT), polyether block ester, polyurethane, polypropylene (PP), polyvinylchloride (PVC), polyether-ester (for example a polyether-ester elastomer such as ARNITEL® available from DSM Engineering Plastics), polyester (for example a polyester elastomer such as HYTREL® available from DuPont), polyamide (for example, DURETHAN® available from Bayer or CRISTAMID® available from Elf Atochem), elastomeric polyamides, block polyamide/ethers, polyether block amide (PEBA, for example available under the trade name PEBAX®), silicones, polyethylene (PE), Marlex high-density polyethylene, Marlex low-density polyethylene, linear low density polyethylene (for example REXELL®), polyethylene terephthalate (PET), polyetheretherketone (PEEK), polyimide (PI), polyetherimide (PEI), polyphenylene sulfide (PPS), polyphenylene oxide (PPO), polysulfone, nylon, perfluoro(propyl vinyl ether) (PFA), other suitable materials, or mixtures, combinations, copolymers thereof, polymer/metal composites, and the like. In some embodiments, portions of or all of the device can be blended with a liquid crystal polymer (LCP). For example, the mixture can contain up to about 5% LCP.
In some embodiments, a coating, for example a lubricious, a hydrophilic, a protective, or other type of coating may be applied over portions or the entire device. Hydrophobic coatings such as fluoropolymers provide a dry lubricity which improves device exchanges. Lubricious coatings improve steerability and improve lesion crossing capability. Suitable lubricious polymers are well known in the art and may include silicone and the like, hydrophilic polymers such as polyarylene oxides, polyvinylpyrolidones, polyvinylalcohols, hydroxy alkyl cellulosics, algins, saccharides, caprolactones, and the like, and mixtures and combinations thereof. Hydrophilic polymers may be blended among themselves or with formulated amounts of water insoluble compounds (including some polymers) to yield coatings with suitable lubricity, bonding, and solubility. Some other examples of such coatings and materials and methods used to create such coatings can be found in U.S. Pat. Nos. 6,139,510 and 5,772,609, which are incorporated herein by reference. In some embodiments, the sheath or coating may be applied over basket region. This may provide extra surface area to contain clots that might be captured therein.
The sheath or polymeric layer coating may be formed, for example, by coating, electrophoresis, by extrusion, co-extrusion, interrupted layer co-extrusion (ILC), or fusing several segments end-to-end. The layer may have a uniform stiffness or a gradual reduction in stiffness from the proximal end to the distal end thereof. The gradual reduction in stiffness may be continuous as by ILC or may be stepped as by fusing together separate extruded tubular segments. The outer layer may be impregnated with a radiopaque filler material to facilitate radiographic visualization. Those skilled in the art will recognize that these materials can vary widely without deviating from the scope of the present invention.
The device, or portions thereof, may also be coated, plated, wrapped or surrounded by, doped with, or otherwise include a radiopaque material. For example, the wires or coils may be made from a radiopaque material or may include a radiopaque marker member or coil coupled thereto. Radiopaque materials are understood to be materials capable of producing a relatively bright image on a fluoroscopy screen or another imaging technique during a medical procedure. This relatively bright image aids the user of the device in determining its location. Some examples of radiopaque materials can include, but are not limited to, gold, platinum, palladium, tantalum, tungsten alloy, plastic material loaded with radiopaque filler, and the like.
An important practical concern in thrombectomy procedures is the accuracy of the navigational process used to direct the endovascular placement of a thrombectomy device relative to the location of a thrombus. Magnetic resonance imaging can play an important role in localizing and characterizing the thrombus and in optimizing the positioning of the thrombectomy device. High-speed, high-resolution MR imaging can now be combined with conventional X-ray fluoroscopy and digital subtraction angiography (DSA) capability in a single hybrid imaging unit. New generations of MR scanners provide frequently updated images of the anatomical structures of interest. This real-time imaging capability makes it possible to use high-speed MR imaging to direct the movement of catheters and other components of the thrombectomy system to specific endovascular locations, and thereafter observe the effects of specific interventional procedures.
MR imaging is also valuable in assessing the presence and size of an intracranial thrombus and in characterizing its age and composition. A growing body of evidence suggests that a combination of MR imaging and neurologic symptoms may in fact have prognostic predictive value in assessing patient outcome. During formation of a thrombus, the blood contains a mixture of oxyhemoglobin, deoxyhemoglobin and methemoglobin that is usually equal to that of arterial blood. As the thrombus ages, however, the concentration of paramagnetic hemoglobin and methemoglobin within the clot also changes resulting in a characteristic appearance on MR images that reflects the age and stability of the clot. Observation of these MR imaging changes can be clinically useful in evaluating the potential utility of various alternative interventions, such as, for example, drug thrombolytic therapy versus mechanical thrombectomy.
The catheter tip on thrombectomy devices described in the prior art is difficult to see on MRI because of inadequate contrast with respect to surrounding tissues and structures. This makes accurate localization difficult and degrades the quality of the diagnostic information obtained from the image. Thus, one objective of this invention is to provide an MR-compatible and visible device that significantly improves the efficacy and safety of thrombus removal using MR guidance. For example, to enhance compatibility with MRI imaging systems, it may be desirable to make portions of the device in a manner that would impart a degree of MRI compatibility. For example, the device, or portions thereof, may be made of a material that does not substantially distort the image and create substantial artifacts (artifacts are gaps in the image). Certain ferromagnetic materials, for example, may not be suitable because they may create artifacts in an MRI image. The device, or portions thereof, may also be made from a material that the MRI machine can image. Some materials that exhibit these characteristics include, for example, tungsten, Elgiloy, MP35N, nitinol, and the like, and others.
Any material that might be added to the structure of a pliable catheter to make it MR visible must not contribute significantly to the overall magnetic susceptibility of the catheter, or imaging artifacts could be introduced during the MR process. It is also important that thrombectomy devices used under MR guidance are MR-compatible in both static and time-varying magnetic fields. Examples of such biocompatible and MR-compatible materials which could be used to practice the invention include elastomeric hydrogel, nylon, teflon, polyamide, polyethylene, polypropylene, polysulfone, ceramics, cermets steatite, carbon fiber composites, silicon nitride, and zirconia, plexiglass, and poly-ether-ether-ketone.
Although the mechanical effects of the magnetic field on ferromagnetic devices present the greatest danger to patients through possible unintended movement of the devices, tissue and device heating may also result from radio-frequency power deposition in electrically conductive material located within the imaging volume. Consequently, all cables, wires, and devices positioned within the MR imaging system must be made of materials that have properties that make them compatible with their use in human tissues during MR imaging procedures. Many materials with acceptable MR-compatibility, such as ceramics, composites and thermoplastic polymers, are electrical insulators and do not produce artifacts or safety hazards associated with applied electric fields. Some metallic materials, such as copper, brass, magnesium and aluminum are also generally MR-compatible, viz. large masses of these materials can be accommodated within the imaging region without significant image degradation.
Guidewires for the catheter component of the thrombectomy system are usually made of radiopaque material so that their precise location can be identified during a surgical procedure through fluoroscopic viewing. Exemplary of guidewires used under X-ray viewing is the guidewire disclosed by LeVeen, U.S. Pat. No. 4,448,195, in which a radiopaque wire can be identified on fluoroscopic images by metered bands placed at predetermined locations. U.S. Pat. No. 4,922,924, awarded to Gambale et al. discloses a bifilar arrangement whereby radiopaque and radiotransparent filaments are wrapped on a mandril to form a bifilar coil which provides radiopaque and radiotransparent areas on the guide wire. U.S. Pat. No. 5,375,596 to Twiss et al. discloses a method for locating catheters and other tubular medical devices using an integrated system of wire transmitters and receivers.
Initial attempts to position and visualize endovascular devices such as catheters in MR imaging were based on passive susceptibility artifacts produced by the device when exposed to the magnetic field. Magnetic susceptibility is a quantitative measure of a material's tendency to interact with and distort an applied magnetic field. U.S. Pat. No. 4,827,931, to Longmore and U.S. Pat. Nos. 5,154,179 and 4,989,608 to Ratner disclose the incorporation of paramagnetic material into endovascular devices to make the devices visible under MR imaging. U.S. Pat. No. 5,211,166 to Sepponen similarly discloses the use of surface impregnation of various “relaxants”, including paramagnetic materials and nitrogen radicals, onto surgical instruments to enable their MR identification. An improved method for passive MR visualization of implantable medical devices has been disclosed by Werne in U.S. Pat. No. 5,744,958. In the method of the invention disclosed by Werne, an ultra thin coating of conductive material comprising 1-10% of the theoretical skin depth of the material being imaged is applied. By using a coating of 2,000-25,000 angstroms thickness, Werne has found that the susceptibility artifact due to the metal is negligible due to the low material mass. At the same time, the eddy currents are limited due to the ultra-thin conductor coating on the device.
However, these patents do not provide for artifact-free MR visibility in the presence of rapidly alternating magnetic fields, such as would be produced during echo-planar MR imaging pulse sequences used in real-time MR guided thrombectomy procedures. Nor do these patents teach a method for monitoring with MR-visible catheters the outcomes of therapeutic interventions, such as, for example, removal of a thrombus from the intracranial circulation followed by therapeutic drug delivery into brain tissues. Thus, there is a continuing need to develop an MR-compatible and visible thrombectomy device that does not obscure surrounding anatomy, and thereby compromise the physician's ability to perform the intervention.
The control wire(s) used to practice the present invention may be produced from any number of suitable materials having reasonable strength in tension, e.g., stainless steels, carbon fibers, engineering plastics, tungsten alloys, variously in the form of a multi-strand cable or single strand thread. Preferably, however, the wire may be made from a “so-called” super-elastic alloy. These alloys are characterized by an ability to transform from an austenitic crystal structure to a stress-induced martensitic (SIM) structure and to return elastically to the austenitic crystal structure (and the original shape) when the stress is removed. A typical alloy is nitinol, a nickel-titanium alloy, which is commercially available and undergoes the austenite-SIM-austenite transformation at a variety of temperature ranges. These materials are described, for instance in U.S. Pat. Nos. 3,174,851 and 3,351,463. These alloys are especially suitable because of their capacity to elastically recover almost completely to the initial configuration once the stress is removed. Since this is so, the size of the actual wire may be made fairly small, e.g., as small as 0.005 inches in diameter or smaller, and the resulting device is able to access very small regions of the body. The wire may also vary in diameter along its length, for example have a larger diameter at the proximal end as compared to the distal end or vice versa.
The wires can have a proximal section and a distal section. The proximal section preferably has a uniform diameter of at least about 0.0001 inch, or about 0.005 to 0.025 inches, preferably 0.0010 to 0.018 inches. Commercially available wires with a material (wire) diameter of 0.008 mm and a loop diameter of 1 mm are available as microcoil materials. Optionally, the distal section that may extend beyond the catheter may have different (more or less) flexibility than the proximal section. Typically, both sections will extend from the distal and proximal ends of the catheter lumen. The wire may have a middle section having a diameter intermediate between the diameter of the two portions of the wire adjoining the middle section or the middle section may be continuously tapered, may have a number of tapered sections or sections of differing diameters, or may be of a uniform diameter along its length and be tapered at or near the distal section. The entire wire may be between about 50 and 300 cm, typically between about 175 to 190 cm in length. The wire may be wrapped to form a coil section or may be independently attached to a coil.
The overall length of the pusher wire, pull wire, and soft coil mesh may extend through a catheter and the wires and catheter inserted into the vasculature. The catheter and wires (with attached soft coil) may extend proximal or distal to the site of the clot or the catheter may be positioned and the wires extend to the site from the catheter. The configurable soft coil component of the device is positioned near the target thrombus site, and the wires position and control the positioning and attitude of the soft coil capture components.
FIG. 5A shows the capture device in a format of providing two distinct macrocoil/microcoil systems 132 and 134, with individual insertion elements 142 and 144. Both macrocoil/microcoil systems 132 and 134 are shown separately deployed and not yet engaged with each other. In a preferred embodiment, each macrocoil/microcoil systems 132 and 134 would also have a pull string or retraction wire (not shown) on the ends of the macrocoil/microcoil systems 132 and 134 most distal from the thrombus 72.
FIG. 5B shows the capture device in a format of providing two distinct macrocoil/microcoil systems 172 and 174 with separate extraction strings 162 and 164 provided through a third catheter 160 or separate retraction strings or pull strings 182 and 184, respectively.
FIG. 6 shows a pneumatic delivery microcatheter delivery system with constrained coils within the catheter. FIG. 6 shows delivery system 202 comprising a catheter 200 having the confined mass of the macrocoil/microcoil material 214 before deployment of the microcoils within the lumen of the catheter. Within the catheter 200 are two sealing elements 218 and 216 that form a pressurable zone 220 within the catheter 200. The forward seal 216 is capable of being moved forward within the catheter 200 by increased pressure within the zone 220. A microcatheter 224 is within the catheter 200 and a lumen 222 within the microcatheter 224 carries fluid pressure and the retraction wire 230 into the pressurable zone 220. When pressure in the zone 222 is sufficient, the forward seal element 216 will press the compressed macrocoil/microcoil mass 214 out of the catheter 200. The seal 216 will be restrained by the retraction wire 230 that also is secured to one end of the contained mesh material 214.
FIG. 7A shows a two-lumen microcatheter 300 providing the macrocoil/microcoil mesh 302 with two separate control wires 304 and 306 acting as the insertion wires. Retraction or pull wires are not shown but are similar to those in FIGS. 1-3. The macrocoil/microcoil mesh 302 is shown deployed beyond the thrombus 72.
FIG. 7B shows a series of steps a) b) c) and d) in which a dual lumen catheter 340 is deploying two microcoil/macrocoil mesh assemblies 350 and 352 to form an engaged single macrocoil mesh 354 with separate end control of the mesh wire in each lumen. The last three steps b) c) and d) represent a single mesh 354 delivered from the two adjacent lumens in a microcatheter 340, progressively encircling the thrombus 72. Two separate control ends 358 and 360 for controlling the composite mesh 354 are shown.
Alternative processes and constructions could provide a soft coil capture device (macrocoil/microcoil mesh) which may be of larger or smaller dimensions than typical intravascular devices. With small coils, but particularly with larger coils, greater strength may be built into the elastic memory of the material, and the length of the remembered coil distribution within the macrocoil element may be increased or decreased. The coil material may be delivered through a catheter or microcatheter, with the elongation of the coils controlled by relative positioning of the push (insertion) and pull (retraction) wires as explained above. One end of the coil material may be secured to the push (insertion) wire, and the distal (leading end) of the coil material may be secured to the distal end of the pull (retraction) wire. When in a fully deployed state, without tension applied by the wires, a natural distribution (frequency) of the macrocoils may exist, but this is not a true memory shape. It is only the random structure of the macrocoils and microcoils. Points of contact between the macrocoils and the pull wire are preferably not secured; rather, the macrocoils are able to slide freely. If the contact points were secured, the frequency between the coils would not be fixed after deployment, since the pull wire is able to telescope or otherwise extend the distribution of the macrocoils within the mesh. The macrocoils, when in a region for deployment, without a restraining action through the connection at the distal connecting point, may have a greater frequency (less spacing) between the macrocoils. The microcoils and macrocoils may be manufactured and designed so as to provide natural dimensions when tension is released after deployment to fit a range of dimensions in the vasculature. The selection of the microcoil size, microcoil spacing, wire thickness, wire material, macrocoil size, and macrocoil spacing are used to determine the frequency, size and shape of the deployed structure.
Although the examples show specific dimensions and materials, the examples and descriptions are not intended to be limiting to the scope of practice and protection of the technology described. Rather, any specific statements or values are intended to be examples within the generic concepts of the inventions and the disclosure taught and provided herein.
Experimentation with the Thrombus Removal System has been conducted in order to remove both soft and very firm clot from the arterial lumens of multiple arteries (renal, subclavian, common and internal carotid arteries) in the pig model. Soft clot was only a few hours old. Hard clot was made by allowing a pig's blood to stand for four days. The firm, fibrin-containing portion separated from the plasma, and the hard clot embolized into the selected artery of a second pig.
Both complex three-dimensional and less complex two-dimensional platinum coils were used in these experiments, including coil structures that were not designed for use in thrombectomy procedures, but rather being the commercially available types used to fill cerebral aneurysms. These coils have a variable cross-sectional diameter and length, and are attached to a stainless steel pusher wire. A commercially available microcatheter with an inner lumen of 0.018 inch was passed beyond the thrombus, particularly between the intima and the thrombus (non-occluded space between the thrombus and the walls) in the case of a firm thrombus, with the aid of a commercially available 0.014 inch microguidewire. A thin nylon line (0.006 inch) was attached to the distal end of a coil, and the coil/string complex gently passed into a microcatheter, to a point distal to the thrombus. Alternatively, the coil/string complex was preloaded into the microcatheter that was passed without the aid of a microguidewire past the distal end of the thrombus. The coils were pushed from the microcatheter, which was progressively pulled back until it was proximal to the thrombus and clot extraction attempted, as previously described.
Soft clot tended to be removed easily from the arteries studied because the clot adhered to the meshwork of the coil and the pulling wire. However, initial experiments with single coils of different sizes, including both 3-D and 2-D coils, demonstrated the inability to consistently and successfully extract the firm clot with this method, even when the coil had formed a mesh around the thrombus and the nylon string was pulled as much as possible to tighten the mesh around the clot. Rather, the coil sometimes simply unraveled from around the thrombus, sliding back into the more proximal microcatheter. It was apparent that in those failed circumstances the loops of the coil were simply wrapping around the clot without becoming tightly engaged, and that such a non-structured mesh was insufficient to overcome the combination of forces keeping the thrombus in place, including friction between the thrombus and the intima and blood flow pushing the embolus distally. However, intertwining and/or overlapping of the loops along the distal aspect of the thrombus, as one would tie a shoelace, kept the distal mesh in place without allowing the entire coil complex to unravel.
In subsequent experiments, two microcatheters were passed distal to the firm clot, each positioned in the same manner as previously described. The distal end of a 3-D coil was pushed into the arterial lumen from the first microcatheter, then the distal end of a second coil, either a 2-D or a 3-D configuration, was pushed forward from the second microcatheter, allowing loops of the two coils to intertwine. By “two coils” in this description, it is meant that there are two masses of coils, one each delivered from a microcatheter, although the term includes two coil masses emanating from two lumens of a single microcatheter, as opposed to requiring two completely distinct microcatheters. Further coils were extended to make a complex, random mesh, then the nylon strings were pulled so that a tight “cap” or “knot” was formed on the distal surface of the clot. The microcatheters were partially withdrawn and as more coils were pushed from the microcatheter, they passively encircled the middle portions of the clot. The process was continued, with more coils (at least a total of two and up to six coils would be used in a preferred range of mesh applications) placed proximal to the clot. The nylon strings was then pulled tightly to form a tight meshwork encircling the entire clot so that little or no fragmentation would occur.
Using this technique, it was possible to successfully extract firm clots from all arteries embolized without evidence of fragmentation on subsequent post-extraction angiography. Coils having diameters equal to or slightly larger than that of the arterial lumen appeared to make the best distal meshwork and, therefore, the most stable macrocoil constructs. By then passively encircling the clot, there was no tendency for the distal “cap” to simply slide from the top over the side of the clot. Post-extraction angiography and post-mortem examination, including microscopy, did not demonstrate any evidence of arterial injury. This was the expected result, given the extensive experience of using these soft platinum coils within the vascular system without producing vascular dissection or vasospasm.
Another way of generally describing articles and methods according to the practice of the technology originally disclosed herein includes a medical device for removing a thrombus from a blood vessel, comprising: a) two microcatheter lumens, each lumen containing: b) a macrocoil thrombus engaging component having a length with a proximal end and a distal end, the length of the macrocoil comprising microcoils that allow the length of the macrocoil to be extendable; c) a first wire capable of providing force on the distal end of the macrocoil; d) a second wire capable of providing force on the proximal end of the macrocoil. The device may have at least two lumens on distinct microcatheters, and the at least two lumens may be attached to a single catheter. A method may be practiced for using the device wherein for at least one macrocoil thrombus engaging coil, a microguidewire is passed through at least one of the lumens to help place the microcatheter distal to the thrombus; the microguidewire is removed; a macrocoil pull-string system comprising push-pull capability is passed through the at least one of the lumens; the macrocoil pull-string system is passed distal to the clot; the pull-string system is used to form an at least partially enclosing distal meshwork on the distal surface of the thrombus, passively encircling mesh around the clot; the pull string is pulled to tighten the meshwork; the macrocoils may have internal structures including loops and other random attachments to facilitate the formation of a tight meshwork; and at least a portion of the device is progressively withdrawn so that the meshwork becomes more tightly engaged with the clot. The method of using the device may be practiced wherein the at least one set of microcoils of at least one macrocoil exhibits a conformation memory of an amorphous shape with overlapping structure resisting complete elongation when ends of the at least one macrocoil are stressed. The conformation memory may form at least one structure selected from the group consisting of knots, loops, multiple crossovers, kinks and snags to reduce excessive slipping of macrocoils, which slipping would allow liner extension of macrocoil material. The method may have the at least one structure assist in forming a network comprising the at least one macrocoil engaging a distal surface of the thrombus. The method may be practiced so that the at least one macrocoil encircles or conforms to the surface of the distal side of the thrombus as the at least one macrocoil is extended from the microcatheter. The method may use a pull-string to tighten the at least one macrocoil against the distal side of the thrombus.
A dual lumen catheter or two separate catheters may deploy a single macrocoil mesh with controls on both ends, or two separate meshes, each with one or two separate end controls of the macrocoil mesh in each lumen. Examples of the end control elements are a pull wire or push pull wire attached to either end of the macrocoil mesh. A thrombus usually has a potential space between the thrombus and the wall of the vessel, allowing the soft macrocoil mesh to passively slid between the surface of the thrombus and the vessel wall. It is to be noted that the deployed macrocoil mesh has no clearly defined shape (such as a basket, box, pyramidal coil complex, or the like) so that the macrocoil mesh may conform to any surface, such as that of the thrombus, as it passively surrounds that surface. Proximal ends of the controlling wires or strings may be used to control the location, deployment, tension, withdrawal and other movement of the macrocoil mesh by appropriately pushing, pulling, twisting, orienting, reorienting, positioning or otherwise moving those proximal ends. Passively encircling the clot reduces the chance of unwanted fragmentation of the thrombus and subsequent embolization of the fragment to vital tissues.
Where there is the deployment of two separate microcatheters, each with a separate macrocoil mesh element, each macrocoil mesh element may have separate end controls extending from each microcatheter, respectfully. Two mesh elements may integrate into a mass on the distal side of a thrombus. Push-pull guidance wire combinations are provided for the respective pairs of macrocoil elements.
In the use of a dual lumen catheter system deploying two macrocoil meshes with separate end controls for each mesh coming out of each lumen of the microcatheter, the distal ends of the mesh, the end controls may operate as push-pull wires, guidance wires, orientation elements, positioning elements, current carrying conductors (as when heating the microcoils in the macrocoil mesh) and the like. The end controls may be the same or different in the construction of the device to assure their ability to perform the ultimately desired tasks. Both end controls aid in the formation of a knot or tight tangle of the distal ends of each macrocoil mesh over the distal aspect of the thrombus, in the passive encirclement of the mid and proximal portions of the thrombus, and in the tightening of the meshwork around the surface of the thrombus.
It is to be noted that the dashed lines for catheters shown behind thrombus in some of the illustrations are not intended to limit the images to catheters passing through the thrombus, and in fact as clearly described herein, the location of the catheters is preferably adjacent to a thrombus. In this regard, it is one of the many novel aspects of the present technology that may be practiced according to these teachings that the catheters are intentionally passed adjacent to and not through a thrombus. It is also novel to pass multiple catheters adjacent to a thrombus in a single medical procedure according to the technology described herein
There are numerous considerations of materials and properties that can be discussed herein to provide general and specific assistance to the design of instruments for various locations and procedures. The composition of the microcoils forming the macrocoil mesh may be any material that will retain its structural integrity during the expected length of an extended procedure, with safeguards built in for overextended periods of the coils being within an environment that may deteriorate or dissolve them. For example, if a standard procedure were expected to take 1-2 hours, it would be appropriate if the coils would remain intact in the operational environment for at least 24 hours and retain their physical properties. The microcoil material can be allowed to breakup or even dissolve after that time, in the event that there is a problem during the procedure, such as if a coil breaks or separates from the mesh.
Typically, the microcoil material will have essentially unaffected properties during the operation. Useful materials may be metals, alloys, plastics (polymeric materials), composites, ceramics and the like. The properties of the microcoil material are intended to provide the macrocoil mesh with resilient properties through the extensibility of the microcoils and macrocoils, and not necessarily elasticity in the material of the wire forming the various coils. The material of the wire may in fact be clearly inelastic within standards for metal wire, plastic wire, ceramic wire and composite wire, for example, having less than 20% or 10% elongation at breaking point for the wire.
Deployment of the at least one wire (with macrocoil mesh therein) may be from a single lumen on a catheter, multiple lumens on a single catheter, single lumens on multiple catheters, multiple lumens on multiple catheters, and 1, 2, 3, 4, 5 6 or more catheters or microcatheters may be used in the process.
The multiple coils may remain separate and distinct when deployed, may incidentally overlap, may intentionally overlap, may tangle with each other, may grip each other or otherwise interact. For example, when the distal ends of the macrocoils are extended from the microcatheter lumens (one microcatheter with two lumens or two separate microcatheters with one lumen each), they will overlap to produce a knot, tangle, or other firm connection. In addition, one or more of loops (the macrocoil loops) may engage each other to form a loose, incidental lock or slip resistant engagement between one or more macrocoils. Design may be built into the macrocoils, such as spikes (less preferred because of potential wall irritation), hooks and loops, posts, and hooks alone to produce a tighter mesh network and to decrease the likelihood of coil loops being extended to relatively ineffectual linearity when one end control is firmly pulled in attempting to position the mesh against the surface of a thrombus.
There are many other variants that may be provided in the practice of the present technology. Among the variations to be considered is the use of actual knot-tying techniques using multiple macrocoil/microcoil structures according to the present descriptions.
In the knot-tying format, two distinct macrocoils are fed from a single lumen, at least two separate lumens, or at least two adjacent lumens, such that a first macrocoil forms a loop with an opening large enough for a straight segment of a second macrocoil to pass through the opening, then passing at least one second macrocoil through the opening, and adjusting the local relative positions of the now at least two macrocoils so that a knot-like arrangement of the coils occurs. The interaction and engagement of the individual macrocoils of the at least two macrocoils also acts to provide a supporting structure and capability to the system.
This feature is more than superficially beneficial. When prior art capture systems are analyzed, they are found to be essentially one-size-fits-all, with only minimum variability in the size of the capture device allowed because of the more defined structure of the capture portion, as can be noted in Rosenbluth (U.S. Pat. No. 6,511,492), where a variety of cage and net structures are provided. Especially with the cage structures, the likelihood of a thrombus being disrupted during insertion and retraction is very high, especially with the more rigid elemental constructions in the pyramidal coil and cage structures. The relatively fixed size of the capture portion means that the system will use a single size for a large thrombus or a small thrombus. The potential for damage or inoperability varies among the range of size of the potential thrombus, and might require an attempt to provide distinct capture systems with advanced knowledge (which may be erroneous) of the specific size and shape of the thrombus. The present technology, because of the flexibility and conformability of the macrocoil/microcoil structure, can be used on an extremely wide variation in size of thrombi, and the coils will themselves conform to the size of whatever thrombus is present. The pull strings aid in altering the position of the distal tip of one or more macrocoils, so that the formation of the knot is facilitated. The pull string also tightens the mesh work distal to the thrombus. Finally, after macrocoils are passively looped around the mid and proximal aspects of the clot, the pull string aids in tightening the entire construct to decrease the chance of clot fragmentation.
Additionally, as noted elsewhere, the conformability of the macrocoil system of the described technology offers the potential for reduced disruption of a thrombus and the generation of floating clots that could cause a stroke. Although there is never a guarantee of avoiding such issues during medical procedures, at least the potential is there for reducing the likelihood of such potentially disastrous events.
Other variations in the materials, designs and processes may be apparent and obvious to those skilled in the art from the generic teaching and examples provided herein.

## Claims

1. A medical device for removing a thrombus from a blood vessel, comprising a single catheter containing:
a macrocoil thrombus engaging component having a length with a proximal end and a distal end, the length of the macrocoil comprised of microcoils that allow the length of the macrocoil to be extendable and flexible;
a first wire capable of providing force on an end of the macrocoil; within the catheter are two sealing elements, a first forward-sealing element and a second rearward-sealing element that form a pressurable zone within the catheter;
the first wire is a retraction wire for the first forward-sealing element;
wherein upon removal from the catheter by force on at least the first forward-sealing element, the macrocoil expands and retains microcoils along a length of the macrocoil.

2. The medical device of claim 1 wherein when the first forward-sealing element and a portion of the microcoils are extending from, but adjacent to, the catheter, the macrocoil is in a naturally expanded condition.

3. The medical device of claim 2 wherein the medical device is configured to be present within the blood vessel having a thrombus therein, and the distal end of the macrocoil thrombus engaging component is configured to extend past the thrombus.