FIELD OF THE INVENTION

[000.1] The present invention relates to apparatus and -methods tor providing embolk protection in a patient's vascular system. In particular. It relates to an embolic protection device that c n be deployed in a patient ^' s aorta to protect the aortic arch vessels and downstream organs from potential emboli. The embolk- protection device can be used acutely, for example for embolic -protection during cardiac surgery and interventional cardiology procedures, or It can be implanted for chronic embolic protection, for example from cardiogenic emboli or emboli from ruptured or vulnerable aortic plaque. ftKM)2f Cerebral embolism Is a known complication of cardiac surgery, cardiopulmonary bypass and catheter-based interventional cardiology and eiectrophyslology procedures such as, but not limited to, transcatheter aortic valve .replacement implantation TAVR/f AYL Embolic particles, which may include thrombus, atheroma and lipids, may become dislodged by surgical or catheter manipulations and enter the bloodstream, embol ng in the brain or other vital organs downstream. Other sources of potential emboli include cardiogenic emboli, such as thrombus that results from chronic atrial fibrillation, and emboli from ruptured or vulnerable aortic plaque. Cerebral embolism can lead to neuropsychological deficits, stroke and even death.. Other organs d wns ream can also be damaged by embolism, resulting In diminished function or organ failure.. Prevention of embolism formation by capture or collection of antegrade-fiowing embolic debris benefits patients and substantially improves the outcome of the various procedures with which it Is used.

[0003] O ven that the sources of potential emboli can be acute or chronic, It would be advantageous to provide an embolic protection, device that can either be used acutely, for example for embolic protection during cardiac surgery and interventional cardiology procedures, or that can be implanted for chronic embolic protection, for example from cardiogenic emboli or emboli from ruptured or vulnerable aortic plaque, A further advantage would be realized by providing an embolic protection device that can be implanted without interfering with transiumiaal aortic access for performing future surgeries and other interventional or diagnostic procedures. Another advantage would come from providing an embolic protection device that can be retrieved and removed from the patient after the necessity for it has pass d. Yet another advantage would come from providing m embolic protection device that can be deployed and retrieved using minimally Invasive techniques. 0004| The embolic protection device of this application is char cteri ed as being "High Flow," By this it is meant, that the device of this application is particularly adapted to capture emboli in vascular or aortic locations where larger blood volumes; or higher blood pressure or both is found. For example, a preferred location for deployment of this protection device within or adjacent to the aortic arch. In such high flow locations this device can filter emboli from large volumes of blood with minimal creation of hack flow or back pressure. Back pressure or back flow gradients as are sometime- created b embol protection devices are generally to be avoided so as not to cause the heart to work harder to produce the required cardiac output 0ft05] Previous devices for preventing cerebral embolism are described in the following patents and patent applications, which are hereby incorporated by reference: U.S. Pat App. 2004021.516? Embolic Protection Device, PCX App. WO/2004/01 817 Embolic Protection Device, U.S. Pat No. 6,371,935 Aortic Catheter with Flow Divider and Methods for Preventing Cerebral Embolization, U.S. Pat No. 6361,545 Perfusion Filter Catheter, U.S. Pat No. 6,254,563 Perfusion Shunt Apparatus and Method, U.S. Pat No. 6,139,517 Perfusion Shunt Apparatus and Method, U.S. Pat. No. 6,537*29? Methods of Protecting a Patient from Embolization during Surgery, U.S. Pat No. 6,499,487 Implantable Cerebral Protection Device and Methods of Use, U.S. Pat. No. 5,769,81 Cannula with Associated Filter. U.S. Pat, App. 20030100940 implantable Intraluminal Protector Device and Method of Using Same for Stabilizing Atheromas.

BRIEF DESCRIPTION OF THE DRAWINGS

|#i06J It is to he understood that the drawings and the description below are provided primarily for purposes of facilitating understanding the conceptual aspects of the invention and various possible embodiments thereof including wha is presently consi ered to be preferred embodiments, it is to be further understood that the embodiments described are for purposes of example only, and that the invention is capable of being embodied In other forms and applications than described herein as will be suggested to one skilled in this art in view of the present disclosure, figures, and claims.

100071 FIG. I shows basic coronary anatomy discussed with respect to this invention. (OOOSJ FIG. shows m embolic protection device of this invention in its Implanted, ex anded condition.

[0009f FIG. 3 shows the embolic protection device of FIG. 2 in an undepkwed or retracted condition.

fOOlOf FIG. 4 s ows an embolic protection device in an. undeployed condition being inserted into a patient's aortic arch,

(00111 FIG. 5 shows an embolic protection device in a retracted condition for .removal from the patient's aorta.

1 _. 00121 FIG, 6 shows schematically an embodiment of the present embolic protection device 1 0 partially deployed into the left subclavian artery 300.

10013 _. 1 FIG. 7 shows the embodiment of FIG. 6 in which a TAVR catheter 302 accesses the aortic valve through the present embolic device,

|βί 1 ί| FIG. 8 shows deployment of a device of this invention 100' into the descending aorta. The arrows 208 show possible directions of blood flow after emboli have been captured or filtered therefrom by the present device.

(00151 FIG. 9 shows the location in the descending aorta where emboli would be captured by the device shown in FIG. 8.

1001.6 _. 1 FIG. J 0 illustrates withdrawal of device of this invention containing captured emboli using a large lumen catheter.

(O017| FIG. 11 shows the device of FK5. 10 with attachment points asserting embolic protection device withdrawal.

(00181 FIG. 12 shows capture of the emboli-contalniag device by withdrawal of same into the catheter. [8819] FIG. 13 illustrates a recapture hook 202 which can be used to assist device retrieval and withdrawal.

$820J FIG. 14 illustrates and describes a further approach to embolic protection device ^' Withdrawal.

[88211 FIG, 15 is a detailed depiction of emboli being captured by an embolic protection device of fee invention along the -wall of the aorta,

[8922] FIG, 16 shows an embodiment of the invention in which a porous membrane of polymer sieve or membrane 204 is deployed within, upon or outside the embolic protection device to capture emboli.

| 23| FIG. 17 A shows a detailed schematic sectioned representation of emboli capture using a triaxiai protection device of Ibis invention.

[8824| FIGS, ί 78 and 1?C show a side and perspective view of the triaxiai braided mesh embodiment of this embolic protection device >

18825! FIGS, 1?D and 17E show partially assembled exploded views of the device shown in FIGS. 1?A through !?€..

|98261 FIGS. 18a and ISb are side and end view, respectively, illustrating one form of intraluminal device constructed in accordance wife the present invention, he device being shown in its implanted _* expanded condition.

188271 FIGS. !9a and 19b are corresponding views but illustrating the devic in its contracted;, stressed condition,

[88281 FIG. 20 more particularly illustrates the braid pattern of FIGS, 1.8a, 18b and 1 a. 1 b in the expanded condition of the braided tube,

[8829] FIG. 21 illustrates another braid pattern, wherein one filament extending In one helical directio is Interwoven over and under two filaments extending in the opposite helical direction,

[8838) FIG, 22 illustrates a further braid pattern in which two (o more) contiguous filaments extending helically In one direction are interwoven over and under two (or more) contiguous filaments extending m fee opposite direction,

[883.1] FIG. 23 schematically shows the relationship between the bending rigidity of the braided tube with respect to the diameter of the filaments producing the braided tube. BRIEF SUMMARY OF THE INVENTION

£8832} The present invention, la one aspec provides a high-flow intehrmlna! embolic protection device implantable in a blood vessel, the device comprising: a braided mesh-like tube of bio~compati sle material having an expanded condition in which the tube diameter is larger than the diameter of the blood vessel in which it is to be implanted, the braided mesh- like tube having a length sufficient to be anchored to the source blood vessel, the braided mesh-Hke tube being dimensioned and configured t have in its implanted condition a porosity index such as to filter or capture asitegrade-flo ing emboli but not to unduly reduce the blood flow,

DETAILED DESCRIPTION OF THE INVENTION

£8833| FIG. I shows schematically basic aortic anatomy relevant to one aspect of this invention I.e., when the present embolic protection device or filter Is employed in conjunction with a TA I or TAVR procedure. It Is to be understood that the present invention can be deployed before, during, or after a transeatheier procedure in which emboli may be generated. Oxygenated blood flows from the heart, to the ascending aorta, to the arch of aorta to the right and left subclavian arteries, the right and left carotid arteries, and to tie descending aorta. FIG. I is used schenmtkaliy, generally in section, to illustrate the features of this invention in several of the FIGs which fellow,

|0Θ34| FIG. 2 shows an embolic protection device 100 according to the present Invention in an expanded or deployed condition. It will he recognised that device 182 Is deployed within the aortic arch. The embolic protection device 180 has an approximately cylindrical outer structure 182 made of a braided mesh-like material Device 108 has an upstream end 1(18 and downstream end 118. The upstream end 188 of the embolic- protection device 100 is open, for blood to .flow as Indicated by the arrow in FIG. 2. The braided mesh-like material (sometimes referred to as ' ilter mesh material ^* *) of the cylindrical outer structure 182 may be made of knitted, woven or non woven fibers, filaments or wires and will have a pore size chosen to prevent emboli above a certain size from passing through. The filter mesh material may be made of a metal, a polymer or a combination thereof and may optionally have an antithrombogeMe coating on its surface. The filter mesh material o the cylindrical outer structure 102 ma have a pore size m the range o ^' approximately 1 mm to 0.1 mm or even smaller, depending on whether it. is intended to capture acroembolt only or mkroemboh as well. Alternatively, the filter mmh material of the cylindrical outer structure 102 may have a pore siz to stop microemholi as small as 0,1 mm, f0$35j BCL 3 shows the embolic protection device 100 of FIG. 1 in an undeployed or retracted condition. Typically, delivery catheter 124 will be used, the delivery catheter 124 constructed with as internal lumen .125 that terminates in a guidewire port 126 at the distal end of the catheter 124, Optionally, a tubular outer delivery sheath 130 shown in dashed line may fee used to maintain the embolic protection device 100 in the undeployed condition. The delivery catheter 124 may optionally include a shoulder or other retention structure 128 positioned proximal to the embolic protection device 100 to maintain the position of the embolic protection device 100 on the delivery catheter 124 as the delivery sheath .130 is withdrawn during deployment Alternatively, a pusher catheter (not shown) thai Its in between the delivery catheter 124 and the delivery sheath 130 may he ^' used to facilitate deployment.

[ 0361 Optionally, when the embolic protection device 10 is Intended to he used for embolic protection during a catheter-based diagnostic or interventional procedure, the deliver}- catheter 124 may be configured as a diagnostic catheter, guiding catheter, or therapeutic catheter,

|0037| The embolic protection device 100 will preferably he self-supporting in the deployed condition. This can fee accomplished with a variety of different constructions. In one example, the cylindrical outer structure 102 can be constructed with a resilient filter mesh .material that can be compressed into the undeployed condition and wil self-expand into the deployed condition. The filter mesh can be resilient flaccid or plastically defcrmabie.

100381 Hybrid constructions that combine features of the self-suppoifing structure and the frame-supported stmcture. Hybrid deployment methods, such as balloon-assisted self- expansion can also be utilized. Optionally, the embolic protection device 100 may include features to assist in retracting the device tor retrieval from the patient's aorta {See, Fig, 5 discussion below). For example _* the upstream end 108 and the downstream end 110 of the e bolic protection device 100 -may be constructed with ^' -retraction members 11.6, 120 mat are configured like purse strings or lassos around the circumference of the cylindrical outer structure 102. A pull loop 322 or other gsraspabie structure near the downstream end 110 of the embolic protection device 100 is connected to the retraction .members 1.16, 1 0 b one or more connecting members 113. Optionally, two separate pull loops 122- may be provided for selectively retracting the upstream and downstream retraction members 1 6, 120. High strength magnets could be substituted for pull loops 122 (not show) their opposite polarities being used to couple the device and a reduction apparatus or -retraction member J 16, 1.20, The retraction members 116, 120 and connecting members 113 may be made of suture, wire, plastic filament or a combination of these materials, in an alternate construction, the support hoops 112, 114 described above .may also be configured to serve as the retraction members 116, 120, f 03fj FIG. 4 shorn an embolic protection device 100 m an nndeployed condition mounted on a delivery catheter 126 being inserted over a guidewire 142 into a patient's aortic arch. Optionally, a delivery sheath 130 may be used to hold the embolic protection device 100 in the undep!oyed position. Once the embolic protection device 100 is at the desired location, the embolic protection device 100 is deployed, for example b withdrawing tire deli very sheath 130 and allowing the embolic protection device 100 to expand. If the delivery catheter 126 is in the form of a diagnostic or therapentie catheter, the catheter 126 can. be advanced after the embolic protection device 100 is deployed to perform a diagnostic or Interventional procedure. Optionally, the embolic protection device 1.00 can be retracted and withdrawn with the delivery catheter 126 after the diagnostic or interventional procedure has been completed. Alternatively, the delivery catheter 126 can be withdrawn, leaving the embolic protection device 100 in place.

[0040] FIG. 5 shows an embolic protection device 100 in a -retracted condition for removal from the patient's aorta. A retrieval catheter 152 has been inserted intralaminaliy over a guidewire 146 to the location of the embolic protection device 100. Optionally, the guidewire 146 and retrieval catheter 1.52 may be inserted into the conical inner structure 104 and/or thro h t e catheter port 106. A hook 154 on the distal end of an elongated member 156 ^" within the retrieval catheter 152 has engaged the pull loop 122 on the embolic protection device 100. The hook 154 may engage the pall loop 122 through a distal port or a side port 1S# on the retrieval catheter 152. The hook 154 and the poll loo 122 are withdrawn into the retrieval catheter tS2, pulling oa the connecting member 11$ and causing the retraction members 116. 120 to tighten and collapse the embolic protection device 100 to a smaller diameter with the embolic debris 144 trapped inside the retracted embolic protectio device 1Θ0.

|0 411 The tatinilated embolic protection device 100 may be delivered into t!te patient's aorta on a guidewire or deliver catheter and/or inside of a delivery sheath. Once, the embolic protection device 100 is in the proper position w thin the aortic arch, the inflatable support framework 160 is inflated through the inflation tube 170, At least the distal inflatable toroidal balloon 164, and optionally the proximal inflatable toroidal balloon 1 2, makes a seal with the aortic wall when inflated so that blood flow will be directed int the collectio chamber 103 and through the filter mesh material to capture any potential emboli, if the embolic protection device 100 is intended for shor term use, the proximal end of the inflation tube 170 may be left exposed a the insertion site. Alternatively, if the embolic protection device 100 is intended for long term ¾se _» the Inflation tube 170 may be detached from the inflated embolic protection device 100. As another alternative, the proximal end of the inflation tribe 170 may be buried under the patient's skin to allow later access for deflating and withdrawing the embolic protection device 100. 0042j When the embolic protection device 100 is no longer needed _* the inflatable support framework 160 is deflated and the embolic protection device 100 is withdrawn from the patient. Preferably, the embolic protection device 100 is configured such that the distal toroidal balloon 164 on the upstream end ^' of ^' the collection chamber 103 deflates first t effectively capture any potential - emboli inside of the collection chamber 103. Other echartisms described herein may also be used to assist i» retracting the embolic protection device 100. f0043J Other mechanisms may b employed for deploying and/or retrieving the embolic protection device 108. For ex mple, the embolic protection device 100 c n be elongated in the longitudinal direction to cause it contract radially. Releasing the tension on the embolic protection device 100 allows it to contract in the longitudinal direction and to expand radially for deployment A retrieval catheter can be configured to apply longitudinal tension to the embolic protection device 100 to collapse it radially for withdrawal from the patient. Alternatively or in addition, the -embolic protection device I©0 can be twisted or wrapped to cause it contract radially. Releasing the embolic protectio device 180 allows it to untwisted or unwrapped and to expand radially for deployment. A retrieval catheter can be configured to apply torque to the embolic protection device 100 to twist or wrap it to collapse it radially for withdrawal from the patient, ^' these mechanisms may also be used in combination with the methods described above, such as those using retraction members or an inflatable support framework, to deploy and/or retrieve the embolic protection device 100. & 4\ Alternate embodiments of the embolic protection device 100 may combine features of the embodiments described herein to accomplish the same ends. For example, an embolic protection device 100 may be constructed wish a single hoop 112 or inflatable toroidal balloon 164 on the upstream end of cylindrical or conical outer structure 102 in contact with the vessel wall to anchor the device. The downstream end of the outer structure 102 ma be constructed without a hoop or toroidal balloon, or alternatively with a smaller diameter hoop or toroidal balloon, as it is not critical for the downstream end of the embolic protection device 100 to contact or make a seal with the vessel wail. The embolic protection device of the present invention can also be used for embolic protection of other organ systems. For example, an embolic protection device can be deployed m the patient's descending aorta for preventing embolic particles in the aortic blood flow from entering the renal arteries and emboiizing in the patient's kidneys,

|004S| The present invention, in one aspect, provides high-flow intralnminal embolic protection device implantable in a blood vessel, the device comprising: a braided mesh-like tube of Mo-compatible material having m expanded condition in whic the tube diameter is lar er than the diameter of the Mood vessel in wMch it is to be implanted, the braided meshlike tube tmvmg length sufficien to be anchored to the source blood vessel, the braided mesh-like tube being dimensioned and configured to have in its implanted condition a porosity index such as to filter or capture antegrade~flowing emboli but not to unduly reduce the blood How. The foregoing advantageous .results have been found attainable when the braided mesh-like tube s designed to have, in lis expanded condition, a porosity index of 55 to80¾, preferably 60-75%; windows or openings having an inscribed diameter of 30-480 microns, preferably 50-320 microns; and/or a diameter of wire filaments of 10-40 microns, preferably 20-40 microns; but when the filaments are of rectangular cross-section, circumference 40-200 microns.

{1)0 61 ft* the described preferred embodiments, the windows in the mesh-like tube produce a porosity index of preferably 60%-75%, The porosit index (P.L) is defined by the relation:

P.I. ^™ 1 - JSjsj wherein: "Sm" is the actual surface covered by the mesh-like -tube , and "S _t " is the total surface area of the mesh-like tube. In the tube devices of the present invention, however, the porosity index is not more than 80%, preferably 55-80%, more preferably 60-75%.

{0047J In the described preferred embodiments, the mesh-like tube includes windows having an inscribed diameter of 30- 80μη preferably 5 »320um, in the implanted condition of the mesh-like tube, j M8| According to the described preferred embodiments, the mesh-like tube includes a plurality of filaments of bio-eompatiblc material extending helically in an interlaced manner in opposite directions so as to form a braided tube, it is contemplated, however, that other mesh-like strictures could be used, such as woven or knitted tubes,

10049] A maximum porosity index is attained when the braiding angle, in the implanted condition of the braided tube, is 90*. Decreasing the implanted braiding angle below 90° increases the radial force applied by the braided tube against the inner surface of the blood vessel and decreases the P.I. Increasing the implanted braiding angle above 0" decreases the radial force applied by the braided tribe agai nst the inner surface of the blood vessel and decreases the Pi, In cases, where low radial force is needed, th desirable P.L can thus be achieved by Increasing the implanted braiding angle, as described below with respect to specific examples. Preferably, the braided tube has a braiding angle k the range of 20%- 150% in the implanted condition of the braided tube,

|0050| Also m the described preferred embodiments, the filaments, or at least most of them, are of circular cross-section and have a diameter of 10-50 μη , preferably 20-40 um The filaments could also be of non-circular cross-section, such as of square or rectangular cross-section, in which ease it Is preferred that they have a circumference of 40-200 urn. It is also possible to use combination of several filament diameters and filament materials in one device to achieve structural stability and/or desired radio-opacity characteristic. Preferably the braid is formed of 24-144 filaments, more preferably 62-120 filaments. The filaments may be of a suitable Mo-compatible material, metal or plastic, and may include a drug or other biological coating or cladding,

fOOSl] FIG, 6 shows schematically an embodiment of the present embolic protection device 180 partially deployed into the left subclavian artery 300.

00521 FIG. 7 shows the embodiment of FIG. 6 in which a TAVR catheter 302 accesses the aortic val ve through die present embolic device,

£0053] PIG. 8 shows deployment of device of this invention 100' into the descending aorta. The arrows 200 show possible directions of blood flow after emboli have been captured or filtered therefrom by the present device,

£0 54| FIG. 9 shows the location in the descendin aorta where emboli would be captured by the device shown in FIG, 8.

[9055] FIG, 10 illustrates withdrawal of device of this Invention containing captured emboli using a large lumen catheter.

[0 J56] FIG. 1 1 shows the device of FIG. 10 with attachment points asserting embolic protection device withdrawal. |00S?f FIG. 12 shows capture of the emboli-eontaining device by withdrawal of same Into the c theter.

£0058f FIG. 13 illustrates a recapture hook 202 which can he used to assist device retrieval and withdrawal.

[00S9J FIG, 14 Illustrates and describes a further approach to embolic protection device withdrawal m which a thread is employed as a distally located (from the perspective of the patient) recapture mechanism.

|0060| FIG. 15 Is a detail sectional depiction of emboli being captured by an embolic prelection device of the con vention along the wall of the aorta _*

£00&lf FIG. 16 shows an embodiment of th invention in which a porous mem r e of ^• polymer sieve or membrane W4 is deployed within, upon or outside the embolic protection device to capture emboli.

f 0862 J FIG. 17A shows a detailed schematic sectioned representation of emboli capture using fcriaxial protection device of this invention. In this sectional view, a 3 coaxial 3 layer braided meshvllke embolic protection device is shown. Two (2) layer braided coaxial construction is also contemplated. Using a 3 coaxial 3 layer braided tube construction, the inner-most braided, mesh-like structure has the largest porosity, the middle tube has a smaller porosity and the outer-most braided tube is the least porous. The inner-most structure Sites or traps the largest emboli, the middle coaxial braided tube structure filtering intermediate- sized emboli and the outer-most coaxial braided tube structure filtering the smallest emboli. That construction permits the maximum filtration of emboli from high flow blood stream with minimal creation, of vessel hack pressure or resistance to flow.

FIGS. 178 and 17C show a side and perspective view of this triaxial braided mesh protection device 400, FIGS. I7D and l ?B show partially assembled exploded views of device 400 prior to assembly.

|8064J FIGS. 18a and 18b illustrate a detailed view of an intraluminal device, therein generally designated 2, constructed in accordance with the present invention k its implanted condition which it assumes in a blood vessel after deployment therein. [0065] FIGS, 19a and 19b illustrate the intraluminal device 2 of FIGS. 18a and 18b in the contracted or stressed condition of the device which it assumes to facilitate its manipulation through the blood vessel to the deployment site. 0066] As shown particularly in FIG. 18a. the intraluminal embolic protection device includes a plurality of filaments of elastic or no -elastic bio-compatible material, metal or plastic, extending helically in an interlaced manner to define a braided tube. Thns _t shown in FIG. 18a is a first group of filaments 3 extending helically in one direction, and a second group of filaments 4 extending helically in the opposite direction, with the two groups of filaments being interwoven such that a filament 3 overlies a filament 4 at some points as shown at 5, and underlies a filament 4 at other points as shown at 6,

|tltJ67| Filaments 3 and 4 thus define a braided woven tube having a plurality of windows ?,. The inscribed diameter and the length of each window are shown at W _¾ and W respectively, in the implanted condition of the braided tube. These characteristics depend on, among other factors Including: the number of filaments; Ihe cross section of fee filaments; and the implanted angle "a" at the cross-over points of th two groups of filaments 3, 4, It is understood by those skilled in the art that the above dimensions describe ihe dimensions in the implanted condition of the braided t b . The dimensions In the fully expanded unirnplarited condition will be somewhat different, with the angle "a" and W¾.. typically being larger than, and W _< j typically being smaller m n _* the equivalent respective dimensions in the implanted state,

|0O68| FIG. 20 more particularly illustrates the above-described braid pattern in the fully expanded condition of the braided tube. Thus, as shown in FIG. 20, each filament 3« extending helically in one direction is interwoven with one filament 4a extending helically in the opposite direction. Such a braid pattern is sometimes called a "one over one" pattern _* f 06 ] FIG. 21 illustrates a "one over two" pattern, in which each filament 3h extending helically in one direction is interwoven with two filaments 4b extending helically n the opposite direction, (00701 FIG. 22 illustrates a further r^d pattern that may be used, in which two (or more) contiguous filaments 3c extending helically m one direction are interwoven with two (or more) contiguous filaments 4c extending helically in the opposite direction,

(00711 The braid pattern illustrated, in FIG. 20 is of highest flexibility, whereas that illustrated in FIG, 22 Is of lower flexibility but of higher strength,

[0072] Braided-tube intraluminal devices are used in other systems, for example a described in a!lsten et a1, US. Pat. No. 5,061,275 and Wallsien 0.$» Pal No, 4,954,126, the contents of which are incorporated herein by reference, They are generally used as stents for providing support to a wall of a blood vessel, for implanting a graft, e.g., to treat an aneurysm (FIG, 9 of the latter patent), or for other purposes. In other contexts, the braided tube sometimes is shown to have an expanded, wnkiplanted condition having a diameter slightly larger than the diameter of the intended blood vessel in which it is to be implanted so that when the device is deployed it becomes firmly embedded in the wall of blood vessel. The braided tube is capable of being stressed into a contracted condition, as shown in FIGS. 9a and 19b, wherein the diameter of the braided tube is decreased, and its length increased, to permit manipulation of the braided, tube through the blood vessel to the site of Implantation.

(0073J Further .information concerning the construction and deployment of such hra!ded- tube intraluminal devices is available In the above-cited patents, and also in U.S. patent application Ser. No, 10/311,876, filed on Dec. 20, 2002, entitled "Implantable Braided Stroke Preventing Device and Method of Manufacturing the contents of which are incorporated herein by reference,

|O074| According to the present invention, the constituent element making up the mesh- like tube are of a sufficiently small size in cross-section and define windows of a size such that the mesh-like tube, when in its contracted condition, is sufficiently flexible so as to he easily anipulaiahle through the blood vessel to be implanted in e,g., an artery; and when in its implanted condition anchoring itself to both the source blood vessel/artery and fdtering capturmg emboli flowin therethrough. The skewin is caused by the flow of blood through the wails of the mesh-like tu e, and the amount of skew Is a fimetion of the predetermined implanted porosity index. m an exemplary embodiment, In which the meshlike tube is constituted of braided filaments, the windows defined by the filaments of the braided tube are such as to fitter emboli from the blood, but does not unduly reduce the blood flow to the branch vessels to the degree likely to cause damage to tissues supplied with blood by such vessels. fO075j FIG, 23 schematically illustrates how the bending rigidity or flexibility of a braided tube varies with the diameter of the filaments. Region A in FIG. 23 itmsttates typical diameters in conventional stents used for supporting blood vessels, which region usually starts above 60 π¾ and extends to several hundred um. Region B in FIG. 23 illustrates the region of filament diameters for use in constructin braided tubes in accordance with the present invention. The filament diameters in this region would be significantly sraailer than m region A, preferably being 10-50 um, more preferably 20-40 μηκ f0«?(i| The foregoing dimensions apply to the diameters of filaments of circular cross- section. Where the filaments are of non-circular cross-section, such as of rectangular or square cross-section, the filaments would preferably have a circumference of 40-200 urn. The circumference is defined in macro scale. The circumference can be enlarged at the micro-scale level by addin roughness to the wire, in order to control the neoimimal growth and making the circumference in micro scale longer while keeping the macro scal the same, in this case the surface cross sectio of the filament would be m the ran e ?5~3O0 um ² preferably 300-1300 ^* *.

[O077| As indicated earlier, the windows formed in the braided mesh-like tube would also be preferably within a predetermined range suc as to filter the blood-flow, but ma ntain sufficient blood flow in or to the branch vessels. Preferably the length of the window, i.e., its long dimension as shown at W«, in FIG. 18 , would be within the range of 30-480 um, more preferably 50-320 um, in the implanted condition of the braided tube. Also _* the implanted angle (a, FIG. 18a) would preferably be within the range of ^' 20°- 150 more preferably 40- 80° for high radial force and 100-140° for low radial force, in the implanted condition of the braided tube. I yet another preferred embodiment the braid angle in the implanted condition is approximate!)' 90% preferably in the range of 70°- 110°, The diameter and length of the braided tube its normal, implanted condition will vary according to the location and anatomical dimensions at the particular site of the implantation. Preferably, the windows are preferably globally (but not necessary locally) unifoftn in size, 078| The filaments of the exemplary braided meshrhke tube em odinient can be made of any suitable material which are bio-ecmpatible and which can be worked into a braid. Bio-compatible herein includes any material that can foe safely introduced and implanted in .human or animal bodies for indefinite poods of time without causing any significant physiological damage. Preferably, the filaments are made of a material selected from among the 316L stainless steel, tantalum, and super elastic tinoL cobalt base alloy, polymer or any other suitable metal or metal combination.

J8879J Filaments also can be coated with bio-compatible coatings [Ulrica Sigwari, "Endoluminal Stenting' ¹ . . B. Saunders Company Ltd.. London, 1 96]. It is possible to use a combination of several filament materials in one device and combinations of several materials in one -filament The above embodiments have been described in relation to a braided mesh-like tube, however this is not meant to be limiting in any way. Other mesh~Hke structures, such as woven or knitted tubes exhibiting similar porosity and flexibility can be used without exceeding the scope of the Invention. 0080 in some situations, it may be desired to implant the device in a portion of a lumen, e.g., an artery, varying significantly in diameter along its length. As will he appreciated, if a constant diameter braided tube device is inserted Into such a variable-diameter lumen, this may result in a defective anchoring of the device at the larger diameter portion of the lumen, and in a possible risk of the migration of the device within the lumen. This problem can be easily overcome in several ways, e,g<, by creating braided devices with variable diameters along their longitudinal axis, or varying the pitch along the longitudinal axis, as described in the above-cited U.S. patent application Set. No. 10/311,876 is incorporated herein b reference. fOOSi] United States Patents 8,414,482 to Beison and 7,942,921 to Yodfat et al are specifically incorporated herein in their entireties.

Whiie the present invention has been described herein with respect to the exemplary embodiments and the best mode for piaeticmg the invention, it will be apparent to one of ordinary skill in the art that many modifications, improvements and subcombinations of the vanoas embodiments, adaptations md variations can be made to the invention without departing from the spirit and scope thereof.