US20080167677A1 - Filter element for embolic protection device - Google Patents
Filter element for embolic protection device Download PDFInfo
- Publication number
- US20080167677A1 US20080167677A1 US11/562,720 US56272006A US2008167677A1 US 20080167677 A1 US20080167677 A1 US 20080167677A1 US 56272006 A US56272006 A US 56272006A US 2008167677 A1 US2008167677 A1 US 2008167677A1
- Authority
- US
- United States
- Prior art keywords
- filter
- poly
- coating
- filter body
- blood
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Abandoned
Links
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/01—Filters implantable into blood vessels
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/01—Filters implantable into blood vessels
- A61F2002/018—Filters implantable into blood vessels made from tubes or sheets of material, e.g. by etching or laser-cutting
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2230/00—Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2230/0002—Two-dimensional shapes, e.g. cross-sections
- A61F2230/0004—Rounded shapes, e.g. with rounded corners
- A61F2230/0006—Rounded shapes, e.g. with rounded corners circular
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2230/00—Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2230/0063—Three-dimensional shapes
- A61F2230/0067—Three-dimensional shapes conical
Definitions
- This invention relates to a filter element for a transcatheter embolic protection device.
- the invention is particularly concerned with filter elements for transcatheter embolic protection devices of the type described in our WO-A-9923976.
- One type of such embolic filter essentially comprises a filter body mounted on an associated collapsible support frame which can be collapsed against the guide wire by means of a catheter for deployment of the filter through a patient's vascular system. Upon retraction of the catheter the support frame and filter body expand outwardly from the guidewire across a blood vessel within which the filter is positioned to filter blood flowing through the blood vessel.
- a practical problem that arises with filter elements of such embolic protection devices is that they should be able to accommodate blood vessels of different diameter as it would be impractical to manufacture a large range of filters each of different size to accommodate all possible diameters of blood vessel.
- a relatively soft and elastic filter body material can be used. It is, however, important that the filter when deployed maintains its shape during use and to prevent distortion or collapsing of the filter body in use. Because of this and also the need for adequate strength in the body material, the walls of the filter body tend to be relatively thick. This presents a problem in that the filter then has a relatively large crossing profile when in the collapsed deployment position, which is undesirable.
- the present invention is directed towards overcoming these and other problems.
- a collapsible filter element for a transcatheter embolic protection device comprising:
- the thickness of the coating is from 4% to 30% of the thickness of the membrane, ideally the thickness of the coating is approximately 20% of the thickness of the membrane.
- the membrane may be of a material selected from one or more of polyether block amide (PEBAX), polyester, polyethylene, polyurethane, terephthalate, nylon or, as appropriate copolymers thereof.
- PEBAX polyether block amide
- polyester polyethylene
- polyurethane polyurethane
- terephthalate nylon
- nylon as appropriate copolymers thereof.
- the coating is at least partially of a material selected from a non thrombogenic material and a fluoropolymer material.
- the coating is most preferably of a hydrophilic material.
- the coating is of a hydrogel material.
- the coating includes a physiologically acceptable additive.
- the additive may be a therapeutic additive.
- the additive is preferably an antithrombogenic additive such as heparin.
- the filter body is surface treated prior to application of the coating.
- the filter body comprises a proximal body section, a distal body section and an intermediate body section interconnecting the proximal and distal body sections, one or more of the body sections being of laminate construction.
- the body sections may be of the same laminate construction. At least two of the body sections may be of different laminate construction.
- the filter body has regions of varying hardness or stiffness.
- the filter body has a durometer of between 60 D and 70 A Shore hardness.
- the filter body has a first relatively stiff portion and a second relatively soft portion.
- One portion or section of the filter body may have a larger wall thickness than the wall thickness of another section or portion.
- the filter body may comprise a proximal body section and a distal body section, one of which forms a stiff first portion and the other of which forms a soft second portion.
- a proximal body section forms the soft second portion.
- the filter body comprises a proximal body section and a distal body section interconnected by an intermediate body section, one or both of the proximal body section and the intermediate body section forming the soft second portion, the distal body section forming the stiff first portion.
- the proximal body section has a ribbed outer surface.
- a plurality of spaced-apart longitudinal ribs may be provided on the proximal section.
- the proximal body section includes corrugations.
- the filter body has expansion means to facilitate retrieval of the captured embolic material.
- At least the distal portion of the filter body is of a membrane material that is stretchable.
- Preferably at least the membrane is stretchable in the longitudinal direction to facilitate retrieval from the vasculature.
- the filter body includes an intermediate portion extending proximally of the distal portion, the intermediate portion being of a membrane material that is stretchable.
- the filter body is preferably of a membrane of a memory material especially a polymeric material.
- the invention also provides a collapsible filter element for a transcatheter embolic protection device the filter element comprising:
- the invention further provides a collapsible filter element for a transcatheter embolic protection device, the filter element comprising:
- transcatheter embolic protection device including:
- the frame preferably comprises a plurality of support arms having proximal and distal ends.
- the arms may be formed of an elastic, a superelastic and/or a shape memory material.
- said frame is constructed such that filter body is biased toward said second, deployed configuration.
- said inlet openings are defined at least partially by said arms, proximal portions of said arms preferably extend generally outwardly and distally from said guidewire when said filter body is in said second, deployed configuration. Distal portions of said arms may extend generally outwardly and proximally from said guidewire when said filter body is in said second, deployed configuration.
- the distal portion of the tubular member further includes a pod for receiving therein the filter body when in said first, collapsed configuration.
- said filter body is urged into said first, collapsed configuration by said pod when the guidewire is moved proximally.
- said guidewire is solid.
- said filter body comprises a sleeve slidably disposed on said guidewire.
- the device comprises stops for limiting the range of longitudinal movement of the sleeve on said guidewire.
- the sleeve may further comprise a guidewire member distal to the filter body tapering distally.
- FIG. 1 is partially sectioned elevational view of an embolic protection device according to the invention
- FIG. 2 is a schematic sectional elevational view of the embolic protection device of FIG. 1 ;
- FIG. 3 is a sectional view of the distal end of the device of FIG. 1 shown in its loaded condition within its delivery catheter;
- FIG. 4 is a longitudinal cross sectional view of the device of FIG. 1 ;
- FIG. 5 is a cross sectional view of a distal end of the device of FIG. 1 ;
- FIG. 6 is a view on the line A-A in FIG. 4 ;
- FIG. 7 is a perspective view of a filter body of the device of FIGS. 1 to 6 ;
- FIG. 8 is a side elevational view of the filter body of FIG. 7 ;
- FIG. 9 is a view on a proximal end of the filter body
- FIG. 10 is a perspective view of a support frame
- FIG. 11 is a side elevational view of the support frame
- FIG. 12 is a perspective view illustrating the manufacture of the support frame
- FIG. 13 is a view of the support frame and filter body assembly
- FIGS. 14A to 14E are developed views of the distal end of a filter body illustrating different arrangements of outlet holes for filter sizes 6 mm, 4 mm, 4.5 mm, 5 mm, and 5.5 mm respectively;
- FIG. 15 is a side elevational view of another filter body of the invention.
- FIG. 16 is a developed view of the distal end of the filter body of FIG. 15 illustrating an arrangement of outlet holes
- FIGS. 17( a ) and 17 ( b ) are perspective partially cut-away cross sectional views of a filter body before and after solvent polishing respectively;
- FIG. 18 is a graph of shear stress with outlet hole size and hole number
- FIG. 19 is a longitudinal cross sectional view of a filter body according to the invention.
- FIGS. 20 to 25 are longitudinal cross sectional views of different embodiments of the filter body according to the invention.
- FIGS. 26 to 28 are longitudinal cross sectional views of further embodiments of the filter body according to the invention.
- FIG. 29 is a schematic perspective view of a filter element according to another aspect of the invention.
- FIGS. 30 to 33 are schematic perspective views of different embodiments of the filter element according to the invention.
- FIG. 34 is a schematic perspective view of a filter element according to a further aspect of the invention.
- FIGS. 35( a ) to 35 ( d ) are longitudinal side views of another filter according to the invention in different configurations of use.
- FIGS. 1 to 13 there is illustrated an embolic protection device as described in our WO-A-9923976 indicated generally by the reference number 100 .
- the device 100 has a guidewire 101 with a proximal end 102 and a distal end 103 .
- a tubular sleeve 104 is slidably mounted on the guidewire 101 .
- a collapsible filter 105 is mounted on the sleeve 104 . the filter 105 being movable between a collapsed stored position against the sleeve 104 and an expanded position as shown in the drawings extended outwardly of the sleeve 104 for deployment in a blood vessel.
- the sleeve 104 is slidable on the guidewire 101 between a pair of spaced-apart end stops, namely an inner stop 106 and an outer stop which in this case is formed by a spring tip 107 at the distal end 103 of the guidewire 101 .
- the filter 105 comprises a filter body 110 mounted over a collapsible support frame 111 .
- the filter body 110 is mounted to the sleeve 104 at each end, the body 110 being rigidly attached to a proximal end 112 of the sleeve 104 and the body 110 being attached to a collar 115 which is slidable along a distal end 114 of the sleeve 104 .
- the distal end of the body 110 is longitudinally slidable along the sleeve 104 .
- the support frame 111 is also fixed at the proximal end 112 of the sleeve 104 .
- a distal end 116 of the support frame 111 is not attached to the sleeve 104 and is thus also free to move longitudinally along the sleeve 104 to facilitate collapsing the support frame 111 against the sleeve 104 .
- the support frame 111 is such that it is naturally expanded as shown in the drawings and can be collapsed inwardly against the sleeve 104 for loading in a catheter 118 or the like.
- the filter body 110 has large proximal inlet openings 117 and small distal outlet openings 119 .
- the proximal inlet openings 117 allow blood and embolic material to enter the filter body 110
- the distal outlet openings 119 allow through passage of blood but retain undesired embolic material within the filter body 110 .
- An olive guide 120 is mounted at a distal end of the sleeve 104 and has a cylindrical central portion 121 with tapered ends 122 , 123 .
- the distal end 122 may be an arrowhead configuration for smooth transition between the catheter and olive surfaces.
- the support frame 111 is shaped to provide a circumferential groove 125 in the filter body 110 . If the filter 105 is too large for a vessel, the body 110 may crease and this groove 125 ensures any crease does not propagate along the filter 105 .
- Enlarged openings are provided at a proximal end of the filter body 110 to allow ingress of blood and embolic material into an interior of the body 110 .
- the collapsible support frame 111 has four foldable arms 290 which are collapsed for deployment and upon release extend outwardly to expand the filter body 110 .
- the support frame 111 can be manufactured from a range of metallic or polymeric components such as a shape memory alloy like nitinol or a shape memory polymer or a shaped stainless steel or metal with similar properties that will recover from the deformation sufficiently to cause the filter body 110 to open.
- a shape memory alloy like nitinol or a shape memory polymer or a shaped stainless steel or metal with similar properties that will recover from the deformation sufficiently to cause the filter body 110 to open.
- the support frame 111 may be formed as illustrated in FIG. 12 by machining slots in a tube 291 of shape memory alloy such as nitinol. On machining, the unslotted distal end of the tube 291 forms a distal collar 293 and the unslotted proximal end of the tube 291 forms a proximal collar 294 .
- the distal collar 293 is slidably movable along the tubular sleeve 104 which in turn is slidably mounted on the guidewire 101 for deployment and retrieval.
- the proximal collar 294 is fixed relative to the tubular sleeve 104 .
- the sub assembly of the support frame 111 and filter body 110 is pulled back into the catheter 118 to engage the distal stop 107 .
- the support arms 290 are hinged inwardly and the distal collar 293 moves forward along the tubular sleeve 104 .
- the filter body 110 stretches as the filter body collar 115 slides along the tubular sleeve 104 proximal to the olive 120 .
- the catheter 118 is retracted proximally along the guidewire 101 initially bringing the collapsed filter assembly with it until it engages the proximal stop 106 .
- the catheter sleeve then begins to pull off the filter 105 freeing the support arms 290 to expand and the filter body 110 apposes the vessel wall.
- a retrieval catheter For retrieval a retrieval catheter is introduced by sliding it over the guidewire 101 until it is positioned at the proximal end of the filter body 110 and support frame 111 . Pulling the guidewire 101 will initially engage the distal stop 107 with the filter element and begin to pull it into the retrieval catheter. The initial travel into the retrieval catheter acts to close the proximal openings 117 of the filter element, thus entrapping the embolic load. As the filter 105 continues to be pulled back the filter body 110 and the support frame 111 are enveloped in the retrieval catheter. The collapsed filter 105 may then be removed from the patient.
- the tip of the catheter which forms a housing or pod for reception of the filter is of an elastic material which can radially expand to accommodate the filter with the captured embolic material.
- the same catheter or pod can be used to deploy and retrieve the filter.
- the elastic material holds the filter in a tightly collapsed position to minimise the size of the catheter tip or pod. Then, when retrieving the filter, the catheter tip or pod is sufficiently elastic to accommodate the extra bulk of the filter due to the embolic material.
- the filter is not fast on the guidewire and thus accidental movement of the guidewire is accommodated without unintentionally moving the filter, for example, during exchange of medical devices or when changing catheters.
- the filter according to the invention does not have a sharp outer edge as with many umbrella type filters. Rather, the generally tubular filter shape is more accommodating of the interior walls of blood vessels.
- the catheter can be removed leaving a bare guidewire proximal to the filter for use with known devices such as balloon catheter and stent devices upstream of the filter.
- the outer filter body 110 is preferably of a resilient biocompatible elastomeric material.
- the material may be a polyurethane based material.
- polyurethane based material There are a series of commercially available polyurethane materials that may be suitable. These are typically based on polyether or polycarbonate or silicone macroglycols together with diisocyanate and a diol or diamine or alkanolamine or water chain extender. Examples of these are described in EP-A-461,375 and U.S. Pat. No. 5,621,065.
- polyurethane elastomers manufactured from polycarbonate polyols as described in U.S. Pat. No. 5,254,622 (Szycher) are also suitable.
- the filter material may also be a biostable polycarbonate urethane article an example of which may be prepared by reaction of an isocyanate, a chain extender and a polycarbonate copolymer polyol of alkyl carbonates. This material is described in our WO 9924084.
- the filter body may be manufactured from a block and cut into a desired shape.
- the filter may be preferably formed by dipping a rod of desired geometry into a solution of the material which coats the rod. The rod is then dissolved.
- the final geometry of the filter may be determined in the dipping step or the final geometry may be achieved in a finishing operation. Typically the finishing operations involve processes such as mechanical machining operations, laser machining or chemical machining.
- the filter body is of hollow construction and may be formed as described above by dipping a rod in a solution of polymeric material to coat the rod. The rod is then dissolved, leaving a hollow body polymeric material.
- the rod may be of an acrylic material which is dissolved by a suitable solvent such as acetone.
- the polymeric body thus formed is machined to the shape illustrated in FIGS. 1 to 13 .
- the final machined filter body comprises an inlet or proximal portion 210 with a proximal neck 212 , and outlet or distal portion 213 with a distal neck 214 , and an intermediate portion 215 between the proximal and distal portions.
- the filter body may be formed by a blow moulding process using a suitably shaped mould. This results in a filter body which has thin walls.
- the inlet holes 117 are provided in the proximal portion 210 which allow the blood and embolic material to flow into the filter body.
- the proximal portion 210 is of generally conical shape to maximise the hole size.
- the intermediate portion 215 is also hollow and in this case is of generally cylindrical construction. This is important in ensuring more than simple point contact with the surrounding blood vessel.
- the cylindrical structure allows the filter body to come into soft contact with the blood vessel to avoid damaging the vessel wall.
- the intermediate portion 215 is provided with a radial stiffening means, in this case in the form of a radial strengthening ring or rim 220 .
- the ring 220 provides localised stiffening of the filter body without stiffening the material in contact with the vessel. Such an arrangement provides appropriate structural strength so that line apposition of the filter body to the vessel wall is achieved. It is expected that other geometries of stiffening means will achieve a similar result.
- the tubular intermediate portion 215 is also important in maintaining the stability of the filter body in situ to retain captured emboli and to ensure that flow around the filter is minimised.
- the ratio of the axial length of the intermediate portion 215 of the filter body to the diameter of the intermediate portion 215 is preferably at least 0.5 and ideally greater than 1.0.
- the outlet holes 119 are provided in the distal portion 213 which allow blood to pass and retain embolic material in the filter body.
- the purpose of the filter is to remove larger particulate debris from the bloodstream during procedures such as angioplasty.
- the filter is used to prevent ingress of embolic material to the smaller blood vessels distal to a newly-deployed carotid stent.
- a known property of the filter is that it will present a resistance to the blood flow.
- the maximum blood pressure in the arterial system is determined by the muscular action of the heart.
- the cardiovascular system is a multiple-redundant network designed to supply oxygenated blood to the tissues of the body. The path from the heart through the site of deployment of the filter and back to the heart can be traced through the system. In the absence of the filter this system has a resistance, and the flow through any part of it is determined by the distribution of resistance and by the pressure generated by the heart.
- the introduction of the filter adds a resistance on one of the paths in the network, and therefore there will be a reduced blood flow through this part of the circuit. It is reasonable to assume that the flow along the restricted carotid will be inversely proportional to the resistance of this branch of the circuit. For laminar flow in a tube the resistance is independent of the flow rate.
- vascular filters and particularly vascular filters for smaller blood vessels is determined by the relationship between the filter and the media being filtered.
- Blood is a complex suspension of different cell types that react differently to different stimuli.
- the defining geometric attributes of the filter structure will establish the filter's resistance to flow in any blood vessel. Ideally, all flow will be through the filter and will be exposed to minimal damage.
- Red cells have an ability to deform under the influence of shear stresses. At low stresses (physiological) this deformation is recoverable. Additionally, a percentage of the red cell population is fragile and will fragment at low shear stress even in patients with “healthy” cell populations. While the body can deal with the rupture and fragmentation of small numbers of red blood cells, gross red blood cell damage are likely to be problematic clinically. Consideration must be given to the effects of the shear stresses, both the intensity and duration, on the constituent blood particles and the haemostatic mechanisms. It is the effects on the red blood cells and platelets that are of primary importance.
- thrombus it is also possible for the thrombus to become detached, particularly on removal of the device, and float freely away downstream to become an embolus. Should the embolus be large enough to become trapped in a narrow arterial vessel further along the system, flow in that vessel would be compromised and this could lead directly to stroke. Platelet aggregation occurs most effectively in stagnant and recirculating flow regions.
- activated platelets can coat foreign bodies in the blood, such as intravasculature catheters.
- the foreign material surface then becomes sticky and therefore a site for further aggregation. This in turn could affect the local geometry of the device and the local flow characteristics.
- Shear may be expressed as follows:
- FIG. 18 we show the relationship under specific flow conditions in a stated diameter of vessel. This plot assumes a Newtonian fluid, equal flow rate through each hole, a flow rate of 270 ml/min and a 4 mm blood vessel.
- shear is a good general representation however, local conditions at the filter pores can have significant impact on the shear with flow irregularities generating the possibility of shear levels increasing by an order of magnitude.
- the location of the maximum shear stress is at the edges of the filter holes at their downstream side.
- the filter element of the invention has local radii and the filter entrance and exit holes to minimise the shear stress levels. Holes may be drilled using mechanical drilling or laser cutting. However, these processes can produce dimensionally repeatable holes but will impart surface conditions that are not suitable for small vessel filtration. Any fraying of edges due to mechanical cutting will certainly cause flow disruptions and form sites for platelet aggregation. Similarly laser cutting due to its local intense heating and vaporisation of the substrate will lead to pitting, surface inclusions, rough edges and surface imperfections.
- the holes are post processed to modify the surfaces and to radius the edges.
- a preferred embodiment of the filter element is manufactured using a medial grade polyurethane such as ChronoflexTM supplied by Cardiotech Inc.
- the filter holes are post-processed by solvent polishing using acetone or other suitable solvent.
- FIG. 17( a ) there is illustrated a section of a polymeric filter body with a number of machined outlet holes 119 . After solvent polishing the hoes are surface treated providing radiused lead-in and lead-out portions.
- Solvent polishing of the membrane is achieved by softening the material in the surface lavers of the membrane such that a local reflow process is facilitated. This reflow is achieved using one of two classes of solvent.
- the process for the first class of solvents involves exposing the membrane to a limited amount of the solvent. This is achieved by dipping the membrane in the solvent for a short time or exposing the membrane to concentrated vapours of the solvent for a time.
- the solvent is absorbed into the surface layers and they become solubilised.
- the solubilised surface layers act like a viscous liquid and they adopt configurations of lowest surface energy.
- the lowest energy configuration for a liquid is a sphere.
- the sharp edges and corners become rounded by the solubilisation of the surface.
- the solvent is dried to reveal a smooth solvent polished surface.
- Swelling solvents act slightly differently in that they cannot dissolve the material. However their ability to swell the material allows similar reflow processes to occur. The key difference is that the membrane is immersed in the solvent for a longer period of time, preferably in excess of 30 minutes.
- the solvent swelling process is most effective when the membrane material is a two phase polymer such as a polyurethane or a PEBAX, as the solvent can be selected to match either phase.
- Solvents will dissolve polymers when their solubility parameters are similar. Solvents will swell a polymer when their solubility parameters are slightly different. Preferably the swelling solvent swells the material by less than 30%. Above this level the solvent should be considered dissolving solvent.
- filter is one where the polished polymeric surface is combined with a coating on the substrate.
- the swelling of the polymer matrix reduces residual stresses that may have developed during the coated core drying or lasering processes.
- the material in the immediate proximity of the lasered holes will have been exposed to heat. This heat will disrupt hard segment crystallites and they will reform to lower order meta-stable structures or be completely dissolved in the soft phase.
- the heat will also induce the soft segments to contract, however, the re-arrangement of the hard segments imposes new restrictions on the recovery of the soft segments to an equilibrium (relaxed) state.
- the morphology of the block copolymer will have changed, in the sense that the new configurations of the hard segments and soft segments will have been frozen in.
- the holes After lasering, the holes have sharp and well-defined geometries.
- the solvent After exposing the coated material to the solvent, the solvent uncoils the soft segment chains and disassociates low ordered hard segment that are dissolved in the soft segment phase, so on removal of the solvent, the polymer matrix dries in a more relaxed state. In so doing, the sharp, well-defined walls of the lasered holes are transformed to a more contoured relaxed state.
- Such applicable solvents for this application are 2-propanone, methyl ethyl ketone or trichloroethylene.
- the optimum average diameter of the outlet holes in the polymeric membrane is from 100 to 200 microns, ideally approximately 150 microns.
- the number of holes in the distal portion 213 is from 200 to 500, ideally about 300. This hole size and number of holes minimises shear levels by reducing localised flow rates. Thus, we have found that shear can be maintained below 800, preferably below 500 and ideally below 200 Pa at a blood flow rate of up to 270 ml/min in a 4 mm blood vessel. Ideally the holes are circular holes.
- the filter provides appropriate haemodynamics to minimise turbulence and inappropriate shear stress on native arteries and veins. Damage to flowing blood such as haemolysis which involves the destruction of red blood cells by rupture of the cell envelope and release of contained haemoglobin is avoided.
- the outlet hole size and number of holes is optimised in order to capture embolic material, to allow the embolic material to be entrapped in the filter body and to be withdrawn through a delivery device such as a delivery catheter on collapsing of the filter body.
- Shearing of red blood and damage to platelets during filtration is a problem easily solved in extra-corporeal circuits by providing large filter areas with consequent low flow rates through individual pores controlled to flow rates such that the shear is maintained in ranges that are below known threshold levels with clinical relevance.
- the porosity of the distal end of the filter membrane and the arrangement of outlet holes is important in optimising capture of embolic material without adversely effecting blood shear characteristics and the material properties of the filter body which allow it to be collapsed for delivery, expanded for deployment and collapsed for retrieval.
- the overall porosity of the filter element is preferably between 5% and 40% and ideally between 8% and 21%.
- the transverse cross sectional areas of the filter body at longitudinally spaced-apart locations of the distal portion are substantially the same.
- the porosity of the distal portion of the filter body should decrease towards the distal end.
- Arrangements of distal holes 119 for different filter diameters are shown in FIGS. 14( a ) to 14 ( e ).
- FIG. 14( a ) shows an arrangement for a 6 mm filter
- FIG. 14( c ) for a 4.5 mm filter
- FIG. 14( d ) for a 5 mm filter
- FIG. 14( e ) for a 5.5 mm filter.
- the number of outlet holes 119 also increases towards an outer edge of the distal portion of the filter body.
- the distal portion of the filter element includes a blind section 130 adjacent the distal end of the filter element.
- the blind portion 130 extends longitudinally for at least 5% and preferably less than 30% of the length of the distal portion.
- the thickness of the filter membrane In order to reduce the profile of the filter body we have significantly reduced the thickness of the filter membrane to typically in the order of 25 microns. This reduction in thickness however means that the membrane used must have a relatively high stiffness to achieve a comparable strength. However, we have found that such an increase in stiffness results in poor memory performance and is therefore undesirable.
- hydrophilic coatings and hydrogels are highly suitable coatings as they have a similar surface to the endothelial lining of a blood vessel and are not perceived by the body's immune system as foreign. This results in at least reduction and in some cases substantial elimination of platelet adhesion and fibrin build up which could otherwise occlude the filter and/or create a harmful thrombus.
- the coating also provide a relatively low friction surface between the filter body and the delicate endothelial lining of a vessel wall and therefore minimise the trauma and injury to a vessel wall caused by deployment of the filter body in the vasculature.
- a hydrogel will absorb water swelling its volume. The swelling of the hydrogel will exert an expansion force on the membrane helping to pull it into its recovered or deployed shape.
- a coating that expands on contact with blood will exert an expansion force on the membrane helping to pull it into its recovered or deployed shape.
- a coating that expands when subjected to body temperature will exert an expansion force on the membrane helping to pull it into its recovered or deployed shape.
- Hydrophilic coatings can be classified by their molecular structure:
- Hydrophilic coatings may be also synthetic or natural.
- Synthetic hydrophilic polymers include the following:
- Natural hydrophylics include:
- hydrophylic coatings suitable for coating filter membrane include, but are not limited to the following:
- Hydrogels as stated are cross-linked hydrophilic molecules.
- the molecular mobility of hydrogels is constant and extensive, giving ceaseless molecular motion, which contributes to the property of biocompatibility by inhibiting protein absorption.
- W [( Wsw ⁇ Wo )/ Wsw] ⁇ 100
- a typical hydrogel will absorb up to 20% of their dry weight of water.
- Superabsorbant hydrogels will absorb up to 2000% of their dry weight of water.
- Hydrogel strength is directly related to cross link density ( ⁇ ) and molecular weight between cross-links (Mc).
- Hydrophilic coatings may be typically applied by dipping, spraying and/or brushing.
- the coatings may also be applied by solution or by colloidal dispersion.
- the membrane surface to be coated may be prepared by cleaning with a solvent and/or ultrasonic cleaning. Plasma or corona discharge may also be used to increase the surface energy and thus provide for better adhesion.
- Hydrophilics include low friction fluoropolymer i.e. PTFE & FEP coatings that are chemically inert and have low coefficients of friction, which also helps prevent adhesion of platelets.
- Both diamond like carbon & tetracarbon also provide very thin hard surface layers, which help reduce the dynamic coefficient of friction for elastomers.
- the coating may be typically applied by dipping, spraying and/or brushing.
- the coatings may also be applied by solution or colloidal dispersion.
- a polymeric filter membrane is first produced by machining a core of a desired shape from an inert material such as perspex.
- the perspex core is then dipped in a solution of a polymeric material as described above.
- the membrane is formed by blow moulding. Holes are then laser machined in the dipped core.
- the perspex core is removed by dissolving in acetone. Residual acetone is washed out with water.
- a filter frame of gold plated Nitinol is mounted on a filter carrier in the form of a polyimide tube.
- the filter membrane is then slid over the filter support frame to provide an uncoated filter assembly.
- the filter assembly is dipped in a solvent such as propan 2-ol to clean the assembly.
- the cleaned assembly is then dipped in a solution of a coating material.
- a vacuum is applied to remove excess coating material prior to drying in an oven.
- the coating material is typically of Aquamer in a water/ethanol solution.
- the thickness of the coating is typically 2 to 10 microns.
- the filter body contains regions of varying stiffness and durometer hardness.
- the change in filter stiffness along its geometry can be achieved by varying the material properties or by modifications to the thickness or geometry of the membrane.
- the change in material hardness is achieved by varying the material properties.
- the polymer material may be one of the following: polyamides, polyurethanes, polyesters, a polyether block amide (PEBAX), olefinic elastomer, styrenic elastomer.
- the filter body has a durometer of between 60 D and 70 A Shore hardness.
- the filter body 2 has a proximal section 3 and a distal section 4 interconnected by an intermediate section 5 .
- Both the proximal section 3 and the distal section 4 are made from a relatively stiff grade of polyurethane material which enables a low wall thickness to be achieved, thus advantageously minimising the bulk of the filter when it is in a collapsed position so that it has a low crossing profile while at the same time providing adequate strength.
- the intermediate section 5 is made from a soft elastic grade of polyurethane having good shape memory characteristics which will help the filter maintain the desired expanded shape during use of the filter. This soft portion also allows one filter size to accommodate a range of vessel sizes conforming closely to the vessel wall to prevent blood and embolic material bypassing the filter.
- the body is of generally uniform thickness in cross section.
- the thickness may be variable such as in the filter body 10 illustrated in FIG. 20 .
- any required structural properties may also be provided by a filter body which is at least partially of a laminate construction.
- the layers of the laminate may be of the same or different materials.
- the distal section 4 and part of the intermediate section 5 are of a two layer 21 , 22 construction.
- the lavers 21 , 22 may be of the same or different materials.
- the layers 21 , 22 are keyed together by mechanical or chemical means the holes in the distal section 4 are then formed by boring through the two layers 21 , 22 .
- the entire filter body 30 is of a three layer 31 , 32 , 33 construction.
- Layer 31 is a structural layer made from a material such as polyether block amide (PEBAX), polyester, polyethylene, polyurethane, terephthalate (PET), or nylon.
- Layers 32 , 33 are coating layers made from a material such as a hydrophilic, hydrogel, non-thrombogenic, or non-stick material. Layers 32 , 33 may be of the same or different materials.
- the holes at the distal end 4 are also lined with the coating layers 32 , 33 .
- coating layers 32 , 33 are of different materials, they are applied to structural layer 31 as follows. A temporary protective film is first sealed to the outer most surface of layer 31 . Then coating layer 33 is applied to the inner most surface of layer 31 by immersing the body formed by layer 31 in a coating solution. Excess coating solution is sucked out and the protective film is removed from the outer most surface of layer 31 . Another temporary protective film is then sealed to the inner most surface of layer 33 . The body formed by layers 31 , 33 is completely immersed in a coating solution. Excess coating solution is drawn out and the protective film is removed from the innermost surface of layer 33 .
- both layers 32 , 33 may be applied to the structural layer 31 in one step without the use of protective films.
- the entire filter body 45 is of a three layer 46 , 47 , 48 construction.
- Layers 46 , 47 , 48 are structural layers and layers 47 , 48 are of the same material.
- the holes at the distal end 4 are also lined with the structural layers 47 , 48 .
- the entire filter body 50 is of a three layer 51 , 52 , 53 construction.
- Layers 51 , 52 , 53 are structural layers, and in this embodiment layers 52 , 53 are of different materials.
- the entire filter body 55 is of a four layer 56 , 57 , 58 , 59 construction.
- Layers 56 , 57 are structural layers and may be of the same or different materials.
- Layers 58 , 59 are coating layers and may be of the same or different materials.
- the holes at the distal end 4 are also lined with the coating layers 58 , 59 .
- FIG. 26 there is illustrated another filter element 60 according to the invention, which is similar to part of the distal section 4 of filter element 2 of FIG. 19 . But having no proximal webbing members thus maximising the size of the inlet opening.
- FIG. 27 illustrates a filter element 61 , which is similar to the distal section 4 and part of the intermediate section 5 of filter element 20 of FIG. 21 , having the advantages of the laminate structure previously described, combined with the large inlet opening of FIG. 26 and the variable distal geometry of FIG. 19 (enabling the filter to accommodate a range of vessel sizes).
- FIG. 28 illustrates a further filter element 65 , which includes a support ring 66 to maintain the intermediate section 5 open to advancing blood flow.
- Support ring 66 may be arranged perpendicular to the direction of the blood flow or inclined at an angle, as illustrated in FIG. 28 .
- the support ring 66 may be of an elastic, super elastic or shape memory material. and may be either actuated remotely to appose the vessel wall in a perpendicular or close to perpendicular position, or fixed in circumference so that its inclination and shape are controlled by the diameter of the vessel.
- a different layer structure may be provided at any desired location of the filter body to achieve required properties.
- the filter element 70 has a filter body 72 of generally similar construction to the filter element described previously, the body having a proximal section 73 and a distal section 74 interconnected by an intermediate section 75 .
- the distal section 74 is of a relatively hard polyurethane material whilst the proximal section 73 and intermediate section 75 are of a softer grade polyurethane material.
- a number of longitudinal ribs 76 are provided around a circumference of the proximal section 73 .
- this construction facilitates close engagement of an outer circumference of the proximal section 73 against a vessel wall to minimise the risk of embolic material bypassing the filter element 70 .
- An internal support frame urges the proximal section 73 outwardly so that it expands against and closely conforms with the wall of the blood vessel in which the filter element 70 is mounted in use.
- the corrugations or ribs 76 allow the proximal section 73 of the filter element 70 to accommodate a wider range of vessel sizes whilst maintaining good contact between the outer circumference of the proximal section 73 and the vessel wall and providing improved tilter body integrity.
- FIG. 30 there is illustrated another filter element 80 according to the invention.
- corrugations 81 are provided for improved filter body integrity.
- FIG. 31 there is illustrated another filter element 82 according to the invention.
- the cross section of the filter element 82 is of a flower petal shape with a plurality of longitudinally extending ribs 83 for improved apposition.
- the “petal shaped” cross section (as for corrugations) increase the circumference of the filter body, thus enabling the body to be apposed closely against the vessel wall by a supporting structure in a wide range of vessel sizes.
- FIG. 32 there is illustrated another filter element 85 according to the invention.
- slits 86 are provided in the place of the corrugations or “petal shapes” shown above.
- the slits 86 enable the body of the filter to conform to a range of vessel diameters by overlapping and preventing creasing in small diameter vessels, or allowing the body to expand with the aid of a supporting structure in larger diameter vessels. In both instances close engagement of the outer circumference with the vessel wall is facilitated, thus minimizing the risk of embolic material bypassing the filter.
- FIG. 33 there is illustrated another filter element 88 according to the invention.
- ribs 89 are provided to prevent creases forming along the filter element 88 in the longitudinal direction, and also to allow expansion of the filter element 88 .
- FIG. 34 there is illustrated a further filter element 90 according to the invention, which is of a concertina-like shape with two circumferentially extending grooves 91 , 92 .
- This circumferential grooves or ribs have several advantages. They add to the integrity of the filter body, assisting it in maintaining its shape in the vessel after deployment. They inhibit the propagation of creases between the varying diameter body segments, so that one filter can be designed for a range of vessel sizes. They enable the filter to extend in length to greatly increase its effective volume without adding to the length of the deployed device in use. This provides the benefit of safe retrieval of large embolic loads as explained with reference to stretchable membranes below.
- FIGS. 35( a ) to 35 ( d ) there is illustrated another embolic protection system according to the invention incorporating a filter element 94 according to the invention which is similar to those described above.
- the protection system includes a guidewire 95 and a retrieval catheter 96 which is advanced over the guidewire to retrieve the filter containing trapped embolic material 97 .
- the filter body includes an intermediate 98 and distal 99 membrane, one or both of which are stretchable to facilitate the retrieval of the captured embolic material 97 .
- the stretching of the membrane during the retrieval process is illustrated in FIGS. 35( b ) to 35 ( d ).
- stretchable filter membrane allows larger volumes of captured embolic material to be retrieved than would be possible with a stiffer membrane. This is possible because if a filter is to be retrieved by withdrawing it into or through a catheter of a given internal diameter, the maximum volume of material that can be retrieved is directly proportional to the length of the filter and the internal diameter of the catheter.
- the stretchable membrane allows the filter to increase in length upon retrieval, thus increasing the space available for retention of captured embolic material. This is particularly significant in the case of large volumes of captured embolic material, which will be more difficult to safely retrieve with a non-stretchable device.
- the stretchable section may include some or all of the filter body, and may not necessarily include the distal cone.
- the distal cone containing the outlet pores may be formed from a non stretch material, while the inter mediate filter body is stretchable.
- This provides the advantage of filter extension during retrieval while preventing the problem of release of captured material through expanding distal pores.
- stretchable section Another advantage of the stretchable section is that the crossing profile can be reduced as the filter can be loaded into a delivery pod in a stretched, rather than bunched or folded, configuration. This reduces the volume of filter material contained in any given cross section of the loaded delivery pod.
- a stretchable filter material in the intermediate section can also be advantageous by providing a section of the filter body which can be circumferentially expanded by a support frame to appose the wall of a wide range of vessel sizes.
Abstract
A collapsible filter element (105) for a transcatheter embolic protection device (100) comprises a collapsible filter body (30) which is movable between a collapsed stored position for movement through a vascular system and an expanded position for extension across a blood vessel such that blood passing through the blood vessel is delivered through the filter element (105). A proximal inlet portion of the filter body (30) has one or more inlet openings (117) sized to allow blood and embolic material enter the filter body (30) and a distal outlet portion of the filter body (30) has a plurality of outlet openings (119) sized to allow through-passage of blood, but to retain embolic material within the filter body (30). The filter body (30) is at least partially of laminate construction comprising a membrane (31) coated with a coating (32, 33) which is biocompatible, the thickness of the coating (32, 33) being from 4% to 40% of the thickness of the membrane (31). The coating (32, 33) may be of hydrophilic material. To facilitate retrieval of captured embolic material the distal portion and/or an intermediate portion of the filter membrane (31) may be stretchable. The filter body (30) may have regions of varying hardness or stiffness.
Description
- This application is a continuation of pending prior application Ser. No. 09/985,820 filed Nov. 6, 2001, which is a Continuation Application of PCT Application No. PCT/IE00/00053, filed May 8, 2000, which claims benefit of priority from PCT/IE99/00033 and PCT/IE99/00036, both filed May 7, 1999. The entire disclosure of the prior application U.S. application Ser. No. 09/985,820, as well as prior filed PCT Application No. PCT/IE00/00053, filed May 8, 2000, priority of which is claimed under 35 U.S.C. §120, and prior filed Application Nos. PCT/IE99/00033 and PCT/IE99/00036 both filed May 7, 1999, priority of which is claimed under 35 U.S.C. § 119, are considered part of the disclosure of the present continuation application and are incorporated herein by reference.
- This invention relates to a filter element for a transcatheter embolic protection device.
- The invention is particularly concerned with filter elements for transcatheter embolic protection devices of the type described in our WO-A-9923976. One type of such embolic filter essentially comprises a filter body mounted on an associated collapsible support frame which can be collapsed against the guide wire by means of a catheter for deployment of the filter through a patient's vascular system. Upon retraction of the catheter the support frame and filter body expand outwardly from the guidewire across a blood vessel within which the filter is positioned to filter blood flowing through the blood vessel.
- A practical problem that arises with filter elements of such embolic protection devices is that they should be able to accommodate blood vessels of different diameter as it would be impractical to manufacture a large range of filters each of different size to accommodate all possible diameters of blood vessel. To provide flexibility and accommodate a range of vessel sizes with a given size of filter a relatively soft and elastic filter body material can be used. It is, however, important that the filter when deployed maintains its shape during use and to prevent distortion or collapsing of the filter body in use. Because of this and also the need for adequate strength in the body material, the walls of the filter body tend to be relatively thick. This presents a problem in that the filter then has a relatively large crossing profile when in the collapsed deployment position, which is undesirable.
- The present invention is directed towards overcoming these and other problems.
- According to the invention there is provided a collapsible filter element for a transcatheter embolic protection device, the filter element comprising:
-
- a collapsible filter body which is movable between a collapsed stored position for movement through a vascular system and an expanded position for extension across a blood vessel such that blood passing through the blood vessel is delivered through the filter element;
- a proximal inlet portion of the filter body having one or more inlet openings sized to allow blood and embolic material enter the filter body;
- a distal outlet portion of the filter body having a plurality of outlet openings sized to allow through-passage of blood, but to retain embolic material within the filter body;
- the filter body being at least partially of laminate construction comprising a membrane coated with a coating which is biocompatible, the thickness of the coating being from 4% to 40% of the thickness of the membrane to enhance the mechanical characteristics of the filter body.
- In a preferred embodiment the thickness of the coating is from 4% to 30% of the thickness of the membrane, ideally the thickness of the coating is approximately 20% of the thickness of the membrane.
- The membrane may be of a material selected from one or more of polyether block amide (PEBAX), polyester, polyethylene, polyurethane, terephthalate, nylon or, as appropriate copolymers thereof.
- In a preferred embodiment the coating is at least partially of a material selected from a non thrombogenic material and a fluoropolymer material.
- The coating is most preferably of a hydrophilic material. In one embodiment the coating is of a hydrogel material. In one embodiment the coating includes a physiologically acceptable additive. The additive may be a therapeutic additive. The additive is preferably an antithrombogenic additive such as heparin.
- In a preferred embodiment the filter body is surface treated prior to application of the coating.
- Preferably the filter body comprises a proximal body section, a distal body section and an intermediate body section interconnecting the proximal and distal body sections, one or more of the body sections being of laminate construction. The body sections may be of the same laminate construction. At least two of the body sections may be of different laminate construction.
- In one embodiment of the invention the filter body has regions of varying hardness or stiffness. Preferably the filter body has a durometer of between 60 D and 70 A Shore hardness.
- In one arrangement the filter body has a first relatively stiff portion and a second relatively soft portion. One portion or section of the filter body may have a larger wall thickness than the wall thickness of another section or portion.
- The filter body may comprise a proximal body section and a distal body section, one of which forms a stiff first portion and the other of which forms a soft second portion. In one embodiment a proximal body section forms the soft second portion.
- In one embodiment the filter body comprises a proximal body section and a distal body section interconnected by an intermediate body section, one or both of the proximal body section and the intermediate body section forming the soft second portion, the distal body section forming the stiff first portion.
- In an embodiment of the invention the proximal body section has a ribbed outer surface. A plurality of spaced-apart longitudinal ribs may be provided on the proximal section.
- In another embodiment the proximal body section includes corrugations.
- In a particularly preferred embodiment of the invention the filter body has expansion means to facilitate retrieval of the captured embolic material.
- Ideally at least the distal portion of the filter body is of a membrane material that is stretchable. Preferably at least the membrane is stretchable in the longitudinal direction to facilitate retrieval from the vasculature.
- In one embodiment the filter body includes an intermediate portion extending proximally of the distal portion, the intermediate portion being of a membrane material that is stretchable.
- The filter body is preferably of a membrane of a memory material especially a polymeric material.
- The invention also provides a collapsible filter element for a transcatheter embolic protection device the filter element comprising:
-
- a collapsible filter body which is movable between a collapsed stored position for movement through a vascular system and an expanded position for extension across a blood vessel such that blood passing through the blood vessel is delivered through the filter element;
- a proximal inlet portion of the filter body having one or more inlet openings sized to allow blood and embolic material enter the filter body;
- a distal outlet portion of the filter body having a plurality of outlet openings sized to allow through-passage of blood, but to retain embolic material within the filter body;
- the filter body having regions of varying hardness or stiffness.
- The invention further provides a collapsible filter element for a transcatheter embolic protection device, the filter element comprising:
-
- a collapsible filter body which is movable between a collapsed stored position for movement through a vascular system and an expanded position for extension across a blood vessel such that blood passing through the blood vessel is delivered through the filter element;
- a proximal inlet portion of the filter body having one or more inlet openings sized to allow blood and embolic material enter the filter body;
- a distal outlet portion of the filter body having a plurality of outlet openings sized to allow through-passage of blood, but to retain embolic material within the filter body;
- wherein of the filter body has expansion means to facilitate retrieval of captured embolic material.
- In a further aspect the invention provides a transcatheter embolic protection device including:
-
- a delivery system comprising:
- a tubular member having a longitudinal axis, distal and proximal portions, said distal portion of the tubular member being removably advanceable into the vasculature of a patient;
- a medical guidewire longitudinally axially movable in said tubular member and having distal and proximal portions;
- and a filter element of any aspect of the invention the filter body having;
- a first collapsed, insertion and withdrawal configuration and a second expanded, deployed configuration;
- a proximal inlet section and a distal outlet section, said proximal inlet section including inlet openings which are operable to admit body fluid when the filter body is in the second expanded configuration;
- a plurality of outlet openings disposed on at least a portion of the filter element adjacent to the distal outlet section;
- wherein said filter body is moved between said first and second configurations by displacement of said delivery system.
- The frame preferably comprises a plurality of support arms having proximal and distal ends. The arms may be formed of an elastic, a superelastic and/or a shape memory material. In one embodiment said frame is constructed such that filter body is biased toward said second, deployed configuration.
- Preferably said inlet openings are defined at least partially by said arms, proximal portions of said arms preferably extend generally outwardly and distally from said guidewire when said filter body is in said second, deployed configuration. Distal portions of said arms may extend generally outwardly and proximally from said guidewire when said filter body is in said second, deployed configuration.
- In one embodiment the distal portion of the tubular member further includes a pod for receiving therein the filter body when in said first, collapsed configuration.
- Preferably said filter body is urged into said first, collapsed configuration by said pod when the guidewire is moved proximally.
- In one arrangement said guidewire is solid.
- In one embodiment said filter body comprises a sleeve slidably disposed on said guidewire. Ideally the device comprises stops for limiting the range of longitudinal movement of the sleeve on said guidewire. The sleeve may further comprise a guidewire member distal to the filter body tapering distally.
- The invention will be more clearly understood from the following description thereof given by way of example only with reference to the accompanying drawings in which:
-
FIG. 1 is partially sectioned elevational view of an embolic protection device according to the invention; -
FIG. 2 is a schematic sectional elevational view of the embolic protection device ofFIG. 1 ; -
FIG. 3 is a sectional view of the distal end of the device ofFIG. 1 shown in its loaded condition within its delivery catheter; -
FIG. 4 is a longitudinal cross sectional view of the device ofFIG. 1 ; -
FIG. 5 is a cross sectional view of a distal end of the device ofFIG. 1 ; -
FIG. 6 is a view on the line A-A inFIG. 4 ; -
FIG. 7 is a perspective view of a filter body of the device ofFIGS. 1 to 6 ; -
FIG. 8 is a side elevational view of the filter body ofFIG. 7 ; -
FIG. 9 is a view on a proximal end of the filter body; -
FIG. 10 is a perspective view of a support frame; -
FIG. 11 is a side elevational view of the support frame; -
FIG. 12 is a perspective view illustrating the manufacture of the support frame; -
FIG. 13 is a view of the support frame and filter body assembly; -
FIGS. 14A to 14E are developed views of the distal end of a filter body illustrating different arrangements of outlet holes for filter sizes 6 mm, 4 mm, 4.5 mm, 5 mm, and 5.5 mm respectively; -
FIG. 15 is a side elevational view of another filter body of the invention; -
FIG. 16 is a developed view of the distal end of the filter body ofFIG. 15 illustrating an arrangement of outlet holes; -
FIGS. 17( a) and 17(b) are perspective partially cut-away cross sectional views of a filter body before and after solvent polishing respectively; -
FIG. 18 is a graph of shear stress with outlet hole size and hole number; -
FIG. 19 is a longitudinal cross sectional view of a filter body according to the invention; -
FIGS. 20 to 25 are longitudinal cross sectional views of different embodiments of the filter body according to the invention; -
FIGS. 26 to 28 are longitudinal cross sectional views of further embodiments of the filter body according to the invention; -
FIG. 29 is a schematic perspective view of a filter element according to another aspect of the invention; -
FIGS. 30 to 33 are schematic perspective views of different embodiments of the filter element according to the invention; -
FIG. 34 is a schematic perspective view of a filter element according to a further aspect of the invention; and -
FIGS. 35( a) to 35(d) are longitudinal side views of another filter according to the invention in different configurations of use. - Referring to
FIGS. 1 to 13 there is illustrated an embolic protection device as described in our WO-A-9923976 indicated generally by thereference number 100. Thedevice 100 has aguidewire 101 with aproximal end 102 and adistal end 103. Atubular sleeve 104 is slidably mounted on theguidewire 101. Acollapsible filter 105 is mounted on thesleeve 104. thefilter 105 being movable between a collapsed stored position against thesleeve 104 and an expanded position as shown in the drawings extended outwardly of thesleeve 104 for deployment in a blood vessel. - The
sleeve 104 is slidable on theguidewire 101 between a pair of spaced-apart end stops, namely aninner stop 106 and an outer stop which in this case is formed by aspring tip 107 at thedistal end 103 of theguidewire 101. - The
filter 105 comprises afilter body 110 mounted over acollapsible support frame 111. Thefilter body 110 is mounted to thesleeve 104 at each end, thebody 110 being rigidly attached to aproximal end 112 of thesleeve 104 and thebody 110 being attached to acollar 115 which is slidable along adistal end 114 of thesleeve 104. Thus the distal end of thebody 110 is longitudinally slidable along thesleeve 104. Thesupport frame 111 is also fixed at theproximal end 112 of thesleeve 104. Adistal end 116 of thesupport frame 111 is not attached to thesleeve 104 and is thus also free to move longitudinally along thesleeve 104 to facilitate collapsing thesupport frame 111 against thesleeve 104. Thesupport frame 111 is such that it is naturally expanded as shown in the drawings and can be collapsed inwardly against thesleeve 104 for loading in acatheter 118 or the like. - The
filter body 110 has largeproximal inlet openings 117 and smalldistal outlet openings 119. Theproximal inlet openings 117 allow blood and embolic material to enter thefilter body 110, however, thedistal outlet openings 119 allow through passage of blood but retain undesired embolic material within thefilter body 110. - An
olive guide 120 is mounted at a distal end of thesleeve 104 and has a cylindricalcentral portion 121 with tapered ends 122, 123. Thedistal end 122 may be an arrowhead configuration for smooth transition between the catheter and olive surfaces. Thesupport frame 111 is shaped to provide acircumferential groove 125 in thefilter body 110. If thefilter 105 is too large for a vessel, thebody 110 may crease and thisgroove 125 ensures any crease does not propagate along thefilter 105. - Enlarged openings are provided at a proximal end of the
filter body 110 to allow ingress of blood and embolic material into an interior of thebody 110. - Referring in particular to
FIGS. 10 to 13 thecollapsible support frame 111 has fourfoldable arms 290 which are collapsed for deployment and upon release extend outwardly to expand thefilter body 110. - The
support frame 111 can be manufactured from a range of metallic or polymeric components such as a shape memory alloy like nitinol or a shape memory polymer or a shaped stainless steel or metal with similar properties that will recover from the deformation sufficiently to cause thefilter body 110 to open. - The
support frame 111 may be formed as illustrated inFIG. 12 by machining slots in atube 291 of shape memory alloy such as nitinol. On machining, the unslotted distal end of thetube 291 forms adistal collar 293 and the unslotted proximal end of thetube 291 forms aproximal collar 294. In use, as described above, thedistal collar 293 is slidably movable along thetubular sleeve 104 which in turn is slidably mounted on theguidewire 101 for deployment and retrieval. Theproximal collar 294 is fixed relative to thetubular sleeve 104. - To load the
filter 105 the sub assembly of thesupport frame 111 andfilter body 110 is pulled back into thecatheter 118 to engage thedistal stop 107. Thesupport arms 290 are hinged inwardly and thedistal collar 293 moves forward along thetubular sleeve 104. As thesupport arms 290 enter thecatheter 118 thefilter body 110 stretches as thefilter body collar 115 slides along thetubular sleeve 104 proximal to the olive 120. On deployment, thecatheter 118 is retracted proximally along theguidewire 101 initially bringing the collapsed filter assembly with it until it engages theproximal stop 106. The catheter sleeve then begins to pull off thefilter 105 freeing thesupport arms 290 to expand and thefilter body 110 apposes the vessel wall. - For retrieval a retrieval catheter is introduced by sliding it over the
guidewire 101 until it is positioned at the proximal end of thefilter body 110 andsupport frame 111. Pulling theguidewire 101 will initially engage thedistal stop 107 with the filter element and begin to pull it into the retrieval catheter. The initial travel into the retrieval catheter acts to close theproximal openings 117 of the filter element, thus entrapping the embolic load. As thefilter 105 continues to be pulled back thefilter body 110 and thesupport frame 111 are enveloped in the retrieval catheter. Thecollapsed filter 105 may then be removed from the patient. - Conveniently the tip of the catheter which forms a housing or pod for reception of the filter is of an elastic material which can radially expand to accommodate the filter with the captured embolic material. By correct choice of material, the same catheter or pod can be used to deploy and retrieve the filter. For deployment, the elastic material holds the filter in a tightly collapsed position to minimise the size of the catheter tip or pod. Then, when retrieving the filter, the catheter tip or pod is sufficiently elastic to accommodate the extra bulk of the filter due to the embolic material.
- Also, the filter is not fast on the guidewire and thus accidental movement of the guidewire is accommodated without unintentionally moving the filter, for example, during exchange of medical devices or when changing catheters.
- It will also be noted that the filter according to the invention does not have a sharp outer edge as with many umbrella type filters. Rather, the generally tubular filter shape is more accommodating of the interior walls of blood vessels.
- Conveniently also when the filter has been deployed in a blood vessel the catheter can be removed leaving a bare guidewire proximal to the filter for use with known devices such as balloon catheter and stent devices upstream of the filter.
- The
outer filter body 110 is preferably of a resilient biocompatible elastomeric material. The material may be a polyurethane based material. There are a series of commercially available polyurethane materials that may be suitable. These are typically based on polyether or polycarbonate or silicone macroglycols together with diisocyanate and a diol or diamine or alkanolamine or water chain extender. Examples of these are described in EP-A-461,375 and U.S. Pat. No. 5,621,065. In addition, polyurethane elastomers manufactured from polycarbonate polyols as described in U.S. Pat. No. 5,254,622 (Szycher) are also suitable. - The filter material may also be a biostable polycarbonate urethane article an example of which may be prepared by reaction of an isocyanate, a chain extender and a polycarbonate copolymer polyol of alkyl carbonates. This material is described in our WO 9924084.
- The filter body may be manufactured from a block and cut into a desired shape. The filter may be preferably formed by dipping a rod of desired geometry into a solution of the material which coats the rod. The rod is then dissolved. The final geometry of the filter may be determined in the dipping step or the final geometry may be achieved in a finishing operation. Typically the finishing operations involve processes such as mechanical machining operations, laser machining or chemical machining.
- The filter body is of hollow construction and may be formed as described above by dipping a rod in a solution of polymeric material to coat the rod. The rod is then dissolved, leaving a hollow body polymeric material. The rod may be of an acrylic material which is dissolved by a suitable solvent such as acetone.
- The polymeric body thus formed is machined to the shape illustrated in
FIGS. 1 to 13 . The final machined filter body comprises an inlet orproximal portion 210 with aproximal neck 212, and outlet ordistal portion 213 with adistal neck 214, and anintermediate portion 215 between the proximal and distal portions. - Alternatively the filter body may be formed by a blow moulding process using a suitably shaped mould. This results in a filter body which has thin walls.
- The inlet holes 117 are provided in the
proximal portion 210 which allow the blood and embolic material to flow into the filter body. In this case theproximal portion 210 is of generally conical shape to maximise the hole size. - The
intermediate portion 215 is also hollow and in this case is of generally cylindrical construction. This is important in ensuring more than simple point contact with the surrounding blood vessel. The cylindrical structure allows the filter body to come into soft contact with the blood vessel to avoid damaging the vessel wall. - The
intermediate portion 215 is provided with a radial stiffening means, in this case in the form of a radial strengthening ring or rim 220. The ring 220 provides localised stiffening of the filter body without stiffening the material in contact with the vessel. Such an arrangement provides appropriate structural strength so that line apposition of the filter body to the vessel wall is achieved. It is expected that other geometries of stiffening means will achieve a similar result. - The tubular
intermediate portion 215 is also important in maintaining the stability of the filter body in situ to retain captured emboli and to ensure that flow around the filter is minimised. For optimum stability we have found that the ratio of the axial length of theintermediate portion 215 of the filter body to the diameter of theintermediate portion 215 is preferably at least 0.5 and ideally greater than 1.0. - The outlet holes 119 are provided in the
distal portion 213 which allow blood to pass and retain embolic material in the filter body. - The purpose of the filter is to remove larger particulate debris from the bloodstream during procedures such as angioplasty. In one case the filter is used to prevent ingress of embolic material to the smaller blood vessels distal to a newly-deployed carotid stent. A known property of the filter is that it will present a resistance to the blood flow. The maximum blood pressure in the arterial system is determined by the muscular action of the heart. The cardiovascular system is a multiple-redundant network designed to supply oxygenated blood to the tissues of the body. The path from the heart through the site of deployment of the filter and back to the heart can be traced through the system. In the absence of the filter this system has a resistance, and the flow through any part of it is determined by the distribution of resistance and by the pressure generated by the heart.
- The introduction of the filter adds a resistance on one of the paths in the network, and therefore there will be a reduced blood flow through this part of the circuit. It is reasonable to assume that the flow along the restricted carotid will be inversely proportional to the resistance of this branch of the circuit. For laminar flow in a tube the resistance is independent of the flow rate.
- The performance of vascular filters and particularly vascular filters for smaller blood vessels is determined by the relationship between the filter and the media being filtered. Blood is a complex suspension of different cell types that react differently to different stimuli. The defining geometric attributes of the filter structure will establish the filter's resistance to flow in any blood vessel. Ideally, all flow will be through the filter and will be exposed to minimal damage.
- All filters that do not have a sealing mechanism to divert flow only through it and will have some element of flow around it. We have configured the filter geometry such that flow through the filter is maximised and flow around the filter is minimised. Pressure drop across the face of the filter when related to the pressure drop through the alternate pathway will determine the filter efficiency.
- Related to the pressure drop, is the shear stress experienced by the blood elements. Red cells have an ability to deform under the influence of shear stresses. At low stresses (physiological) this deformation is recoverable. Additionally, a percentage of the red cell population is fragile and will fragment at low shear stress even in patients with “healthy” cell populations. While the body can deal with the rupture and fragmentation of small numbers of red blood cells, gross red blood cell damage are likely to be problematic clinically. Consideration must be given to the effects of the shear stresses, both the intensity and duration, on the constituent blood particles and the haemostatic mechanisms. It is the effects on the red blood cells and platelets that are of primary importance.
- Shear stresses can cause red cell destruction which is more pronounced in patients with red cell disorders, such as sickle cell disease. Haemolysis can lead to amaenia, which can impede oxygen transportation around the body, and in extreme cases causes damage to the kidneys, but this would be unlikely given the relatively short duration of deployment of vascular filters.
- More importantly though, shear stress also causes damage to the platelets themselves. Platelets play a key role in haemostasis and help orchestrate the complex cascade of events that lead to blood clot formation. The damage to the platelets causes communication chemicals to be released, and these “activate” other platelets in the vicinity. Once activated, the platelets swell and their surfaces become sticky, and this causes them to aggregate together and on available surfaces to form a “clump”. The released chemicals attract and activate other platelets in the area such that the clump grows in size. Fibrous proteins are also created and together a blood clot (thrombus) is formed. Depending on its size and position, the thrombus may occlude some of the holes in a vascular filter. It is also possible for the thrombus to become detached, particularly on removal of the device, and float freely away downstream to become an embolus. Should the embolus be large enough to become trapped in a narrow arterial vessel further along the system, flow in that vessel would be compromised and this could lead directly to stroke. Platelet aggregation occurs most effectively in stagnant and recirculating flow regions.
- It is also known that activated platelets can coat foreign bodies in the blood, such as intravasculature catheters. The foreign material surface then becomes sticky and therefore a site for further aggregation. This in turn could affect the local geometry of the device and the local flow characteristics.
- Shear may be expressed as follows:
-
Wall shear stress: τ=4μQ/πR 3 -
- Where μ is the blood viscosity
- Q is the mass flow rate
- R is the vessel radius
- In
FIG. 18 we show the relationship under specific flow conditions in a stated diameter of vessel. This plot assumes a Newtonian fluid, equal flow rate through each hole, a flow rate of 270 ml/min and a 4 mm blood vessel. - The relationship shows that as hole size decreases, then the required number of holes increases significantly.
- This representation of shear is a good general representation however, local conditions at the filter pores can have significant impact on the shear with flow irregularities generating the possibility of shear levels increasing by an order of magnitude. The location of the maximum shear stress is at the edges of the filter holes at their downstream side. The filter element of the invention has local radii and the filter entrance and exit holes to minimise the shear stress levels. Holes may be drilled using mechanical drilling or laser cutting. However, these processes can produce dimensionally repeatable holes but will impart surface conditions that are not suitable for small vessel filtration. Any fraying of edges due to mechanical cutting will certainly cause flow disruptions and form sites for platelet aggregation. Similarly laser cutting due to its local intense heating and vaporisation of the substrate will lead to pitting, surface inclusions, rough edges and surface imperfections.
- In the invention the holes are post processed to modify the surfaces and to radius the edges. A preferred embodiment of the filter element is manufactured using a medial grade polyurethane such as Chronoflex™ supplied by Cardiotech Inc. The filter holes are post-processed by solvent polishing using acetone or other suitable solvent.
- Referring in particular to
FIG. 17( a) there is illustrated a section of a polymeric filter body with a number of machined outlet holes 119. After solvent polishing the hoes are surface treated providing radiused lead-in and lead-out portions. - Solvent polishing of the membrane is achieved by softening the material in the surface lavers of the membrane such that a local reflow process is facilitated. This reflow is achieved using one of two classes of solvent.
-
- Solvents that have an ability to dissolve the polymer.
- Solvents that have an ability to swell the polymer.
- The process for the first class of solvents involves exposing the membrane to a limited amount of the solvent. This is achieved by dipping the membrane in the solvent for a short time or exposing the membrane to concentrated vapours of the solvent for a time. The solvent is absorbed into the surface layers and they become solubilised. The solubilised surface layers act like a viscous liquid and they adopt configurations of lowest surface energy. The lowest energy configuration for a liquid is a sphere. The sharp edges and corners become rounded by the solubilisation of the surface. The solvent is dried to reveal a smooth solvent polished surface.
- Swelling solvents act slightly differently in that they cannot dissolve the material. However their ability to swell the material allows similar reflow processes to occur. The key difference is that the membrane is immersed in the solvent for a longer period of time, preferably in excess of 30 minutes. The solvent swelling process is most effective when the membrane material is a two phase polymer such as a polyurethane or a PEBAX, as the solvent can be selected to match either phase.
- Solvents will dissolve polymers when their solubility parameters are similar. Solvents will swell a polymer when their solubility parameters are slightly different. Preferably the swelling solvent swells the material by less than 30%. Above this level the solvent should be considered dissolving solvent.
- Having reduced the local shear stresses as described above, it is then desirable to minimise the propensity for the activated platelets to adhere to the filter substrate. The more preferred embodiment of filter is one where the polished polymeric surface is combined with a coating on the substrate.
- The swelling of the polymer matrix reduces residual stresses that may have developed during the coated core drying or lasering processes. During the lasering process, the material in the immediate proximity of the lasered holes will have been exposed to heat. This heat will disrupt hard segment crystallites and they will reform to lower order meta-stable structures or be completely dissolved in the soft phase. The heat will also induce the soft segments to contract, however, the re-arrangement of the hard segments imposes new restrictions on the recovery of the soft segments to an equilibrium (relaxed) state. Thus, on removal of the heat source (laser), the morphology of the block copolymer will have changed, in the sense that the new configurations of the hard segments and soft segments will have been frozen in. After lasering, the holes have sharp and well-defined geometries. After exposing the coated material to the solvent, the solvent uncoils the soft segment chains and disassociates low ordered hard segment that are dissolved in the soft segment phase, so on removal of the solvent, the polymer matrix dries in a more relaxed state. In so doing, the sharp, well-defined walls of the lasered holes are transformed to a more contoured relaxed state.
- Such applicable solvents for this application, but not limited to, are 2-propanone, methyl ethyl ketone or trichloroethylene.
- The solvent characteristics are described as follows at room temperature:
-
- The solvent is organic, colourless and in a liquid state.
- The overall solubility parameter of the solvent is quoted between 16 to 26 Mpa0.5.
- The solvent is polar and is also capable of hydrogen bond interactions.
- On partitioning the overall solubility parameter of the solvent into dispersion, polar and hydrogen bonding components, the hydrogen bonding value (in its own solution) is quoted between 3 Mpa0.5 to 8.5 Mpa0.5.
- The solvent is infinitely miscible in water.
- The solvent is aprotic (proton acceptor) towards the formation of hydrogen bonding between it and the polymer.
- We have found that the optimum average diameter of the outlet holes in the polymeric membrane is from 100 to 200 microns, ideally approximately 150 microns. The number of holes in the
distal portion 213 is from 200 to 500, ideally about 300. This hole size and number of holes minimises shear levels by reducing localised flow rates. Thus, we have found that shear can be maintained below 800, preferably below 500 and ideally below 200 Pa at a blood flow rate of up to 270 ml/min in a 4 mm blood vessel. Ideally the holes are circular holes. - We have found that by maintaining blood shear below 800, preferably below 500 and ideally below 200 Pa, the filter provides appropriate haemodynamics to minimise turbulence and inappropriate shear stress on native arteries and veins. Damage to flowing blood such as haemolysis which involves the destruction of red blood cells by rupture of the cell envelope and release of contained haemoglobin is avoided. The outlet hole size and number of holes is optimised in order to capture embolic material, to allow the embolic material to be entrapped in the filter body and to be withdrawn through a delivery device such as a delivery catheter on collapsing of the filter body.
- Shearing of red blood and damage to platelets during filtration is a problem easily solved in extra-corporeal circuits by providing large filter areas with consequent low flow rates through individual pores controlled to flow rates such that the shear is maintained in ranges that are below known threshold levels with clinical relevance.
- However, as shear stress increases in inverse proportion to the cube of the radius, small blood vessels do not provide space in which to control shear levels by reducing localised flow rates. At flow rates up to 270 ml/min in a 4 mm blood vessel we have found that we can maintain shear at levels below 200 Pa with 150 micron holes.
- We have also found that the porosity of the distal end of the filter membrane and the arrangement of outlet holes is important in optimising capture of embolic material without adversely effecting blood shear characteristics and the material properties of the filter body which allow it to be collapsed for delivery, expanded for deployment and collapsed for retrieval.
- Referring in particular to
FIGS. 7 , 8 and especially 14(a) to 14(e) we have found that the overall porosity of the filter element is preferably between 5% and 40% and ideally between 8% and 21%. The transverse cross sectional areas of the filter body at longitudinally spaced-apart locations of the distal portion are substantially the same. Most importantly we have found that the porosity of the distal portion of the filter body should decrease towards the distal end. Arrangements ofdistal holes 119 for different filter diameters are shown inFIGS. 14( a) to 14(e).FIG. 14( a) shows an arrangement for a 6 mm filter, 14(b) for a 4 mm filter,FIG. 14( c) for a 4.5 mm filter,FIG. 14( d) for a 5 mm filter andFIG. 14( e) for a 5.5 mm filter. The number of outlet holes 119 also increases towards an outer edge of the distal portion of the filter body. - In addition we have found that for optimum capture of embolic material while facilitating retrieval of the filter with entrapped embolic material into a retrieval catheter the distal portion of the filter element includes a
blind section 130 adjacent the distal end of the filter element. Ideally theblind portion 130 extends longitudinally for at least 5% and preferably less than 30% of the length of the distal portion. - In order to reduce the profile of the filter body we have significantly reduced the thickness of the filter membrane to typically in the order of 25 microns. This reduction in thickness however means that the membrane used must have a relatively high stiffness to achieve a comparable strength. However, we have found that such an increase in stiffness results in poor memory performance and is therefore undesirable.
- We have surprisingly found that by providing a filter body of laminate construction in which a membrane is coated with a coating to a thickness of from 5% to 40% of the thickness of the membrane we have been able to provide a filter body which has a low profile but which has good memory characteristics.
- In particular, we have found that hydrophilic coatings and hydrogels are highly suitable coatings as they have a similar surface to the endothelial lining of a blood vessel and are not perceived by the body's immune system as foreign. This results in at least reduction and in some cases substantial elimination of platelet adhesion and fibrin build up which could otherwise occlude the filter and/or create a harmful thrombus. The coating also provide a relatively low friction surface between the filter body and the delicate endothelial lining of a vessel wall and therefore minimise the trauma and injury to a vessel wall caused by deployment of the filter body in the vasculature.
- A hydrogel will absorb water swelling its volume. The swelling of the hydrogel will exert an expansion force on the membrane helping to pull it into its recovered or deployed shape.
- A coating that expands on contact with blood will exert an expansion force on the membrane helping to pull it into its recovered or deployed shape.
- A coating that expands when subjected to body temperature will exert an expansion force on the membrane helping to pull it into its recovered or deployed shape.
- Hydrophilic coatings can be classified by their molecular structure:
-
- Linear Hydrophilic polymers can dissolve or be dispersed in water
- Cross-linked hydrophilic polymers, which include hydrogels, can swell and retain water.
- Hydrophilic coatings may be also synthetic or natural. Synthetic hydrophilic polymers include the following:
-
- Poly (2-hydroxy ethyl methacrylate)—(PHEMA)
- Poly (vinyl alcohol)—(PVA)
- Poly (ethylene oxide)—(PEO)
- Poly (carboxylic acids) including:
- Poly (acrylic acid)—(PAA)
- Poly (methacrylic acid)—(PMAA)
- Poly (N-vinyl-2-pyrollidone)—(PNVP)
- Poly (sulfonic acids), poly (acrylonitrile), poly (acrylamides)
- Natural hydrophylics include:
-
- Cellulose ethers
- Collagen
- Carrageenan
- Commercially available hydrophylic coatings suitable for coating filter membrane include, but are not limited to the following:
-
- Aquamer (Sky Polymers Inc.)
- Phosphoryicholine (PC) (Biocompatibiles Ltd)
- Surmodics (Surmodics Inc. BSI)
- Hydak (Biocoat Inc)
- Hydomer (Hydormer Inc)
- Hydrogels as stated are cross-linked hydrophilic molecules. The molecular mobility of hydrogels is constant and extensive, giving ceaseless molecular motion, which contributes to the property of biocompatibility by inhibiting protein absorption.
- The extent to which a hydrogel imparts properties of biocompatibility, wettability and lubricity is directly related to the amount of water it absorbs into its molecular matrix, which is referred to as the “degree of swelling”.
-
W=[(Wsw−Wo)/Wsw]×100 -
- Where Wsw =Weight of swollen gel
- Wo=Weight of dry gel
-
Water uptake=U=[(Wsw−Wo)/Wsw]×100 - A typical hydrogel will absorb up to 20% of their dry weight of water. Superabsorbant hydrogels will absorb up to 2000% of their dry weight of water.
- Hydrogel strength is directly related to cross link density (μ) and molecular weight between cross-links (Mc).
- Hydrophilic coatings may be typically applied by dipping, spraying and/or brushing. The coatings may also be applied by solution or by colloidal dispersion.
- The membrane surface to be coated may be prepared by cleaning with a solvent and/or ultrasonic cleaning. Plasma or corona discharge may also be used to increase the surface energy and thus provide for better adhesion.
- Alternatives to Hydrophilics include low friction fluoropolymer i.e. PTFE & FEP coatings that are chemically inert and have low coefficients of friction, which also helps prevent adhesion of platelets.
- Other coatings that rely on being chemically inert include:
-
- Poly-para-xylylene (Paralene N, C & D) made by Novatron Limited.
- Diamond like carbon.
- TetraCarbon (Medisyn Technologies Ltd.).
- Both diamond like carbon & tetracarbon also provide very thin hard surface layers, which help reduce the dynamic coefficient of friction for elastomers.
- The coating may be typically applied by dipping, spraying and/or brushing. The coatings may also be applied by solution or colloidal dispersion.
- Typically, to produce a filter according to the invention a polymeric filter membrane is first produced by machining a core of a desired shape from an inert material such as perspex. The perspex core is then dipped in a solution of a polymeric material as described above. Alternatively the membrane is formed by blow moulding. Holes are then laser machined in the dipped core. The perspex core is removed by dissolving in acetone. Residual acetone is washed out with water.
- A filter frame of gold plated Nitinol is mounted on a filter carrier in the form of a polyimide tube. The filter membrane is then slid over the filter support frame to provide an uncoated filter assembly.
- The filter assembly is dipped in a solvent such as propan 2-ol to clean the assembly. The cleaned assembly is then dipped in a solution of a coating material. A vacuum is applied to remove excess coating material prior to drying in an oven. The coating material is typically of Aquamer in a water/ethanol solution. The thickness of the coating is typically 2 to 10 microns.
- Preferably the filter body contains regions of varying stiffness and durometer hardness. The change in filter stiffness along its geometry can be achieved by varying the material properties or by modifications to the thickness or geometry of the membrane. The change in material hardness is achieved by varying the material properties. The polymer material may be one of the following: polyamides, polyurethanes, polyesters, a polyether block amide (PEBAX), olefinic elastomer, styrenic elastomer. Ideally the filter body has a durometer of between 60 D and 70 A Shore hardness.
- Referring to
FIG. 19 there is illustrated a filter element comprising afilter body 2 according to the invention. In this case, thefilter body 2 has aproximal section 3 and adistal section 4 interconnected by anintermediate section 5. Both theproximal section 3 and thedistal section 4 are made from a relatively stiff grade of polyurethane material which enables a low wall thickness to be achieved, thus advantageously minimising the bulk of the filter when it is in a collapsed position so that it has a low crossing profile while at the same time providing adequate strength. Theintermediate section 5 is made from a soft elastic grade of polyurethane having good shape memory characteristics which will help the filter maintain the desired expanded shape during use of the filter. This soft portion also allows one filter size to accommodate a range of vessel sizes conforming closely to the vessel wall to prevent blood and embolic material bypassing the filter. - In the
filter body 2 illustrated inFIG. 19 the body is of generally uniform thickness in cross section. However, to achieve any desired variation in the properties of the filter body the thickness may be variable such as in thefilter body 10 illustrated inFIG. 20 . - Referring to
FIGS. 21 to 25 , any required structural properties may also be provided by a filter body which is at least partially of a laminate construction. The layers of the laminate may be of the same or different materials. In the illustration ofFIG. 21 thedistal section 4 and part of theintermediate section 5 are of a twolayer lavers - The
layers distal section 4 are then formed by boring through the twolayers - In the illustration of
FIG. 22 theentire filter body 30 is of a threelayer Layer 31 is a structural layer made from a material such as polyether block amide (PEBAX), polyester, polyethylene, polyurethane, terephthalate (PET), or nylon.Layers Layers distal end 4 are also lined with the coating layers 32, 33. - When coating layers 32, 33 are of different materials, they are applied to
structural layer 31 as follows. A temporary protective film is first sealed to the outer most surface oflayer 31. Then coatinglayer 33 is applied to the inner most surface oflayer 31 by immersing the body formed bylayer 31 in a coating solution. Excess coating solution is sucked out and the protective film is removed from the outer most surface oflayer 31. Another temporary protective film is then sealed to the inner most surface oflayer 33. The body formed bylayers layer 33. - If the coating layers 32, 33 are of the same material, both
layers structural layer 31 in one step without the use of protective films. - In the illustration of
FIG. 23 theentire filter body 45 is of a threelayer Layers distal end 4 are also lined with thestructural layers - In the illustration of
FIG. 24 theentire filter body 50 is of a threelayer Layers - In the illustration of
FIG. 25 theentire filter body 55 is of a fourlayer Layers Layers distal end 4 are also lined with the coating layers 58, 59. - Referring to
FIG. 26 there is illustrated anotherfilter element 60 according to the invention, which is similar to part of thedistal section 4 offilter element 2 ofFIG. 19 . But having no proximal webbing members thus maximising the size of the inlet opening. -
FIG. 27 illustrates afilter element 61, which is similar to thedistal section 4 and part of theintermediate section 5 offilter element 20 ofFIG. 21 , having the advantages of the laminate structure previously described, combined with the large inlet opening ofFIG. 26 and the variable distal geometry ofFIG. 19 (enabling the filter to accommodate a range of vessel sizes). -
FIG. 28 illustrates afurther filter element 65, which includes asupport ring 66 to maintain theintermediate section 5 open to advancing blood flow.Support ring 66 may be arranged perpendicular to the direction of the blood flow or inclined at an angle, as illustrated inFIG. 28 . Thesupport ring 66 may be of an elastic, super elastic or shape memory material. and may be either actuated remotely to appose the vessel wall in a perpendicular or close to perpendicular position, or fixed in circumference so that its inclination and shape are controlled by the diameter of the vessel. - A different layer structure may be provided at any desired location of the filter body to achieve required properties.
- Referring now to
FIG. 29 there is shown another filter element according to the invention, indicated generally by thereference 70. Thefilter element 70 has afilter body 72 of generally similar construction to the filter element described previously, the body having aproximal section 73 and a distal section 74 interconnected by anintermediate section 75. In this case, the distal section 74 is of a relatively hard polyurethane material whilst theproximal section 73 andintermediate section 75 are of a softer grade polyurethane material. A number oflongitudinal ribs 76 are provided around a circumference of theproximal section 73. Advantageously, this construction facilitates close engagement of an outer circumference of theproximal section 73 against a vessel wall to minimise the risk of embolic material bypassing thefilter element 70. An internal support frame, as described above, urges theproximal section 73 outwardly so that it expands against and closely conforms with the wall of the blood vessel in which thefilter element 70 is mounted in use. - Conveniently, the corrugations or
ribs 76 allow theproximal section 73 of thefilter element 70 to accommodate a wider range of vessel sizes whilst maintaining good contact between the outer circumference of theproximal section 73 and the vessel wall and providing improved tilter body integrity. - Referring to
FIG. 30 there is illustrated anotherfilter element 80 according to the invention. In this case corrugations 81 are provided for improved filter body integrity. - Referring to
FIG. 31 there is illustrated anotherfilter element 82 according to the invention. In this case the cross section of thefilter element 82 is of a flower petal shape with a plurality of longitudinally extendingribs 83 for improved apposition. As explained in reference toFIG. 29 , the “petal shaped” cross section (as for corrugations) increase the circumference of the filter body, thus enabling the body to be apposed closely against the vessel wall by a supporting structure in a wide range of vessel sizes. - Referring to
FIG. 32 there is illustrated anotherfilter element 85 according to the invention. In this case slits 86 are provided in the place of the corrugations or “petal shapes” shown above. Theslits 86 enable the body of the filter to conform to a range of vessel diameters by overlapping and preventing creasing in small diameter vessels, or allowing the body to expand with the aid of a supporting structure in larger diameter vessels. In both instances close engagement of the outer circumference with the vessel wall is facilitated, thus minimizing the risk of embolic material bypassing the filter. - Referring to
FIG. 33 there is illustrated anotherfilter element 88 according to the invention. In thiscase ribs 89 are provided to prevent creases forming along thefilter element 88 in the longitudinal direction, and also to allow expansion of thefilter element 88. - Referring to
FIG. 34 there is illustrated afurther filter element 90 according to the invention, which is of a concertina-like shape with two circumferentially extendinggrooves 91, 92. This circumferential grooves or ribs have several advantages. They add to the integrity of the filter body, assisting it in maintaining its shape in the vessel after deployment. They inhibit the propagation of creases between the varying diameter body segments, so that one filter can be designed for a range of vessel sizes. They enable the filter to extend in length to greatly increase its effective volume without adding to the length of the deployed device in use. This provides the benefit of safe retrieval of large embolic loads as explained with reference to stretchable membranes below. - Referring to
FIGS. 35( a) to 35(d) there is illustrated another embolic protection system according to the invention incorporating afilter element 94 according to the invention which is similar to those described above. The protection system includes aguidewire 95 and aretrieval catheter 96 which is advanced over the guidewire to retrieve the filter containing trappedembolic material 97. In this case the filter body includes an intermediate 98 and distal 99 membrane, one or both of which are stretchable to facilitate the retrieval of the capturedembolic material 97. The stretching of the membrane during the retrieval process is illustrated inFIGS. 35( b) to 35(d). - The use of such a stretchable filter membrane allows larger volumes of captured embolic material to be retrieved than would be possible with a stiffer membrane. This is possible because if a filter is to be retrieved by withdrawing it into or through a catheter of a given internal diameter, the maximum volume of material that can be retrieved is directly proportional to the length of the filter and the internal diameter of the catheter. The stretchable membrane allows the filter to increase in length upon retrieval, thus increasing the space available for retention of captured embolic material. This is particularly significant in the case of large volumes of captured embolic material, which will be more difficult to safely retrieve with a non-stretchable device.
- The stretchable section may include some or all of the filter body, and may not necessarily include the distal cone. The distal cone containing the outlet pores may be formed from a non stretch material, while the inter mediate filter body is stretchable.
- This provides the advantage of filter extension during retrieval while preventing the problem of release of captured material through expanding distal pores.
- Another advantage of the stretchable section is that the crossing profile can be reduced as the filter can be loaded into a delivery pod in a stretched, rather than bunched or folded, configuration. This reduces the volume of filter material contained in any given cross section of the loaded delivery pod.
- In addition the use of a stretchable filter material in the intermediate section can also be advantageous by providing a section of the filter body which can be circumferentially expanded by a support frame to appose the wall of a wide range of vessel sizes.
- The invention is not limited to the embodiments hereinbefore described which may be varied in both construction and detail.
Claims (20)
1. A method for reducing thrombus formation during a medical procedure, comprising:
tracking an embolic protection device through a body lumen;
moving the embolic protection device from a first position to a second position, the second position configured to at least partially filter fluid passing through the embolic protection device, wherein a portion of the embolic protection device includes a coating disposed thereon, the coating adapted to reduce thrombus formation.
2. The method according to claim 1 , wherein the coating is selected from the group consisting of hydrophilic and hydrophobic coatings.
3. The method according to claim 2 , wherein the coating further includes a physiologically acceptable additive.
4. The method according to claim 3 , wherein the additive is heparin.
5. The method according to claim 2 , wherein the coating has a thickness between about 5% and 40% of a thickness of the embolic protection device.
6. The method according to claim 2 , wherein the coating is chosen from the group comprising, Poly(2-hydroxy ethyl methacrylate)—(PHEMA), Poly(vinyl alcohol)—(PVA), Poly (ethylene oxide)—(PEO), Poly (carboxylic acids), Poly (acrylic acid)—(PAA), Poly (methacrylic acid)—(PMAA), Poly (N-vinyl-2-pyrollidone)—(PNVP), Poly (sulfonic acids), poly (acrylonitrile), poly (acrylamides), Cellulose ethers, Collagen, Carrageenan, Aquamer (Sky Polymers Inc.), Phosphorylcholine (PC) (Biocompatibiles Ltd), Surmodics (Surmodics Inc. BSI), Hydak (Biocoat Inc), Hydomer (Hydormer Inc).
7. The method according to claim 1 , wherein the coating is configured to provide a low friction surface interaction between the filter body and a wall of a body lumen.
8. The method according to claim 1 , wherein the coating is at least partially composed of a non thrombogenic material and a fluropolymer material.
9. A method for reducing thrombus formation during a medical procedure, comprising:
tracking an expandable filter within a body lumen, the filter having a frame and a filtering element associated with the frame;
deploying the filter from a first position to a second position, wherein in the second position the filtering element opposes at least a portion of the body lumen:
passively filtering fluid through the filtering element, wherein the filtering element is further provided with a coating, the coating configured to mimic an inner surface of the body lumen.
10. The method according to claim 9 , wherein the coating comprises between about 5 percent to about 40 percent of the thickness of the filtering element.
11. The method according to claim 10 , wherein the filtering element comprises a flexible membrane having a plurality of apertures formed therein.
12. The method according to claim 9 , wherein the coating comprises a first component and a second component.
13. The method according to claim 12 , wherein the first component is chosen from the group consisting of hydrogels and hydrophilics; the second component is heprin.
14. The method according to claim 9 , wherein the coating is chosen from the group comprising, Poly(2-hydroxy ethyl methacrylate)—(PHEMA), Poly(vinyl alcohol)—(PVA), Poly (ethylene oxide)—(PEO), Poly (carboxylic acids), Poly (acrylic acid)—(PAA), Poly (methacrylic acid)—(PMAA), Poly (N-vinyl-2-pyrollidone)—(PNVP), Poly (sulfonic acids), poly (acrylonitrile), poly (acrylamides), Cellulose ethers, Collagen, Carrageenan, Aquamer (Sky Polymers Inc.), Phosphorylcholine (PC) (Biocompatibiles Ltd), Surmodics (Surmodics Inc. BSI), Hydak (Biocoat Inc), Hydomer (Hydormer Inc).
15. The method according to claim 9 , wherein the coating is configured to provide a low friction surface interaction between the filter body and a wall of a body lumen.
16. The method according to claim 9 , further including the step of moving the filter from the second position back to the first position, thereby entrapping any debris within the filtering element.
17. The method according to claim 9 , further including the step of performing a medical procedure after moving the filter from the first position to the second position.
18. A method for reducing thrombus formation during a medical procedure, comprising:
providing a collapsible filter element, the filter element having a filter body, the filter body being movable between a collapsed stored position and an expanded position for extension across a body lumen, a proximal inlet portion of the filter body having one or more openings sized to allow fluid and embolic material enter the filter body, at least one distal outlet opening sized to allow passage of fluid through the filter body, but to retain the embolic material within the filter body, the filter body comprising a membrane coating with a biocompatible coating, wherein the biocompatible coating is configured to reduce the formation of thrombus from fluid contact with the membrane;
expanding the filter body from the collapsed stored position to the expanded position; and
performing at least one medical procedure proximal to the filter body.
19. The method according to claim 18 , wherein the coating is chosen from the group comprising, Poly(2-hydroxy ethyl methacrylate)—(PHEMA), Poly(vinyl alcohol)—(PVA), poly (ethylene oxide)—(PEO), Poly (carboxylic acids), Poly (acrylic acid)—(PAA), Poly (methacrylic acid)—(PMAA), Poly (N-vinyl-2-pyrollidone)—(PNVP), Poly (sulfonic acids), poly (acrylonitrile), poly (acrylamides), Cellulose ethers, Collagen, Carrageenan, Aquamer (Sky Polymers Inc.), Phosphorylcholine (PC) (Biocompatibiles Ltd), Surmodics (Surmodics Inc. BSI), Hydak (Biocoat Inc), Hydomer (Hydormer Inc).
20. The method according to claim 18 , wherein the coating is configured to provide a low friction surface interaction between the filter body and a wall of a body lumen.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US11/562,720 US20080167677A1 (en) | 1999-05-07 | 2006-11-22 | Filter element for embolic protection device |
Applications Claiming Priority (7)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
IEPCT/IE99/00033 | 1999-05-07 | ||
IEPCT/IE99/00036 | 1999-05-07 | ||
PCT/IE1999/000033 WO2000067664A1 (en) | 1999-05-07 | 1999-05-07 | An embolic protection device |
PCT/IE1999/000036 WO2000067666A1 (en) | 1999-05-07 | 1999-05-07 | Improved filter element for embolic protection device |
PCT/IE2000/000053 WO2000067668A1 (en) | 1999-05-07 | 2000-05-08 | Improved filter element for embolic protection device |
US09/985,820 US7491215B2 (en) | 1999-05-07 | 2001-11-06 | Filter element for embolic protection device |
US11/562,720 US20080167677A1 (en) | 1999-05-07 | 2006-11-22 | Filter element for embolic protection device |
Related Parent Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US09/985,820 Continuation US7491215B2 (en) | 1999-05-07 | 2001-11-06 | Filter element for embolic protection device |
Publications (1)
Publication Number | Publication Date |
---|---|
US20080167677A1 true US20080167677A1 (en) | 2008-07-10 |
Family
ID=26320277
Family Applications (5)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US09/986,064 Expired - Lifetime US6726701B2 (en) | 1999-05-07 | 2001-11-07 | Embolic protection device |
US10/689,846 Abandoned US20040267302A1 (en) | 1999-05-07 | 2003-10-22 | Embolic protection device |
US11/529,525 Expired - Fee Related US8038697B2 (en) | 1999-05-07 | 2006-09-29 | Embolic protection device |
US11/562,720 Abandoned US20080167677A1 (en) | 1999-05-07 | 2006-11-22 | Filter element for embolic protection device |
US12/349,209 Abandoned US20090149881A1 (en) | 1999-05-07 | 2009-01-06 | Filter element for embolic protection device |
Family Applications Before (3)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US09/986,064 Expired - Lifetime US6726701B2 (en) | 1999-05-07 | 2001-11-07 | Embolic protection device |
US10/689,846 Abandoned US20040267302A1 (en) | 1999-05-07 | 2003-10-22 | Embolic protection device |
US11/529,525 Expired - Fee Related US8038697B2 (en) | 1999-05-07 | 2006-09-29 | Embolic protection device |
Family Applications After (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US12/349,209 Abandoned US20090149881A1 (en) | 1999-05-07 | 2009-01-06 | Filter element for embolic protection device |
Country Status (9)
Country | Link |
---|---|
US (5) | US6726701B2 (en) |
EP (2) | EP1176924B1 (en) |
JP (2) | JP2002543875A (en) |
AU (2) | AU4606400A (en) |
CA (1) | CA2384398A1 (en) |
DE (2) | DE20080298U1 (en) |
GB (1) | GB2365356A (en) |
IL (1) | IL145979A0 (en) |
WO (2) | WO2000067670A1 (en) |
Cited By (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20060229660A1 (en) * | 2005-03-15 | 2006-10-12 | Dharmendra Pal | Embolic protection device |
US20100191273A1 (en) * | 2009-01-23 | 2010-07-29 | Salviac Limited | Embolic protection device with no delivery catheter or retrieval catheter and methods of using the same |
Families Citing this family (317)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
WO1998039053A1 (en) * | 1997-03-06 | 1998-09-11 | Scimed Life Systems, Inc. | Distal protection device and method |
US6761727B1 (en) * | 1997-06-02 | 2004-07-13 | Medtronic Ave, Inc. | Filter assembly |
US7491216B2 (en) | 1997-11-07 | 2009-02-17 | Salviac Limited | Filter element with retractable guidewire tip |
EP1028670B1 (en) | 1997-11-07 | 2008-01-02 | Salviac Limited | An embolic protection device |
US7713282B2 (en) | 1998-11-06 | 2010-05-11 | Atritech, Inc. | Detachable atrial appendage occlusion balloon |
US7128073B1 (en) * | 1998-11-06 | 2006-10-31 | Ev3 Endovascular, Inc. | Method and device for left atrial appendage occlusion |
US7044134B2 (en) * | 1999-11-08 | 2006-05-16 | Ev3 Sunnyvale, Inc | Method of implanting a device in the left atrial appendage |
US20020138094A1 (en) * | 1999-02-12 | 2002-09-26 | Thomas Borillo | Vascular filter system |
US6171327B1 (en) | 1999-02-24 | 2001-01-09 | Scimed Life Systems, Inc. | Intravascular filter and method |
WO2000067665A1 (en) * | 1999-05-07 | 2000-11-16 | Salviac Limited | Support frame for embolic protection device |
US6918921B2 (en) | 1999-05-07 | 2005-07-19 | Salviac Limited | Support frame for an embolic protection device |
US6964672B2 (en) | 1999-05-07 | 2005-11-15 | Salviac Limited | Support frame for an embolic protection device |
DE20080298U1 (en) * | 1999-05-07 | 2001-12-20 | Salviac Ltd | Embolic protection device |
US7229462B2 (en) * | 1999-07-30 | 2007-06-12 | Angioguard, Inc. | Vascular filter system for carotid endarterectomy |
WO2001008742A1 (en) * | 1999-07-30 | 2001-02-08 | Incept Llc | Vascular filter having articulation region and methods of use in the ascending aorta |
US6544279B1 (en) | 2000-08-09 | 2003-04-08 | Incept, Llc | Vascular device for emboli, thrombus and foreign body removal and methods of use |
US7229463B2 (en) * | 1999-07-30 | 2007-06-12 | Angioguard, Inc. | Vascular filter system for cardiopulmonary bypass |
US8414543B2 (en) | 1999-10-22 | 2013-04-09 | Rex Medical, L.P. | Rotational thrombectomy wire with blocking device |
US6217589B1 (en) | 1999-10-27 | 2001-04-17 | Scimed Life Systems, Inc. | Retrieval device made of precursor alloy cable and method of manufacturing |
US6994092B2 (en) * | 1999-11-08 | 2006-02-07 | Ev3 Sunnyvale, Inc. | Device for containing embolic material in the LAA having a plurality of tissue retention structures |
US6575997B1 (en) | 1999-12-23 | 2003-06-10 | Endovascular Technologies, Inc. | Embolic basket |
US6402771B1 (en) | 1999-12-23 | 2002-06-11 | Guidant Endovascular Solutions | Snare |
US6660021B1 (en) | 1999-12-23 | 2003-12-09 | Advanced Cardiovascular Systems, Inc. | Intravascular device and system |
US6695813B1 (en) | 1999-12-30 | 2004-02-24 | Advanced Cardiovascular Systems, Inc. | Embolic protection devices |
US7918820B2 (en) | 1999-12-30 | 2011-04-05 | Advanced Cardiovascular Systems, Inc. | Device for, and method of, blocking emboli in vessels such as blood arteries |
GB2369575A (en) | 2000-04-20 | 2002-06-05 | Salviac Ltd | An embolic protection system |
US6520978B1 (en) | 2000-05-15 | 2003-02-18 | Intratherapeutics, Inc. | Emboli filter |
US6565591B2 (en) * | 2000-06-23 | 2003-05-20 | Salviac Limited | Medical device |
DE10191982T1 (en) * | 2000-06-23 | 2003-11-06 | Salviac Ltd | Filter element for embolic protection device |
US6964670B1 (en) | 2000-07-13 | 2005-11-15 | Advanced Cardiovascular Systems, Inc. | Embolic protection guide wire |
US6656202B2 (en) | 2000-07-14 | 2003-12-02 | Advanced Cardiovascular Systems, Inc. | Embolic protection systems |
US6875197B1 (en) * | 2000-11-14 | 2005-04-05 | Advanced Cardiovascular Systems, Inc. | Dimensionally stable and growth controlled inflatable member for a catheter |
WO2002043595A2 (en) * | 2000-11-28 | 2002-06-06 | Advanced Cardiovascular Systems, Inc. | Embolic protection devices |
US6506203B1 (en) | 2000-12-19 | 2003-01-14 | Advanced Cardiovascular Systems, Inc. | Low profile sheathless embolic protection system |
DE10105592A1 (en) | 2001-02-06 | 2002-08-08 | Achim Goepferich | Placeholder for drug release in the frontal sinus |
US6974468B2 (en) | 2001-02-28 | 2005-12-13 | Scimed Life Systems, Inc. | Filter retrieval catheter |
US6599307B1 (en) * | 2001-06-29 | 2003-07-29 | Advanced Cardiovascular Systems, Inc. | Filter device for embolic protection systems |
US7338510B2 (en) | 2001-06-29 | 2008-03-04 | Advanced Cardiovascular Systems, Inc. | Variable thickness embolic filtering devices and method of manufacturing the same |
US6638294B1 (en) | 2001-08-30 | 2003-10-28 | Advanced Cardiovascular Systems, Inc. | Self furling umbrella frame for carotid filter |
US6592606B2 (en) | 2001-08-31 | 2003-07-15 | Advanced Cardiovascular Systems, Inc. | Hinged short cage for an embolic protection device |
US7097651B2 (en) * | 2001-09-06 | 2006-08-29 | Advanced Cardiovascular Systems, Inc. | Embolic protection basket |
US8262689B2 (en) | 2001-09-28 | 2012-09-11 | Advanced Cardiovascular Systems, Inc. | Embolic filtering devices |
US20030078614A1 (en) * | 2001-10-18 | 2003-04-24 | Amr Salahieh | Vascular embolic filter devices and methods of use therefor |
US6887257B2 (en) | 2001-10-19 | 2005-05-03 | Incept Llc | Vascular embolic filter exchange devices and methods of use thereof |
US7241304B2 (en) | 2001-12-21 | 2007-07-10 | Advanced Cardiovascular Systems, Inc. | Flexible and conformable embolic filtering devices |
WO2003055413A2 (en) | 2001-12-21 | 2003-07-10 | Salviac Limited | A support frame for an embolic protection device |
US7118539B2 (en) * | 2002-02-26 | 2006-10-10 | Scimed Life Systems, Inc. | Articulating guide wire for embolic protection and methods of use |
US20030187495A1 (en) | 2002-04-01 | 2003-10-02 | Cully Edward H. | Endoluminal devices, embolic filters, methods of manufacture and use |
AU2003231886A1 (en) * | 2002-05-13 | 2003-11-11 | Salviac Limited | Retrieval catheter for an embolic filter |
US7303575B2 (en) * | 2002-08-01 | 2007-12-04 | Lumen Biomedical, Inc. | Embolism protection devices |
AU2003209629A1 (en) | 2002-08-05 | 2004-02-23 | Gil Ofir | Embolism filter with self-deployable guidewire stop |
US8114114B2 (en) | 2002-08-27 | 2012-02-14 | Emboline, Inc. | Embolic protection device |
US8317816B2 (en) | 2002-09-30 | 2012-11-27 | Acclarent, Inc. | Balloon catheters and methods for treating paranasal sinuses |
US7252675B2 (en) | 2002-09-30 | 2007-08-07 | Advanced Cardiovascular, Inc. | Embolic filtering devices |
US7331973B2 (en) | 2002-09-30 | 2008-02-19 | Avdanced Cardiovascular Systems, Inc. | Guide wire with embolic filtering attachment |
US20040093012A1 (en) | 2002-10-17 | 2004-05-13 | Cully Edward H. | Embolic filter frame having looped support strut elements |
US7481823B2 (en) * | 2002-10-25 | 2009-01-27 | Boston Scientific Scimed, Inc. | Multiple membrane embolic protection filter |
US20040088000A1 (en) | 2002-10-31 | 2004-05-06 | Muller Paul F. | Single-wire expandable cages for embolic filtering devices |
US20040111111A1 (en) * | 2002-12-10 | 2004-06-10 | Scimed Life Systems, Inc. | Intravascular filter membrane with shape memory |
US20040138694A1 (en) * | 2003-01-15 | 2004-07-15 | Scimed Life Systems, Inc. | Intravascular filtering membrane and method of making an embolic protection filter device |
US20040153119A1 (en) * | 2003-01-30 | 2004-08-05 | Kusleika Richard S. | Embolic filters with a distal loop or no loop |
US7323001B2 (en) | 2003-01-30 | 2008-01-29 | Ev3 Inc. | Embolic filters with controlled pore size |
US7220271B2 (en) | 2003-01-30 | 2007-05-22 | Ev3 Inc. | Embolic filters having multiple layers and controlled pore size |
US7740644B2 (en) | 2003-02-24 | 2010-06-22 | Boston Scientific Scimed, Inc. | Embolic protection filtering device that can be adapted to be advanced over a guidewire |
US6878291B2 (en) | 2003-02-24 | 2005-04-12 | Scimed Life Systems, Inc. | Flexible tube for cartridge filter |
US8591540B2 (en) | 2003-02-27 | 2013-11-26 | Abbott Cardiovascular Systems Inc. | Embolic filtering devices |
ATE416717T1 (en) * | 2003-03-17 | 2008-12-15 | Ev3 Endovascular Inc | STENT WITH LAMINATED THIN FILM COMPOSITE |
US7597704B2 (en) * | 2003-04-28 | 2009-10-06 | Atritech, Inc. | Left atrial appendage occlusion device with active expansion |
US7604649B2 (en) * | 2003-04-29 | 2009-10-20 | Rex Medical, L.P. | Distal protection device |
US7331976B2 (en) * | 2003-04-29 | 2008-02-19 | Rex Medical, L.P. | Distal protection device |
US20040249409A1 (en) * | 2003-06-09 | 2004-12-09 | Scimed Life Systems, Inc. | Reinforced filter membrane |
US7879062B2 (en) * | 2003-07-22 | 2011-02-01 | Lumen Biomedical, Inc. | Fiber based embolism protection device |
US9301829B2 (en) | 2003-07-30 | 2016-04-05 | Boston Scientific Scimed, Inc. | Embolic protection aspirator |
US7735493B2 (en) | 2003-08-15 | 2010-06-15 | Atritech, Inc. | System and method for delivering a left atrial appendage containment device |
US7763063B2 (en) | 2003-09-03 | 2010-07-27 | Bolton Medical, Inc. | Self-aligning stent graft delivery system, kit, and method |
US20080264102A1 (en) | 2004-02-23 | 2008-10-30 | Bolton Medical, Inc. | Sheath Capture Device for Stent Graft Delivery System and Method for Operating Same |
US8292943B2 (en) | 2003-09-03 | 2012-10-23 | Bolton Medical, Inc. | Stent graft with longitudinal support member |
US11259945B2 (en) | 2003-09-03 | 2022-03-01 | Bolton Medical, Inc. | Dual capture device for stent graft delivery system and method for capturing a stent graft |
US11596537B2 (en) | 2003-09-03 | 2023-03-07 | Bolton Medical, Inc. | Delivery system and method for self-centering a proximal end of a stent graft |
US7056286B2 (en) | 2003-11-12 | 2006-06-06 | Adrian Ravenscroft | Medical device anchor and delivery system |
US7892251B1 (en) | 2003-11-12 | 2011-02-22 | Advanced Cardiovascular Systems, Inc. | Component for delivering and locking a medical device to a guide wire |
US7988705B2 (en) * | 2004-03-06 | 2011-08-02 | Lumen Biomedical, Inc. | Steerable device having a corewire within a tube and combination with a functional medical component |
US20080228209A1 (en) * | 2004-03-08 | 2008-09-18 | Demello Richard M | System and method for removal of material from a blood vessel using a small diameter catheter |
US7473265B2 (en) * | 2004-03-15 | 2009-01-06 | Boston Scientific Scimed, Inc. | Filter media and methods of manufacture |
US7678129B1 (en) | 2004-03-19 | 2010-03-16 | Advanced Cardiovascular Systems, Inc. | Locking component for an embolic filter assembly |
US7559925B2 (en) | 2006-09-15 | 2009-07-14 | Acclarent Inc. | Methods and devices for facilitating visualization in a surgical environment |
US10188413B1 (en) | 2004-04-21 | 2019-01-29 | Acclarent, Inc. | Deflectable guide catheters and related methods |
US9351750B2 (en) * | 2004-04-21 | 2016-05-31 | Acclarent, Inc. | Devices and methods for treating maxillary sinus disease |
US8894614B2 (en) | 2004-04-21 | 2014-11-25 | Acclarent, Inc. | Devices, systems and methods useable for treating frontal sinusitis |
US20060063973A1 (en) | 2004-04-21 | 2006-03-23 | Acclarent, Inc. | Methods and apparatus for treating disorders of the ear, nose and throat |
US20060004323A1 (en) | 2004-04-21 | 2006-01-05 | Exploramed Nc1, Inc. | Apparatus and methods for dilating and modifying ostia of paranasal sinuses and other intranasal or paranasal structures |
US7410480B2 (en) | 2004-04-21 | 2008-08-12 | Acclarent, Inc. | Devices and methods for delivering therapeutic substances for the treatment of sinusitis and other disorders |
US9101384B2 (en) | 2004-04-21 | 2015-08-11 | Acclarent, Inc. | Devices, systems and methods for diagnosing and treating sinusitis and other disorders of the ears, Nose and/or throat |
US9399121B2 (en) | 2004-04-21 | 2016-07-26 | Acclarent, Inc. | Systems and methods for transnasal dilation of passageways in the ear, nose or throat |
US20190314620A1 (en) | 2004-04-21 | 2019-10-17 | Acclarent, Inc. | Apparatus and methods for dilating and modifying ostia of paranasal sinuses and other intranasal or paranasal structures |
US20070208252A1 (en) * | 2004-04-21 | 2007-09-06 | Acclarent, Inc. | Systems and methods for performing image guided procedures within the ear, nose, throat and paranasal sinuses |
US8702626B1 (en) | 2004-04-21 | 2014-04-22 | Acclarent, Inc. | Guidewires for performing image guided procedures |
US8864787B2 (en) | 2004-04-21 | 2014-10-21 | Acclarent, Inc. | Ethmoidotomy system and implantable spacer devices having therapeutic substance delivery capability for treatment of paranasal sinusitis |
US9554691B2 (en) | 2004-04-21 | 2017-01-31 | Acclarent, Inc. | Endoscopic methods and devices for transnasal procedures |
US8764729B2 (en) | 2004-04-21 | 2014-07-01 | Acclarent, Inc. | Frontal sinus spacer |
US7361168B2 (en) | 2004-04-21 | 2008-04-22 | Acclarent, Inc. | Implantable device and methods for delivering drugs and other substances to treat sinusitis and other disorders |
US7803150B2 (en) | 2004-04-21 | 2010-09-28 | Acclarent, Inc. | Devices, systems and methods useable for treating sinusitis |
US8146400B2 (en) | 2004-04-21 | 2012-04-03 | Acclarent, Inc. | Endoscopic methods and devices for transnasal procedures |
US8932276B1 (en) | 2004-04-21 | 2015-01-13 | Acclarent, Inc. | Shapeable guide catheters and related methods |
US8747389B2 (en) | 2004-04-21 | 2014-06-10 | Acclarent, Inc. | Systems for treating disorders of the ear, nose and throat |
US7462175B2 (en) | 2004-04-21 | 2008-12-09 | Acclarent, Inc. | Devices, systems and methods for treating disorders of the ear, nose and throat |
US20070167682A1 (en) | 2004-04-21 | 2007-07-19 | Acclarent, Inc. | Endoscopic methods and devices for transnasal procedures |
US7419497B2 (en) | 2004-04-21 | 2008-09-02 | Acclarent, Inc. | Methods for treating ethmoid disease |
US9089258B2 (en) | 2004-04-21 | 2015-07-28 | Acclarent, Inc. | Endoscopic methods and devices for transnasal procedures |
US7654997B2 (en) | 2004-04-21 | 2010-02-02 | Acclarent, Inc. | Devices, systems and methods for diagnosing and treating sinusitus and other disorders of the ears, nose and/or throat |
US8801746B1 (en) | 2004-05-04 | 2014-08-12 | Covidien Lp | System and method for delivering a left atrial appendage containment device |
EP1788978B1 (en) * | 2004-09-17 | 2011-11-09 | Codman & Shurtleff, Inc. | Thin film devices for temporary or permanent occlusion of a vessel |
WO2006034074A1 (en) * | 2004-09-17 | 2006-03-30 | Nitinol Development Corporation | Shape memory thin film embolic protection device |
ATE520369T1 (en) * | 2004-09-17 | 2011-09-15 | Nitinol Dev Corp | SHAPE MEMORY THIN FILM EMBOLIC PROTECTION DEVICE |
WO2006042114A1 (en) | 2004-10-06 | 2006-04-20 | Cook, Inc. | Emboli capturing device having a coil and method for capturing emboli |
US20060079863A1 (en) * | 2004-10-08 | 2006-04-13 | Scimed Life Systems, Inc. | Medical devices coated with diamond-like carbon |
JP4913062B2 (en) * | 2004-10-15 | 2012-04-11 | コーディス・ニューロバスキュラー・インコーポレイテッド | Aneurysm remodeling instrument |
US20060095067A1 (en) * | 2004-11-01 | 2006-05-04 | Horng-Ban Lin | Lubricious filter |
US20060184194A1 (en) * | 2005-02-15 | 2006-08-17 | Cook Incorporated | Embolic protection device |
WO2006089178A2 (en) | 2005-02-18 | 2006-08-24 | Ev3 Inc. | Rapid exchange catheters and embolic protection devices |
US8945169B2 (en) | 2005-03-15 | 2015-02-03 | Cook Medical Technologies Llc | Embolic protection device |
US9259305B2 (en) | 2005-03-31 | 2016-02-16 | Abbott Cardiovascular Systems Inc. | Guide wire locking mechanism for rapid exchange and other catheter systems |
US8951225B2 (en) | 2005-06-10 | 2015-02-10 | Acclarent, Inc. | Catheters with non-removable guide members useable for treatment of sinusitis |
US7850708B2 (en) | 2005-06-20 | 2010-12-14 | Cook Incorporated | Embolic protection device having a reticulated body with staggered struts |
US8109962B2 (en) | 2005-06-20 | 2012-02-07 | Cook Medical Technologies Llc | Retrievable device having a reticulation portion with staggered struts |
US7771452B2 (en) | 2005-07-12 | 2010-08-10 | Cook Incorporated | Embolic protection device with a filter bag that disengages from a basket |
US7766934B2 (en) | 2005-07-12 | 2010-08-03 | Cook Incorporated | Embolic protection device with an integral basket and bag |
US8187298B2 (en) | 2005-08-04 | 2012-05-29 | Cook Medical Technologies Llc | Embolic protection device having inflatable frame |
US8377092B2 (en) | 2005-09-16 | 2013-02-19 | Cook Medical Technologies Llc | Embolic protection device |
US7972359B2 (en) | 2005-09-16 | 2011-07-05 | Atritech, Inc. | Intracardiac cage and method of delivering same |
US7816975B2 (en) * | 2005-09-20 | 2010-10-19 | Hewlett-Packard Development Company, L.P. | Circuit and method for bias voltage generation |
US8114113B2 (en) | 2005-09-23 | 2012-02-14 | Acclarent, Inc. | Multi-conduit balloon catheter |
US8632562B2 (en) | 2005-10-03 | 2014-01-21 | Cook Medical Technologies Llc | Embolic protection device |
US8182508B2 (en) | 2005-10-04 | 2012-05-22 | Cook Medical Technologies Llc | Embolic protection device |
US8252017B2 (en) | 2005-10-18 | 2012-08-28 | Cook Medical Technologies Llc | Invertible filter for embolic protection |
US8216269B2 (en) | 2005-11-02 | 2012-07-10 | Cook Medical Technologies Llc | Embolic protection device having reduced profile |
US9440003B2 (en) * | 2005-11-04 | 2016-09-13 | Boston Scientific Scimed, Inc. | Medical devices having particle-containing regions with diamond-like coatings |
US8152831B2 (en) | 2005-11-17 | 2012-04-10 | Cook Medical Technologies Llc | Foam embolic protection device |
US20070135826A1 (en) * | 2005-12-01 | 2007-06-14 | Steve Zaver | Method and apparatus for delivering an implant without bias to a left atrial appendage |
WO2007133366A2 (en) | 2006-05-02 | 2007-11-22 | C. R. Bard, Inc. | Vena cava filter formed from a sheet |
US20070265655A1 (en) * | 2006-05-09 | 2007-11-15 | Boston Scientific Scimed, Inc. | Embolic protection filter with enhanced stability within a vessel |
US8190389B2 (en) | 2006-05-17 | 2012-05-29 | Acclarent, Inc. | Adapter for attaching electromagnetic image guidance components to a medical device |
DE102006024176B4 (en) | 2006-05-23 | 2008-08-28 | Pah, Gunnar M. | A device for filtering blood in the removal of heart valve stenosis and methods for eliminating heart valve stenosis |
US20070299456A1 (en) * | 2006-06-06 | 2007-12-27 | Teague James A | Light responsive medical retrieval devices |
US20090317443A1 (en) * | 2006-07-14 | 2009-12-24 | Biocompatibles Uk Limited Chapman House | Coated implant |
US9820688B2 (en) | 2006-09-15 | 2017-11-21 | Acclarent, Inc. | Sinus illumination lightwire device |
US20080071307A1 (en) | 2006-09-19 | 2008-03-20 | Cook Incorporated | Apparatus and methods for in situ embolic protection |
WO2008039684A2 (en) * | 2006-09-20 | 2008-04-03 | Peacock James C | Embolic filter device and related systems and methods |
US9149609B2 (en) * | 2006-10-16 | 2015-10-06 | Embolitech, Llc | Catheter for removal of an organized embolic thrombus |
WO2008066881A1 (en) | 2006-11-29 | 2008-06-05 | Amir Belson | Embolic protection device |
US20080147110A1 (en) * | 2006-12-19 | 2008-06-19 | Lalith Hiran Wijeratne | Embolic protection device with distal tubular member for improved torque response |
US8439687B1 (en) | 2006-12-29 | 2013-05-14 | Acclarent, Inc. | Apparatus and method for simulated insertion and positioning of guidewares and other interventional devices |
US8814930B2 (en) | 2007-01-19 | 2014-08-26 | Elixir Medical Corporation | Biodegradable endoprosthesis and methods for their fabrication |
US9901434B2 (en) | 2007-02-27 | 2018-02-27 | Cook Medical Technologies Llc | Embolic protection device including a Z-stent waist band |
ATE526888T1 (en) * | 2007-03-08 | 2011-10-15 | Boston Scient Ltd | SYSTEM FOR DELIVERING A DETACHABLE IMPLANTABLE PRODUCT |
US8118757B2 (en) | 2007-04-30 | 2012-02-21 | Acclarent, Inc. | Methods and devices for ostium measurement |
US8485199B2 (en) | 2007-05-08 | 2013-07-16 | Acclarent, Inc. | Methods and devices for protecting nasal turbinate during surgery |
US8216209B2 (en) | 2007-05-31 | 2012-07-10 | Abbott Cardiovascular Systems Inc. | Method and apparatus for delivering an agent to a kidney |
US7867273B2 (en) | 2007-06-27 | 2011-01-11 | Abbott Laboratories | Endoprostheses for peripheral arteries and other body vessels |
US8795318B2 (en) * | 2007-09-07 | 2014-08-05 | Merit Medical Systems, Inc. | Percutaneous retrievable vascular filter |
WO2009032834A1 (en) * | 2007-09-07 | 2009-03-12 | Crusader Medical Llc | Percutaneous permanent retrievable vascular filter |
US8419748B2 (en) | 2007-09-14 | 2013-04-16 | Cook Medical Technologies Llc | Helical thrombus removal device |
US9138307B2 (en) | 2007-09-14 | 2015-09-22 | Cook Medical Technologies Llc | Expandable device for treatment of a stricture in a body vessel |
US8252018B2 (en) | 2007-09-14 | 2012-08-28 | Cook Medical Technologies Llc | Helical embolic protection device |
US9220522B2 (en) | 2007-10-17 | 2015-12-29 | Covidien Lp | Embolus removal systems with baskets |
US20090105746A1 (en) * | 2007-10-17 | 2009-04-23 | Gardia Medical Ltd | Guidewire stop |
US7819844B2 (en) * | 2007-10-17 | 2010-10-26 | Gardia Medical Ltd. | Guidewire stop |
EP2211972B1 (en) * | 2007-10-26 | 2015-12-23 | Embolitech, LLC | Intravascular guidewire filter system for pulmonary embolism protection and embolism removal or maceration |
DE102007056946A1 (en) | 2007-11-27 | 2009-05-28 | Gunnar Pah | Device for filtering blood |
US10206821B2 (en) | 2007-12-20 | 2019-02-19 | Acclarent, Inc. | Eustachian tube dilation balloon with ventilation path |
US8182432B2 (en) | 2008-03-10 | 2012-05-22 | Acclarent, Inc. | Corewire design and construction for medical devices |
BRPI0913877A2 (en) | 2008-06-30 | 2015-10-27 | Bolton Medical Inc | abdominal aortic aneurysms: systems and methods of use |
US8070694B2 (en) | 2008-07-14 | 2011-12-06 | Medtronic Vascular, Inc. | Fiber based medical devices and aspiration catheters |
US9402707B2 (en) | 2008-07-22 | 2016-08-02 | Neuravi Limited | Clot capture systems and associated methods |
CN102112040B (en) | 2008-07-30 | 2015-04-01 | 阿克拉伦特公司 | Paranasal ostium finder devices and methods |
CN103623498B (en) | 2008-09-18 | 2015-12-30 | 阿克拉伦特公司 | Be used for the treatment of the method and apparatus of otorhinolaryngology disease |
US8388644B2 (en) | 2008-12-29 | 2013-03-05 | Cook Medical Technologies Llc | Embolic protection device and method of use |
US20170202657A1 (en) | 2009-01-16 | 2017-07-20 | Claret Medical, Inc. | Intravascular blood filters and methods of use |
ES2516066T3 (en) | 2009-01-16 | 2014-10-30 | Claret Medical, Inc. | Intravascular blood filter |
US9326843B2 (en) | 2009-01-16 | 2016-05-03 | Claret Medical, Inc. | Intravascular blood filters and methods of use |
WO2010088520A2 (en) * | 2009-01-29 | 2010-08-05 | Claret Medical, Inc. | Illuminated intravascular blood filter |
US20100241155A1 (en) | 2009-03-20 | 2010-09-23 | Acclarent, Inc. | Guide system with suction |
US8435290B2 (en) | 2009-03-31 | 2013-05-07 | Acclarent, Inc. | System and method for treatment of non-ventilating middle ear by providing a gas pathway through the nasopharynx |
US7978742B1 (en) | 2010-03-24 | 2011-07-12 | Corning Incorporated | Methods for operating diode lasers |
US8974489B2 (en) | 2009-07-27 | 2015-03-10 | Claret Medical, Inc. | Dual endovascular filter and methods of use |
EP3300691B1 (en) | 2009-09-21 | 2021-06-30 | Boston Scientific Scimed, Inc. | Intravascular blood filters |
US8298258B2 (en) * | 2009-10-05 | 2012-10-30 | Boston Scientific Scimed, Inc | Embolic protection device |
WO2011056981A2 (en) | 2009-11-04 | 2011-05-12 | Nitinol Devices And Components, Inc. | Alternating circumferential bridge stent design and methods for use thereof |
JP5668192B2 (en) * | 2010-03-10 | 2015-02-12 | 株式会社ライトニックス | Medical needle and puncture device |
US9155492B2 (en) | 2010-09-24 | 2015-10-13 | Acclarent, Inc. | Sinus illumination lightwire device |
WO2012047308A1 (en) | 2010-10-08 | 2012-04-12 | Nitinol Devices And Components, Inc. | Alternating circumferential bridge stent design and methods for use thereof |
US9463036B2 (en) | 2010-10-22 | 2016-10-11 | Neuravi Limited | Clot engagement and removal system |
US8756789B2 (en) | 2010-11-16 | 2014-06-24 | W. L. Gore & Associates, Inc. | Method of manufacturing a catheter assembly |
US8876796B2 (en) | 2010-12-30 | 2014-11-04 | Claret Medical, Inc. | Method of accessing the left common carotid artery |
US11259824B2 (en) | 2011-03-09 | 2022-03-01 | Neuravi Limited | Clot retrieval device for removing occlusive clot from a blood vessel |
ES2871050T3 (en) | 2011-03-09 | 2021-10-28 | Neuravi Ltd | A clot retrieval device to remove the occlusive clot from a blood vessel |
US8740931B2 (en) | 2011-08-05 | 2014-06-03 | Merit Medical Systems, Inc. | Vascular filter |
EP4101399A1 (en) | 2011-08-05 | 2022-12-14 | Route 92 Medical, Inc. | System for treatment of acute ischemic stroke |
US8734480B2 (en) | 2011-08-05 | 2014-05-27 | Merit Medical Systems, Inc. | Vascular filter |
US8617200B2 (en) * | 2011-08-17 | 2013-12-31 | Cook Medical Technologies Llc | Multi-layer filtration device |
WO2013071173A1 (en) * | 2011-11-11 | 2013-05-16 | Dacuycuy Nathan John | Devices for removing vessel occlusions |
ES2625629T7 (en) | 2011-11-16 | 2017-12-19 | Bolton Medical Inc. | Device for the repair of the bifurcated aortic vessel |
US9492265B2 (en) | 2012-01-06 | 2016-11-15 | Emboline, Inc. | Integrated embolic protection devices |
WO2013126773A1 (en) | 2012-02-23 | 2013-08-29 | Merit Medical Systems, Inc. | Vascular filter |
US10213288B2 (en) * | 2012-03-06 | 2019-02-26 | Crux Biomedical, Inc. | Distal protection filter |
JP2015520637A (en) * | 2012-05-08 | 2015-07-23 | ザ・キュレイターズ・オブ・ザ・ユニバーシティー・オブ・ミズーリThe Curators Of The University Of Missouri | Embolic protection system |
US9603693B2 (en) * | 2012-08-10 | 2017-03-28 | W. L. Gore & Associates, Inc. | Dual net vascular filtration devices and related systems and methods |
US9204887B2 (en) | 2012-08-14 | 2015-12-08 | W. L. Gore & Associates, Inc. | Devices and systems for thrombus treatment |
US9456834B2 (en) | 2012-10-31 | 2016-10-04 | Covidien Lp | Thrombectomy device with distal protection |
AU2013361551B2 (en) * | 2012-12-21 | 2018-03-22 | The Regents Of The University Of California | In vivo positionable filtration devices and methods related thereto |
US9642635B2 (en) | 2013-03-13 | 2017-05-09 | Neuravi Limited | Clot removal device |
US9433429B2 (en) | 2013-03-14 | 2016-09-06 | Neuravi Limited | Clot retrieval devices |
CN109157304B (en) | 2013-03-14 | 2021-12-31 | 尼尔拉维有限公司 | A clot retrieval device for removing a clogged clot from a blood vessel |
SI2967611T1 (en) | 2013-03-14 | 2019-04-30 | Neuravi Limited | Devices for removal of acute blockages from blood vessels |
US9433437B2 (en) | 2013-03-15 | 2016-09-06 | Acclarent, Inc. | Apparatus and method for treatment of ethmoid sinusitis |
US9629684B2 (en) | 2013-03-15 | 2017-04-25 | Acclarent, Inc. | Apparatus and method for treatment of ethmoid sinusitis |
US9439751B2 (en) | 2013-03-15 | 2016-09-13 | Bolton Medical, Inc. | Hemostasis valve and delivery systems |
US9402708B2 (en) | 2013-07-25 | 2016-08-02 | Covidien Lp | Vascular devices and methods with distal protection |
WO2015021296A1 (en) | 2013-08-09 | 2015-02-12 | Merit Medical Systems, Inc. | Vascular filter delivery systems and methods |
US10286190B2 (en) | 2013-12-11 | 2019-05-14 | Cook Medical Technologies Llc | Balloon catheter with dynamic vessel engaging member |
US9265512B2 (en) | 2013-12-23 | 2016-02-23 | Silk Road Medical, Inc. | Transcarotid neurovascular catheter |
US9782247B2 (en) * | 2014-02-18 | 2017-10-10 | Cook Medical Technologies, LLC | Flexible embolic double filter |
US10285720B2 (en) | 2014-03-11 | 2019-05-14 | Neuravi Limited | Clot retrieval system for removing occlusive clot from a blood vessel |
US9820761B2 (en) | 2014-03-21 | 2017-11-21 | Route 92 Medical, Inc. | Rapid aspiration thrombectomy system and method |
US10792056B2 (en) | 2014-06-13 | 2020-10-06 | Neuravi Limited | Devices and methods for removal of acute blockages from blood vessels |
US10441301B2 (en) | 2014-06-13 | 2019-10-15 | Neuravi Limited | Devices and methods for removal of acute blockages from blood vessels |
US9579427B2 (en) * | 2014-06-28 | 2017-02-28 | Cordis Corporation | Thin-film composite retrievable endovascular devices and method of use |
US10265086B2 (en) | 2014-06-30 | 2019-04-23 | Neuravi Limited | System for removing a clot from a blood vessel |
US9259339B1 (en) | 2014-08-15 | 2016-02-16 | Elixir Medical Corporation | Biodegradable endoprostheses and methods of their fabrication |
US9855156B2 (en) * | 2014-08-15 | 2018-01-02 | Elixir Medical Corporation | Biodegradable endoprostheses and methods of their fabrication |
US9480588B2 (en) | 2014-08-15 | 2016-11-01 | Elixir Medical Corporation | Biodegradable endoprostheses and methods of their fabrication |
US9730819B2 (en) | 2014-08-15 | 2017-08-15 | Elixir Medical Corporation | Biodegradable endoprostheses and methods of their fabrication |
CN106687074A (en) | 2014-09-23 | 2017-05-17 | 波顿医疗公司 | Vascular repair devices and methods of use |
US11253278B2 (en) | 2014-11-26 | 2022-02-22 | Neuravi Limited | Clot retrieval system for removing occlusive clot from a blood vessel |
US10617435B2 (en) | 2014-11-26 | 2020-04-14 | Neuravi Limited | Clot retrieval device for removing clot from a blood vessel |
JP2017535352A (en) | 2014-11-26 | 2017-11-30 | ニューラヴィ・リミテッド | Clot collection device for removing obstructive clots from blood vessels |
US10426497B2 (en) | 2015-07-24 | 2019-10-01 | Route 92 Medical, Inc. | Anchoring delivery system and methods |
US11065019B1 (en) | 2015-02-04 | 2021-07-20 | Route 92 Medical, Inc. | Aspiration catheter systems and methods of use |
JP6732769B2 (en) | 2015-02-04 | 2020-07-29 | ルート92メディカル・インコーポレイテッドRoute 92 Medical, Inc. | Rapid suction thrombectomy system and method |
US9566144B2 (en) | 2015-04-22 | 2017-02-14 | Claret Medical, Inc. | Vascular filters, deflectors, and methods |
WO2017019572A1 (en) | 2015-07-24 | 2017-02-02 | Ichor Vascular Inc. | Embolectomy system and methods of making same |
US10441746B2 (en) * | 2015-09-04 | 2019-10-15 | Petrus A. Besselink | Flexible and steerable device |
US10716915B2 (en) | 2015-11-23 | 2020-07-21 | Mivi Neuroscience, Inc. | Catheter systems for applying effective suction in remote vessels and thrombectomy procedures facilitated by catheter systems |
WO2017176730A1 (en) | 2016-04-05 | 2017-10-12 | Bolton Medical, Inc. | Stent graft with internal tunnels and fenestrations and methods of use |
US11622872B2 (en) | 2016-05-16 | 2023-04-11 | Elixir Medical Corporation | Uncaging stent |
CN113143536B (en) | 2016-05-16 | 2022-08-30 | 万能医药公司 | Opening support |
EP3463184B1 (en) | 2016-05-25 | 2021-12-22 | Bolton Medical, Inc. | Stent grafts for treating aneurysms |
ES2860458T3 (en) | 2016-06-13 | 2021-10-05 | Aortica Corp | Systems and devices to mark and / or reinforce fenestrations in prosthetic implants |
CN113229998A (en) | 2016-08-02 | 2021-08-10 | 主动脉公司 | Systems, devices, and methods for coupling a prosthetic implant to an fenestration |
AU2017312421A1 (en) | 2016-08-17 | 2019-03-07 | Neuravi Limited | A clot retrieval system for removing occlusive clot from a blood vessel |
CN109906058B (en) | 2016-09-06 | 2022-06-07 | 尼尔拉维有限公司 | Clot retrieval device for removing an occluded clot from a blood vessel |
US11439492B2 (en) | 2016-09-07 | 2022-09-13 | Daniel Ezra Walzman | Lasso filter tipped microcatheter for simultaneous rotating separator, irrigator for thrombectomy and method for use |
US11259820B2 (en) * | 2016-09-07 | 2022-03-01 | Daniel Ezra Walzman | Methods and devices to ameliorate vascular obstruction |
US10299824B2 (en) * | 2016-09-07 | 2019-05-28 | Daniel Ezra Walzman | Rotating separator, irrigator microcatheter for thrombectomy |
US10314684B2 (en) * | 2016-09-07 | 2019-06-11 | Daniel Ezra Walzman | Simultaneous rotating separator, irrigator microcatheter for thrombectomy |
US11877752B2 (en) | 2016-09-07 | 2024-01-23 | Daniel Ezra Walzman | Filterless aspiration, irrigating, macerating, rotating microcatheter and method of use |
EP3522798A4 (en) | 2016-10-06 | 2020-05-13 | Mivi Neuroscience, Inc. | Hydraulic displacement and removal of thrombus clots, and catheters for performing hydraulic displacement |
EP4134120A1 (en) | 2017-01-10 | 2023-02-15 | Route 92 Medical, Inc. | Aspiration catheter systems |
US11337790B2 (en) | 2017-02-22 | 2022-05-24 | Boston Scientific Scimed, Inc. | Systems and methods for protecting the cerebral vasculature |
CN109890331B (en) | 2017-02-24 | 2022-07-12 | 波顿医疗公司 | Stent-graft delivery system with a shrink sheath and method of use |
ES2863978T3 (en) | 2017-02-24 | 2021-10-13 | Bolton Medical Inc | System for radially constricting a stent graft |
ES2859485T3 (en) | 2017-02-24 | 2021-10-04 | Bolton Medical Inc | Radially Adjustable Stent Graft Delivery System |
WO2018156851A1 (en) | 2017-02-24 | 2018-08-30 | Bolton Medical, Inc. | Vascular prosthesis with moveable fenestration |
CN109843226B (en) | 2017-02-24 | 2022-05-17 | 波顿医疗公司 | Delivery systems and methods of use for radially contracting stent grafts |
CN110022795B (en) | 2017-02-24 | 2023-03-14 | 波顿医疗公司 | Constrained stent grafts, delivery systems and methods of use |
WO2018156847A1 (en) | 2017-02-24 | 2018-08-30 | Bolton Medical, Inc. | Delivery system and method to radially constrict a stent graft |
WO2018156848A1 (en) | 2017-02-24 | 2018-08-30 | Bolton Medical, Inc. | Vascular prosthesis with crimped adapter and methods of use |
WO2018156850A1 (en) | 2017-02-24 | 2018-08-30 | Bolton Medical, Inc. | Stent graft with fenestration lock |
WO2018156849A1 (en) | 2017-02-24 | 2018-08-30 | Bolton Medical, Inc. | Vascular prosthesis with fenestration ring and methods of use |
US11432809B2 (en) | 2017-04-27 | 2022-09-06 | Boston Scientific Scimed, Inc. | Occlusive medical device with fabric retention barb |
US10478535B2 (en) | 2017-05-24 | 2019-11-19 | Mivi Neuroscience, Inc. | Suction catheter systems for applying effective aspiration in remote vessels, especially cerebral arteries |
US11234723B2 (en) | 2017-12-20 | 2022-02-01 | Mivi Neuroscience, Inc. | Suction catheter systems for applying effective aspiration in remote vessels, especially cerebral arteries |
CN111148484B (en) | 2017-09-25 | 2022-12-30 | 波尔顿医疗公司 | Systems, devices, and methods for coupling a prosthetic implant to an open window |
CN111565673A (en) | 2017-10-27 | 2020-08-21 | 波士顿科学医学有限公司 | System and method for protecting cerebral blood vessels |
ES2910187T3 (en) | 2017-10-31 | 2022-05-11 | Bolton Medical Inc | Distal torque component, delivery system and method of use thereof |
JP7013591B2 (en) | 2017-12-18 | 2022-01-31 | ボストン サイエンティフィック サイムド,インコーポレイテッド | Closure device with expandable members |
EP3727192B1 (en) | 2017-12-19 | 2023-03-08 | Boston Scientific Scimed, Inc. | System for protecting the cerebral vasculature |
EP3740139A1 (en) | 2018-01-19 | 2020-11-25 | Boston Scientific Scimed Inc. | Occlusive medical device with delivery system |
EP3784168B1 (en) | 2018-04-26 | 2024-03-20 | Boston Scientific Scimed, Inc. | Systems for protecting the cerebral vasculature |
WO2019213274A1 (en) | 2018-05-02 | 2019-11-07 | Boston Scientific Scimed, Inc. | Occlusive sealing sensor system |
US11241239B2 (en) | 2018-05-15 | 2022-02-08 | Boston Scientific Scimed, Inc. | Occlusive medical device with charged polymer coating |
CN112423824B (en) | 2018-05-17 | 2023-02-21 | 92号医疗公司 | Aspiration catheter system and method of use |
EP3801301A1 (en) | 2018-06-08 | 2021-04-14 | Boston Scientific Scimed Inc. | Occlusive device with actuatable fixation members |
WO2019237004A1 (en) | 2018-06-08 | 2019-12-12 | Boston Scientific Scimed, Inc. | Medical device with occlusive member |
EP3817671A1 (en) | 2018-07-06 | 2021-05-12 | Boston Scientific Scimed Inc. | Occlusive medical device |
US11351023B2 (en) | 2018-08-21 | 2022-06-07 | Claret Medical, Inc. | Systems and methods for protecting the cerebral vasculature |
CN112714632A (en) | 2018-08-21 | 2021-04-27 | 波士顿科学医学有限公司 | Barbed protruding member for cardiovascular devices |
US10842498B2 (en) | 2018-09-13 | 2020-11-24 | Neuravi Limited | Systems and methods of restoring perfusion to a vessel |
US11406416B2 (en) | 2018-10-02 | 2022-08-09 | Neuravi Limited | Joint assembly for vasculature obstruction capture device |
WO2020168091A1 (en) | 2019-02-13 | 2020-08-20 | Emboline, Inc. | Catheter with integrated embolic protection device |
EP4000540B1 (en) | 2019-03-04 | 2024-02-14 | Neuravi Limited | Actuated clot retrieval catheter |
WO2021011694A1 (en) | 2019-07-17 | 2021-01-21 | Boston Scientific Scimed, Inc. | Left atrial appendage implant with continuous covering |
US11707351B2 (en) | 2019-08-19 | 2023-07-25 | Encompass Technologies, Inc. | Embolic protection and access system |
CN114340516A (en) | 2019-08-30 | 2022-04-12 | 波士顿科学医学有限公司 | Left atrial appendage implant with sealing disk |
US11529495B2 (en) | 2019-09-11 | 2022-12-20 | Neuravi Limited | Expandable mouth catheter |
US11712231B2 (en) | 2019-10-29 | 2023-08-01 | Neuravi Limited | Proximal locking assembly design for dual stent mechanical thrombectomy device |
US11839725B2 (en) | 2019-11-27 | 2023-12-12 | Neuravi Limited | Clot retrieval device with outer sheath and inner catheter |
US11779364B2 (en) | 2019-11-27 | 2023-10-10 | Neuravi Limited | Actuated expandable mouth thrombectomy catheter |
US11517340B2 (en) | 2019-12-03 | 2022-12-06 | Neuravi Limited | Stentriever devices for removing an occlusive clot from a vessel and methods thereof |
US11617865B2 (en) | 2020-01-24 | 2023-04-04 | Mivi Neuroscience, Inc. | Suction catheter systems with designs allowing rapid clearing of clots |
US11633198B2 (en) | 2020-03-05 | 2023-04-25 | Neuravi Limited | Catheter proximal joint |
US11944327B2 (en) | 2020-03-05 | 2024-04-02 | Neuravi Limited | Expandable mouth aspirating clot retrieval catheter |
US11903589B2 (en) | 2020-03-24 | 2024-02-20 | Boston Scientific Scimed, Inc. | Medical system for treating a left atrial appendage |
US11883043B2 (en) | 2020-03-31 | 2024-01-30 | DePuy Synthes Products, Inc. | Catheter funnel extension |
US11759217B2 (en) | 2020-04-07 | 2023-09-19 | Neuravi Limited | Catheter tubular support |
US11717308B2 (en) | 2020-04-17 | 2023-08-08 | Neuravi Limited | Clot retrieval device for removing heterogeneous clots from a blood vessel |
US11871946B2 (en) | 2020-04-17 | 2024-01-16 | Neuravi Limited | Clot retrieval device for removing clot from a blood vessel |
US11730501B2 (en) | 2020-04-17 | 2023-08-22 | Neuravi Limited | Floating clot retrieval device for removing clots from a blood vessel |
US11737771B2 (en) | 2020-06-18 | 2023-08-29 | Neuravi Limited | Dual channel thrombectomy device |
US11937836B2 (en) | 2020-06-22 | 2024-03-26 | Neuravi Limited | Clot retrieval system with expandable clot engaging framework |
US11439418B2 (en) | 2020-06-23 | 2022-09-13 | Neuravi Limited | Clot retrieval device for removing clot from a blood vessel |
US11395669B2 (en) | 2020-06-23 | 2022-07-26 | Neuravi Limited | Clot retrieval device with flexible collapsible frame |
US11864781B2 (en) | 2020-09-23 | 2024-01-09 | Neuravi Limited | Rotating frame thrombectomy device |
US11937837B2 (en) | 2020-12-29 | 2024-03-26 | Neuravi Limited | Fibrin rich / soft clot mechanical thrombectomy device |
US11872354B2 (en) | 2021-02-24 | 2024-01-16 | Neuravi Limited | Flexible catheter shaft frame with seam |
US11937839B2 (en) | 2021-09-28 | 2024-03-26 | Neuravi Limited | Catheter with electrically actuated expandable mouth |
WO2024015921A2 (en) * | 2022-07-15 | 2024-01-18 | Maduro Discovery, Llc | Accessory device to provide neuroprotection during interventional procedures |
Citations (94)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3435824A (en) * | 1966-10-27 | 1969-04-01 | Herminio Gamponia | Surgical apparatus and related process |
US3952747A (en) * | 1974-03-28 | 1976-04-27 | Kimmell Jr Garman O | Filter and filter insertion instrument |
US4423725A (en) * | 1982-03-31 | 1984-01-03 | Baran Ostap E | Multiple surgical cuff |
US4425909A (en) * | 1982-01-04 | 1984-01-17 | Rieser Michael J | Laryngoscope |
US4425908A (en) * | 1981-10-22 | 1984-01-17 | Beth Israel Hospital | Blood clot filter |
US4493711A (en) * | 1982-06-25 | 1985-01-15 | Thomas J. Fogarty | Tubular extrusion catheter |
US4512762A (en) * | 1982-11-23 | 1985-04-23 | The Beth Israel Hospital Association | Method of treatment of atherosclerosis and a balloon catheter for same |
US4585000A (en) * | 1983-09-28 | 1986-04-29 | Cordis Corporation | Expandable device for treating intravascular stenosis |
US4643187A (en) * | 1983-05-30 | 1987-02-17 | Olympus Optical Co., Ltd. | High-frequency incising and excising instrument |
US4650466A (en) * | 1985-11-01 | 1987-03-17 | Angiobrade Partners | Angioplasty device |
US4723549A (en) * | 1986-09-18 | 1988-02-09 | Wholey Mark H | Method and apparatus for dilating blood vessels |
US4794928A (en) * | 1987-06-10 | 1989-01-03 | Kletschka Harold D | Angioplasty device and method of using the same |
US4807626A (en) * | 1985-02-14 | 1989-02-28 | Mcgirr Douglas B | Stone extractor and method |
US4817600A (en) * | 1987-05-22 | 1989-04-04 | Medi-Tech, Inc. | Implantable filter |
US4990156A (en) * | 1988-06-21 | 1991-02-05 | Lefebvre Jean Marie | Filter for medical use |
US5011488A (en) * | 1988-12-07 | 1991-04-30 | Robert Ginsburg | Thrombus extraction system |
US5092839A (en) * | 1989-09-29 | 1992-03-03 | Kipperman Robert M | Coronary thrombectomy |
US5100423A (en) * | 1990-08-21 | 1992-03-31 | Medical Engineering & Development Institute, Inc. | Ablation catheter |
US5108419A (en) * | 1990-08-16 | 1992-04-28 | Evi Corporation | Endovascular filter and method for use thereof |
US5178158A (en) * | 1990-10-29 | 1993-01-12 | Boston Scientific Corporation | Convertible guidewire-catheter with soft tip |
US5192284A (en) * | 1992-01-10 | 1993-03-09 | Pleatman Mark A | Surgical collector and extractor |
US5383887A (en) * | 1992-12-28 | 1995-01-24 | Celsa Lg | Device for selectively forming a temporary blood filter |
US5387219A (en) * | 1992-09-23 | 1995-02-07 | Target Therapeutics | Medical retrieval snare with coil wrapped loop |
US5405329A (en) * | 1991-01-08 | 1995-04-11 | Durand; Alain J. | Intravascular multi-lumen catheter, capable of being implanted by "tunnelling" |
US5593394A (en) * | 1995-01-24 | 1997-01-14 | Kanesaka; Nozomu | Shaft for a catheter system |
US5709704A (en) * | 1994-11-30 | 1998-01-20 | Boston Scientific Corporation | Blood clot filtering |
US5720764A (en) * | 1994-06-11 | 1998-02-24 | Naderlinger; Eduard | Vena cava thrombus filter |
US5725519A (en) * | 1996-09-30 | 1998-03-10 | Medtronic Instent Israel Ltd. | Stent loading device for a balloon catheter |
US5876367A (en) * | 1996-12-05 | 1999-03-02 | Embol-X, Inc. | Cerebral protection during carotid endarterectomy and downstream vascular protection during other surgeries |
US5879697A (en) * | 1997-04-30 | 1999-03-09 | Schneider Usa Inc | Drug-releasing coatings for medical devices |
US5882329A (en) * | 1997-02-12 | 1999-03-16 | Prolifix Medical, Inc. | Apparatus and method for removing stenotic material from stents |
US5899935A (en) * | 1997-08-04 | 1999-05-04 | Schneider (Usa) Inc. | Balloon expandable braided stent with restraint |
US6010522A (en) * | 1996-07-17 | 2000-01-04 | Embol-X, Inc. | Atherectomy device having trapping and excising means for removal of plaque from the aorta and other arteries |
US6013093A (en) * | 1995-11-28 | 2000-01-11 | Boston Scientific Corporation | Blood clot filtering |
US6027509A (en) * | 1996-10-03 | 2000-02-22 | Scimed Life Systems, Inc. | Stent retrieval device |
US6027520A (en) * | 1997-05-08 | 2000-02-22 | Embol-X, Inc. | Percutaneous catheter and guidewire having filter and medical device deployment capabilities |
US6168579B1 (en) * | 1999-08-04 | 2001-01-02 | Scimed Life Systems, Inc. | Filter flush system and methods of use |
US6168604B1 (en) * | 1995-10-06 | 2001-01-02 | Metamorphic Surgical Devices, Llc | Guide wire device for removing solid objects from body canals |
US6171327B1 (en) * | 1999-02-24 | 2001-01-09 | Scimed Life Systems, Inc. | Intravascular filter and method |
US6171328B1 (en) * | 1999-11-09 | 2001-01-09 | Embol-X, Inc. | Intravascular catheter filter with interlocking petal design and methods of use |
US6176849B1 (en) * | 1999-05-21 | 2001-01-23 | Scimed Life Systems, Inc. | Hydrophilic lubricity coating for medical devices comprising a hydrophobic top coat |
US6179861B1 (en) * | 1999-07-30 | 2001-01-30 | Incept Llc | Vascular device having one or more articulation regions and methods of use |
US6179859B1 (en) * | 1999-07-16 | 2001-01-30 | Baff Llc | Emboli filtration system and methods of use |
US6203561B1 (en) * | 1999-07-30 | 2001-03-20 | Incept Llc | Integrated vascular device having thrombectomy element and vascular filter and methods of use |
US6206868B1 (en) * | 1998-03-13 | 2001-03-27 | Arteria Medical Science, Inc. | Protective device and method against embolization during treatment of carotid artery disease |
US20020002384A1 (en) * | 1997-11-07 | 2002-01-03 | Paul Gilson | Embolic protection device |
US6340364B2 (en) * | 1999-10-22 | 2002-01-22 | Nozomu Kanesaka | Vascular filtering device |
US6346116B1 (en) * | 1999-08-03 | 2002-02-12 | Medtronic Ave, Inc. | Distal protection device |
US6348056B1 (en) * | 1999-08-06 | 2002-02-19 | Scimed Life Systems, Inc. | Medical retrieval device with releasable retrieval basket |
US20020022858A1 (en) * | 1999-07-30 | 2002-02-21 | Demond Jackson F. | Vascular device for emboli removal having suspension strut and methods of use |
US20020022860A1 (en) * | 2000-08-18 | 2002-02-21 | Borillo Thomas E. | Expandable implant devices for filtering blood flow from atrial appendages |
US20020026211A1 (en) * | 1999-12-23 | 2002-02-28 | Farhad Khosravi | Vascular device having emboli and thrombus removal element and methods of use |
US6355051B1 (en) * | 1999-03-04 | 2002-03-12 | Bioguide Consulting, Inc. | Guidewire filter device |
US20020032460A1 (en) * | 1999-09-21 | 2002-03-14 | Kusleika Richard S. | Temporary vascular filter |
US6361545B1 (en) * | 1997-09-26 | 2002-03-26 | Cardeon Corporation | Perfusion filter catheter |
US6361546B1 (en) * | 2000-01-13 | 2002-03-26 | Endotex Interventional Systems, Inc. | Deployable recoverable vascular filter and methods for use |
US20030004540A1 (en) * | 2001-07-02 | 2003-01-02 | Rubicon Medical, Inc. | Methods, systems, and devices for deploying an embolic protection filter |
US20030004539A1 (en) * | 2001-07-02 | 2003-01-02 | Linder Richard J. | Methods, systems, and devices for providing embolic protection and removing embolic material |
US20030004541A1 (en) * | 2001-07-02 | 2003-01-02 | Rubicon Medical, Inc. | Methods, systems, and devices for providing embolic protection |
US20030004536A1 (en) * | 2001-06-29 | 2003-01-02 | Boylan John F. | Variable thickness embolic filtering devices and method of manufacturing the same |
US20030004537A1 (en) * | 2001-06-29 | 2003-01-02 | Boyle William J. | Delivery and recovery sheaths for medical devices |
US20030009188A1 (en) * | 2001-07-02 | 2003-01-09 | Linder Richard J. | Methods, systems, and devices for deploying a filter from a filter device |
US6506203B1 (en) * | 2000-12-19 | 2003-01-14 | Advanced Cardiovascular Systems, Inc. | Low profile sheathless embolic protection system |
US6506205B2 (en) * | 2001-02-20 | 2003-01-14 | Mark Goldberg | Blood clot filtering system |
US20030015206A1 (en) * | 2001-07-18 | 2003-01-23 | Roth Noah M. | Integral vascular filter system |
US6511496B1 (en) * | 2000-09-12 | 2003-01-28 | Advanced Cardiovascular Systems, Inc. | Embolic protection device for use in interventional procedures |
US6511503B1 (en) * | 1999-12-30 | 2003-01-28 | Advanced Cardiovascular Systems, Inc. | Catheter apparatus for treating occluded vessels and filtering embolic debris and method of use |
US6511492B1 (en) * | 1998-05-01 | 2003-01-28 | Microvention, Inc. | Embolectomy catheters and methods for treating stroke and other small vessel thromboembolic disorders |
US6511497B1 (en) * | 1999-09-14 | 2003-01-28 | Cormedics Gmbh | Vascular filter system |
US20030023265A1 (en) * | 2001-07-13 | 2003-01-30 | Forber Simon John | Vascular protection system |
US6514273B1 (en) * | 2000-03-22 | 2003-02-04 | Endovascular Technologies, Inc. | Device for removal of thrombus through physiological adhesion |
US6517559B1 (en) * | 1999-05-03 | 2003-02-11 | O'connell Paul T. | Blood filter and method for treating vascular disease |
US6517550B1 (en) * | 2000-02-02 | 2003-02-11 | Board Of Regents, The University Of Texas System | Foreign body retrieval device |
US20030032977A1 (en) * | 1997-11-07 | 2003-02-13 | Salviac Limited | Filter element with retractable guidewire tip |
US20030032941A1 (en) * | 2001-08-13 | 2003-02-13 | Boyle William J. | Convertible delivery systems for medical devices |
US6520978B1 (en) * | 2000-05-15 | 2003-02-18 | Intratherapeutics, Inc. | Emboli filter |
US20030040772A1 (en) * | 1999-02-01 | 2003-02-27 | Hideki Hyodoh | Delivery devices |
US6527746B1 (en) * | 2000-08-03 | 2003-03-04 | Ev3, Inc. | Back-loading catheter |
US20030042186A1 (en) * | 2001-08-31 | 2003-03-06 | Boyle William J. | Embolic protection devices one way porous membrane |
US20030045898A1 (en) * | 2001-09-06 | 2003-03-06 | Harrison William J. | Embolic protection basket |
US6530940B2 (en) * | 1999-10-25 | 2003-03-11 | John S. Fisher | Emboli capturing device |
US6530939B1 (en) * | 1999-07-30 | 2003-03-11 | Incept, Llc | Vascular device having articulation region and methods of use |
US6533800B1 (en) * | 2001-07-25 | 2003-03-18 | Coaxia, Inc. | Devices and methods for preventing distal embolization using flow reversal in arteries having collateral blood flow |
US6537294B1 (en) * | 2000-10-17 | 2003-03-25 | Advanced Cardiovascular Systems, Inc. | Delivery systems for embolic filter devices |
US6537296B2 (en) * | 1999-04-01 | 2003-03-25 | Scion Cardio-Vascular, Inc. | Locking frame, filter and deployment system |
US6537295B2 (en) * | 2001-03-06 | 2003-03-25 | Scimed Life Systems, Inc. | Wire and lock mechanism |
US20030060843A1 (en) * | 2001-09-27 | 2003-03-27 | Don Boucher | Vascular filter system with encapsulated filter |
US20030060844A1 (en) * | 1999-02-12 | 2003-03-27 | Thomas Borillo | Vascular filter system |
US20030060782A1 (en) * | 1998-06-04 | 2003-03-27 | Arani Bose | Endovascular thin film devices and methods for treating and preventing stroke |
US20030057156A1 (en) * | 2001-03-08 | 2003-03-27 | Dean Peterson | Atrial filter implants |
US20040010282A1 (en) * | 2002-07-12 | 2004-01-15 | Kusleika Richard S. | Catheter with occluding cuff |
US6682812B2 (en) * | 1998-02-27 | 2004-01-27 | Ticona Gmbh | Thermal spray powder of oxidized polyarylene incorporating a particular high temperature polymer |
US20060028238A1 (en) * | 2003-11-28 | 2006-02-09 | Arnold Barry J | Partial termination voltage current shunting |
US20070060945A1 (en) * | 1999-05-07 | 2007-03-15 | Salviac Limited | Embolic protection device |
Family Cites Families (69)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US2854983A (en) | 1957-10-31 | 1958-10-07 | Arnold M Baskin | Inflatable catheter |
US3334629A (en) | 1964-11-09 | 1967-08-08 | Bertram D Cohn | Occlusive device for inferior vena cava |
US3540431A (en) | 1968-04-04 | 1970-11-17 | Kazi Mobin Uddin | Collapsible filter for fluid flowing in closed passageway |
US3692029A (en) | 1971-05-03 | 1972-09-19 | Edwin Lloyd Adair | Retention catheter and suprapubic shunt |
US3730185A (en) | 1971-10-29 | 1973-05-01 | Cook Inc | Endarterectomy apparatus |
DE2821048C2 (en) | 1978-05-13 | 1980-07-17 | Willy Ruesch Gmbh & Co Kg, 7053 Kernen | Medical instrument |
US4295464A (en) | 1980-03-21 | 1981-10-20 | Shihata Alfred A | Ureteric stone extractor with two ballooned catheters |
US4404971A (en) | 1981-04-03 | 1983-09-20 | Leveen Harry H | Dual balloon catheter |
DE3235974A1 (en) | 1981-11-24 | 1983-06-01 | Volkmar Dipl.-Ing. Merkel (FH), 8520 Erlangen | DEVICE FOR REMOVAL OR FOR THE EXPANSION OF CONSTRAINTS IN BODY LIQUID LEADING VESSELS |
US4445892A (en) | 1982-05-06 | 1984-05-01 | Laserscope, Inc. | Dual balloon catheter device |
US4611594A (en) | 1984-04-11 | 1986-09-16 | Northwestern University | Medical instrument for containment and removal of calculi |
DK151404C (en) | 1984-05-23 | 1988-07-18 | Cook Europ Aps William | FULLY FILTER FOR IMPLANTATION IN A PATIENT'S BLOOD |
US4926858A (en) | 1984-05-30 | 1990-05-22 | Devices For Vascular Intervention, Inc. | Atherectomy device for severe occlusions |
FR2580504B1 (en) | 1985-04-22 | 1987-07-10 | Pieronne Alain | FILTER FOR THE PARTIAL AND AT LEAST PROVISIONAL INTERRUPTION OF A VEIN AND CATHETER CARRYING THE FILTER |
US4790812A (en) | 1985-11-15 | 1988-12-13 | Hawkins Jr Irvin F | Apparatus and method for removing a target object from a body passsageway |
EP0256683A3 (en) | 1986-08-04 | 1989-08-09 | Aries Medical Incorporated | Means for furling a balloon of a balloon catheter |
GB2200848B (en) | 1987-02-25 | 1991-02-13 | Mo Med Inst Pirogova | Intravenous filter, and apparatus and method for preoperative preparation thereof |
FR2616666A1 (en) | 1987-06-22 | 1988-12-23 | Scit Sc | Device of the catheter type for extracting and repositioning filters of the Greenfield or similar type which are wrongly positioned, through the vein |
US4873978A (en) | 1987-12-04 | 1989-10-17 | Robert Ginsburg | Device and method for emboli retrieval |
US4990159A (en) * | 1988-12-02 | 1991-02-05 | Kraff Manus C | Intraocular lens apparatus with haptics of varying cross-sectional areas |
US4927426A (en) | 1989-01-03 | 1990-05-22 | Dretler Stephen P | Catheter device |
DE9010130U1 (en) | 1989-07-13 | 1990-09-13 | American Medical Systems, Inc., Minnetonka, Minn., Us | |
US5122125A (en) | 1990-04-25 | 1992-06-16 | Ashridge A.G. | Catheter for angioplasty with soft centering tip |
CA2048307C (en) | 1990-08-14 | 1998-08-18 | Rolf Gunther | Method and apparatus for filtering blood in a blood vessel of a patient |
CA2095814C (en) * | 1990-11-09 | 2002-09-17 | John E. Abele | Guidewire for crossing occlusions in blood vessels |
US5053008A (en) | 1990-11-21 | 1991-10-01 | Sandeep Bajaj | Intracardiac catheter |
DE9109006U1 (en) | 1991-07-22 | 1991-10-10 | Schmitz-Rode, Thomas, Dipl.-Ing. Dr.Med., 5100 Aachen, De | |
US5324304A (en) | 1992-06-18 | 1994-06-28 | William Cook Europe A/S | Introduction catheter set for a collapsible self-expandable implant |
US5897567A (en) | 1993-04-29 | 1999-04-27 | Scimed Life Systems, Inc. | Expandable intravascular occlusion material removal devices and methods of use |
DE19513164A1 (en) * | 1995-04-07 | 1996-10-10 | Bayer Ag | Hydroxy-terminated polycarbonates based on high mol. cyclic dimer diols with and use in prodn. of polyurethanes stable against hydrolysis and oxidn. |
US5795322A (en) | 1995-04-10 | 1998-08-18 | Cordis Corporation | Catheter with filter and thrombus-discharge device |
US5707354A (en) | 1995-04-17 | 1998-01-13 | Cardiovascular Imaging Systems, Inc. | Compliant catheter lumen and methods |
NL1001410C2 (en) | 1995-05-19 | 1996-11-20 | Cordis Europ | Medical device for long-term residence in a body. |
US5766203A (en) | 1995-07-20 | 1998-06-16 | Intelliwire, Inc. | Sheath with expandable distal extremity and balloon catheters and stents for use therewith and method |
US5769816A (en) | 1995-11-07 | 1998-06-23 | Embol-X, Inc. | Cannula with associated filter |
US5769871A (en) | 1995-11-17 | 1998-06-23 | Louisville Laboratories, Inc. | Embolectomy catheter |
US5695519A (en) | 1995-11-30 | 1997-12-09 | American Biomed, Inc. | Percutaneous filter for carotid angioplasty |
NL1002423C2 (en) | 1996-02-22 | 1997-08-25 | Cordis Europ | Temporary filter catheter. |
NL1003497C2 (en) | 1996-07-03 | 1998-01-07 | Cordis Europ | Catheter with temporary vena-cava filter. |
US5669933A (en) | 1996-07-17 | 1997-09-23 | Nitinol Medical Technologies, Inc. | Removable embolus blood clot filter |
NL1003984C2 (en) | 1996-09-09 | 1998-03-10 | Cordis Europ | Catheter with internal stiffening bridges. |
WO1998033443A1 (en) * | 1997-02-03 | 1998-08-06 | Angioguard, Inc. | Vascular filter |
JP2001512334A (en) | 1997-02-12 | 2001-08-21 | プロリフィックス メディカル,インコーポレイテッド | Equipment for removing material from stents |
US5800457A (en) | 1997-03-05 | 1998-09-01 | Gelbfish; Gary A. | Intravascular filter and associated methodology |
US5814064A (en) | 1997-03-06 | 1998-09-29 | Scimed Life Systems, Inc. | Distal protection device |
US5827324A (en) | 1997-03-06 | 1998-10-27 | Scimed Life Systems, Inc. | Distal protection device |
US6152946A (en) | 1998-03-05 | 2000-11-28 | Scimed Life Systems, Inc. | Distal protection device and method |
WO1998039053A1 (en) * | 1997-03-06 | 1998-09-11 | Scimed Life Systems, Inc. | Distal protection device and method |
EP0981308B1 (en) * | 1997-05-16 | 2006-05-31 | Jonathan Gertler | Catheter-filter set having a compliant seal |
US5954745A (en) | 1997-05-16 | 1999-09-21 | Gertler; Jonathan | Catheter-filter set having a compliant seal |
US5800525A (en) | 1997-06-04 | 1998-09-01 | Vascular Science, Inc. | Blood filter |
US5848964A (en) | 1997-06-06 | 1998-12-15 | Samuels; Shaun Lawrence Wilkie | Temporary inflatable filter device and method of use |
FR2768326B1 (en) | 1997-09-18 | 1999-10-22 | De Bearn Olivier Despalle | TEMPORARY BLOOD FILTER |
JPH11100112A (en) | 1997-09-27 | 1999-04-13 | Ricoh Co Ltd | Belt device |
NO311781B1 (en) * | 1997-11-13 | 2002-01-28 | Medinol Ltd | Metal multilayer stents |
US6132458A (en) | 1998-05-15 | 2000-10-17 | American Medical Systems, Inc. | Method and device for loading a stent |
IL124958A0 (en) | 1998-06-16 | 1999-01-26 | Yodfat Ofer | Implantable blood filtering device |
US6102917A (en) * | 1998-07-15 | 2000-08-15 | The Regents Of The University Of California | Shape memory polymer (SMP) gripper with a release sensing system |
US6245012B1 (en) | 1999-03-19 | 2001-06-12 | Nmt Medical, Inc. | Free standing filter |
US6277139B1 (en) | 1999-04-01 | 2001-08-21 | Scion Cardio-Vascular, Inc. | Vascular protection and embolic material retriever |
US6277138B1 (en) | 1999-08-17 | 2001-08-21 | Scion Cardio-Vascular, Inc. | Filter for embolic material mounted on expandable frame |
US6468291B2 (en) | 1999-07-16 | 2002-10-22 | Baff Llc | Emboli filtration system having integral strut arrangement and methods of use |
US6214026B1 (en) | 1999-07-30 | 2001-04-10 | Incept Llc | Delivery system for a vascular device with articulation region |
US6540722B1 (en) * | 1999-12-30 | 2003-04-01 | Advanced Cardiovascular Systems, Inc. | Embolic protection devices |
US6540768B1 (en) | 2000-02-09 | 2003-04-01 | Cordis Corporation | Vascular filter system |
EP1149566A3 (en) | 2000-04-24 | 2003-08-06 | Cordis Corporation | Vascular filter systems with guidewire and capture mechanism |
US6602271B2 (en) | 2000-05-24 | 2003-08-05 | Medtronic Ave, Inc. | Collapsible blood filter with optimal braid geometry |
US6575995B1 (en) * | 2000-07-14 | 2003-06-10 | Advanced Cardiovascular Systems, Inc. | Expandable cage embolic material filter system and method |
US6569184B2 (en) * | 2001-02-27 | 2003-05-27 | Advanced Cardiovascular Systems, Inc. | Recovery system for retrieving an embolic protection device |
-
2000
- 2000-05-08 DE DE20080298U patent/DE20080298U1/en not_active Expired - Lifetime
- 2000-05-08 IL IL14597900A patent/IL145979A0/en unknown
- 2000-05-08 AU AU46064/00A patent/AU4606400A/en not_active Abandoned
- 2000-05-08 EP EP00927679A patent/EP1176924B1/en not_active Expired - Lifetime
- 2000-05-08 JP JP2000616701A patent/JP2002543875A/en active Pending
- 2000-05-08 CA CA002384398A patent/CA2384398A1/en not_active Abandoned
- 2000-05-08 JP JP2000616703A patent/JP2002543877A/en active Pending
- 2000-05-08 EP EP00925546A patent/EP1176923A1/en not_active Withdrawn
- 2000-05-08 WO PCT/IE2000/000055 patent/WO2000067670A1/en not_active Application Discontinuation
- 2000-05-08 DE DE10084521T patent/DE10084521T1/en not_active Withdrawn
- 2000-05-08 AU AU44265/00A patent/AU774500B2/en not_active Expired
- 2000-05-08 WO PCT/IE2000/000053 patent/WO2000067668A1/en active IP Right Grant
- 2000-05-08 GB GB0124864A patent/GB2365356A/en not_active Withdrawn
-
2001
- 2001-11-07 US US09/986,064 patent/US6726701B2/en not_active Expired - Lifetime
-
2003
- 2003-10-22 US US10/689,846 patent/US20040267302A1/en not_active Abandoned
-
2006
- 2006-09-29 US US11/529,525 patent/US8038697B2/en not_active Expired - Fee Related
- 2006-11-22 US US11/562,720 patent/US20080167677A1/en not_active Abandoned
-
2009
- 2009-01-06 US US12/349,209 patent/US20090149881A1/en not_active Abandoned
Patent Citations (100)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3435824A (en) * | 1966-10-27 | 1969-04-01 | Herminio Gamponia | Surgical apparatus and related process |
US3952747A (en) * | 1974-03-28 | 1976-04-27 | Kimmell Jr Garman O | Filter and filter insertion instrument |
US4425908A (en) * | 1981-10-22 | 1984-01-17 | Beth Israel Hospital | Blood clot filter |
US4425909A (en) * | 1982-01-04 | 1984-01-17 | Rieser Michael J | Laryngoscope |
US4423725A (en) * | 1982-03-31 | 1984-01-03 | Baran Ostap E | Multiple surgical cuff |
US4493711A (en) * | 1982-06-25 | 1985-01-15 | Thomas J. Fogarty | Tubular extrusion catheter |
US4512762A (en) * | 1982-11-23 | 1985-04-23 | The Beth Israel Hospital Association | Method of treatment of atherosclerosis and a balloon catheter for same |
US4643187A (en) * | 1983-05-30 | 1987-02-17 | Olympus Optical Co., Ltd. | High-frequency incising and excising instrument |
US4585000A (en) * | 1983-09-28 | 1986-04-29 | Cordis Corporation | Expandable device for treating intravascular stenosis |
US4807626A (en) * | 1985-02-14 | 1989-02-28 | Mcgirr Douglas B | Stone extractor and method |
US4650466A (en) * | 1985-11-01 | 1987-03-17 | Angiobrade Partners | Angioplasty device |
US4723549A (en) * | 1986-09-18 | 1988-02-09 | Wholey Mark H | Method and apparatus for dilating blood vessels |
US4817600A (en) * | 1987-05-22 | 1989-04-04 | Medi-Tech, Inc. | Implantable filter |
US4794928A (en) * | 1987-06-10 | 1989-01-03 | Kletschka Harold D | Angioplasty device and method of using the same |
US4990156A (en) * | 1988-06-21 | 1991-02-05 | Lefebvre Jean Marie | Filter for medical use |
US5011488A (en) * | 1988-12-07 | 1991-04-30 | Robert Ginsburg | Thrombus extraction system |
US5092839A (en) * | 1989-09-29 | 1992-03-03 | Kipperman Robert M | Coronary thrombectomy |
US5108419A (en) * | 1990-08-16 | 1992-04-28 | Evi Corporation | Endovascular filter and method for use thereof |
US5100423A (en) * | 1990-08-21 | 1992-03-31 | Medical Engineering & Development Institute, Inc. | Ablation catheter |
US5178158A (en) * | 1990-10-29 | 1993-01-12 | Boston Scientific Corporation | Convertible guidewire-catheter with soft tip |
US5405329A (en) * | 1991-01-08 | 1995-04-11 | Durand; Alain J. | Intravascular multi-lumen catheter, capable of being implanted by "tunnelling" |
US5192284A (en) * | 1992-01-10 | 1993-03-09 | Pleatman Mark A | Surgical collector and extractor |
US5387219A (en) * | 1992-09-23 | 1995-02-07 | Target Therapeutics | Medical retrieval snare with coil wrapped loop |
US5383887A (en) * | 1992-12-28 | 1995-01-24 | Celsa Lg | Device for selectively forming a temporary blood filter |
US5720764A (en) * | 1994-06-11 | 1998-02-24 | Naderlinger; Eduard | Vena cava thrombus filter |
US5709704A (en) * | 1994-11-30 | 1998-01-20 | Boston Scientific Corporation | Blood clot filtering |
US5593394A (en) * | 1995-01-24 | 1997-01-14 | Kanesaka; Nozomu | Shaft for a catheter system |
US6168604B1 (en) * | 1995-10-06 | 2001-01-02 | Metamorphic Surgical Devices, Llc | Guide wire device for removing solid objects from body canals |
US6013093A (en) * | 1995-11-28 | 2000-01-11 | Boston Scientific Corporation | Blood clot filtering |
US6010522A (en) * | 1996-07-17 | 2000-01-04 | Embol-X, Inc. | Atherectomy device having trapping and excising means for removal of plaque from the aorta and other arteries |
US5725519A (en) * | 1996-09-30 | 1998-03-10 | Medtronic Instent Israel Ltd. | Stent loading device for a balloon catheter |
US6027509A (en) * | 1996-10-03 | 2000-02-22 | Scimed Life Systems, Inc. | Stent retrieval device |
US5876367A (en) * | 1996-12-05 | 1999-03-02 | Embol-X, Inc. | Cerebral protection during carotid endarterectomy and downstream vascular protection during other surgeries |
US5882329A (en) * | 1997-02-12 | 1999-03-16 | Prolifix Medical, Inc. | Apparatus and method for removing stenotic material from stents |
US5879697A (en) * | 1997-04-30 | 1999-03-09 | Schneider Usa Inc | Drug-releasing coatings for medical devices |
US6042598A (en) * | 1997-05-08 | 2000-03-28 | Embol-X Inc. | Method of protecting a patient from embolization during cardiac surgery |
US6537297B2 (en) * | 1997-05-08 | 2003-03-25 | Embol-X, Inc. | Methods of protecting a patient from embolization during surgery |
US6027520A (en) * | 1997-05-08 | 2000-02-22 | Embol-X, Inc. | Percutaneous catheter and guidewire having filter and medical device deployment capabilities |
US5899935A (en) * | 1997-08-04 | 1999-05-04 | Schneider (Usa) Inc. | Balloon expandable braided stent with restraint |
US6361545B1 (en) * | 1997-09-26 | 2002-03-26 | Cardeon Corporation | Perfusion filter catheter |
US6336934B1 (en) * | 1997-11-07 | 2002-01-08 | Salviac Limited | Embolic protection device |
US20030032977A1 (en) * | 1997-11-07 | 2003-02-13 | Salviac Limited | Filter element with retractable guidewire tip |
US20020002384A1 (en) * | 1997-11-07 | 2002-01-03 | Paul Gilson | Embolic protection device |
US20030009189A1 (en) * | 1997-11-07 | 2003-01-09 | Salviac Limited | Embolic protection device |
US20020026213A1 (en) * | 1997-11-07 | 2002-02-28 | Paul Gilson | Embolic protection device |
US6682812B2 (en) * | 1998-02-27 | 2004-01-27 | Ticona Gmbh | Thermal spray powder of oxidized polyarylene incorporating a particular high temperature polymer |
US6206868B1 (en) * | 1998-03-13 | 2001-03-27 | Arteria Medical Science, Inc. | Protective device and method against embolization during treatment of carotid artery disease |
US6511492B1 (en) * | 1998-05-01 | 2003-01-28 | Microvention, Inc. | Embolectomy catheters and methods for treating stroke and other small vessel thromboembolic disorders |
US20030060782A1 (en) * | 1998-06-04 | 2003-03-27 | Arani Bose | Endovascular thin film devices and methods for treating and preventing stroke |
US20030040772A1 (en) * | 1999-02-01 | 2003-02-27 | Hideki Hyodoh | Delivery devices |
US20030060844A1 (en) * | 1999-02-12 | 2003-03-27 | Thomas Borillo | Vascular filter system |
US6171327B1 (en) * | 1999-02-24 | 2001-01-09 | Scimed Life Systems, Inc. | Intravascular filter and method |
US6355051B1 (en) * | 1999-03-04 | 2002-03-12 | Bioguide Consulting, Inc. | Guidewire filter device |
US6537296B2 (en) * | 1999-04-01 | 2003-03-25 | Scion Cardio-Vascular, Inc. | Locking frame, filter and deployment system |
US6517559B1 (en) * | 1999-05-03 | 2003-02-11 | O'connell Paul T. | Blood filter and method for treating vascular disease |
US20070060945A1 (en) * | 1999-05-07 | 2007-03-15 | Salviac Limited | Embolic protection device |
US6176849B1 (en) * | 1999-05-21 | 2001-01-23 | Scimed Life Systems, Inc. | Hydrophilic lubricity coating for medical devices comprising a hydrophobic top coat |
US6179859B1 (en) * | 1999-07-16 | 2001-01-30 | Baff Llc | Emboli filtration system and methods of use |
US20020022858A1 (en) * | 1999-07-30 | 2002-02-21 | Demond Jackson F. | Vascular device for emboli removal having suspension strut and methods of use |
US6203561B1 (en) * | 1999-07-30 | 2001-03-20 | Incept Llc | Integrated vascular device having thrombectomy element and vascular filter and methods of use |
US6530939B1 (en) * | 1999-07-30 | 2003-03-11 | Incept, Llc | Vascular device having articulation region and methods of use |
US6179861B1 (en) * | 1999-07-30 | 2001-01-30 | Incept Llc | Vascular device having one or more articulation regions and methods of use |
US6346116B1 (en) * | 1999-08-03 | 2002-02-12 | Medtronic Ave, Inc. | Distal protection device |
US6168579B1 (en) * | 1999-08-04 | 2001-01-02 | Scimed Life Systems, Inc. | Filter flush system and methods of use |
US6348056B1 (en) * | 1999-08-06 | 2002-02-19 | Scimed Life Systems, Inc. | Medical retrieval device with releasable retrieval basket |
US6511497B1 (en) * | 1999-09-14 | 2003-01-28 | Cormedics Gmbh | Vascular filter system |
US20020032460A1 (en) * | 1999-09-21 | 2002-03-14 | Kusleika Richard S. | Temporary vascular filter |
US6340364B2 (en) * | 1999-10-22 | 2002-01-22 | Nozomu Kanesaka | Vascular filtering device |
US6530940B2 (en) * | 1999-10-25 | 2003-03-11 | John S. Fisher | Emboli capturing device |
US6171328B1 (en) * | 1999-11-09 | 2001-01-09 | Embol-X, Inc. | Intravascular catheter filter with interlocking petal design and methods of use |
US20020026211A1 (en) * | 1999-12-23 | 2002-02-28 | Farhad Khosravi | Vascular device having emboli and thrombus removal element and methods of use |
US6511503B1 (en) * | 1999-12-30 | 2003-01-28 | Advanced Cardiovascular Systems, Inc. | Catheter apparatus for treating occluded vessels and filtering embolic debris and method of use |
US6361546B1 (en) * | 2000-01-13 | 2002-03-26 | Endotex Interventional Systems, Inc. | Deployable recoverable vascular filter and methods for use |
US6517550B1 (en) * | 2000-02-02 | 2003-02-11 | Board Of Regents, The University Of Texas System | Foreign body retrieval device |
US6514273B1 (en) * | 2000-03-22 | 2003-02-04 | Endovascular Technologies, Inc. | Device for removal of thrombus through physiological adhesion |
US6520978B1 (en) * | 2000-05-15 | 2003-02-18 | Intratherapeutics, Inc. | Emboli filter |
US6527746B1 (en) * | 2000-08-03 | 2003-03-04 | Ev3, Inc. | Back-loading catheter |
US20020022860A1 (en) * | 2000-08-18 | 2002-02-21 | Borillo Thomas E. | Expandable implant devices for filtering blood flow from atrial appendages |
US6511496B1 (en) * | 2000-09-12 | 2003-01-28 | Advanced Cardiovascular Systems, Inc. | Embolic protection device for use in interventional procedures |
US6537294B1 (en) * | 2000-10-17 | 2003-03-25 | Advanced Cardiovascular Systems, Inc. | Delivery systems for embolic filter devices |
US6506203B1 (en) * | 2000-12-19 | 2003-01-14 | Advanced Cardiovascular Systems, Inc. | Low profile sheathless embolic protection system |
US6506205B2 (en) * | 2001-02-20 | 2003-01-14 | Mark Goldberg | Blood clot filtering system |
US6537295B2 (en) * | 2001-03-06 | 2003-03-25 | Scimed Life Systems, Inc. | Wire and lock mechanism |
US20030057156A1 (en) * | 2001-03-08 | 2003-03-27 | Dean Peterson | Atrial filter implants |
US20030004537A1 (en) * | 2001-06-29 | 2003-01-02 | Boyle William J. | Delivery and recovery sheaths for medical devices |
US20030004536A1 (en) * | 2001-06-29 | 2003-01-02 | Boylan John F. | Variable thickness embolic filtering devices and method of manufacturing the same |
US20030004541A1 (en) * | 2001-07-02 | 2003-01-02 | Rubicon Medical, Inc. | Methods, systems, and devices for providing embolic protection |
US20030009188A1 (en) * | 2001-07-02 | 2003-01-09 | Linder Richard J. | Methods, systems, and devices for deploying a filter from a filter device |
US20030004539A1 (en) * | 2001-07-02 | 2003-01-02 | Linder Richard J. | Methods, systems, and devices for providing embolic protection and removing embolic material |
US20030004540A1 (en) * | 2001-07-02 | 2003-01-02 | Rubicon Medical, Inc. | Methods, systems, and devices for deploying an embolic protection filter |
US20030023265A1 (en) * | 2001-07-13 | 2003-01-30 | Forber Simon John | Vascular protection system |
US20030018354A1 (en) * | 2001-07-18 | 2003-01-23 | Roth Noah M. | Integral vascular filter system with core wire activation |
US20030015206A1 (en) * | 2001-07-18 | 2003-01-23 | Roth Noah M. | Integral vascular filter system |
US6533800B1 (en) * | 2001-07-25 | 2003-03-18 | Coaxia, Inc. | Devices and methods for preventing distal embolization using flow reversal in arteries having collateral blood flow |
US20030032941A1 (en) * | 2001-08-13 | 2003-02-13 | Boyle William J. | Convertible delivery systems for medical devices |
US20030042186A1 (en) * | 2001-08-31 | 2003-03-06 | Boyle William J. | Embolic protection devices one way porous membrane |
US20030045898A1 (en) * | 2001-09-06 | 2003-03-06 | Harrison William J. | Embolic protection basket |
US20030060843A1 (en) * | 2001-09-27 | 2003-03-27 | Don Boucher | Vascular filter system with encapsulated filter |
US20040010282A1 (en) * | 2002-07-12 | 2004-01-15 | Kusleika Richard S. | Catheter with occluding cuff |
US20060028238A1 (en) * | 2003-11-28 | 2006-02-09 | Arnold Barry J | Partial termination voltage current shunting |
Cited By (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20060229660A1 (en) * | 2005-03-15 | 2006-10-12 | Dharmendra Pal | Embolic protection device |
US8221446B2 (en) * | 2005-03-15 | 2012-07-17 | Cook Medical Technologies | Embolic protection device |
US20100191273A1 (en) * | 2009-01-23 | 2010-07-29 | Salviac Limited | Embolic protection device with no delivery catheter or retrieval catheter and methods of using the same |
Also Published As
Publication number | Publication date |
---|---|
DE10084521T1 (en) | 2002-06-20 |
US8038697B2 (en) | 2011-10-18 |
AU4606400A (en) | 2000-11-21 |
IL145979A0 (en) | 2002-07-25 |
AU4426500A (en) | 2000-11-21 |
US20040267302A1 (en) | 2004-12-30 |
WO2000067668A1 (en) | 2000-11-16 |
GB0124864D0 (en) | 2001-12-05 |
AU774500B2 (en) | 2004-07-01 |
US20070060945A1 (en) | 2007-03-15 |
GB2365356A (en) | 2002-02-20 |
JP2002543877A (en) | 2002-12-24 |
EP1176923A1 (en) | 2002-02-06 |
CA2384398A1 (en) | 2000-11-16 |
US20090149881A1 (en) | 2009-06-11 |
US6726701B2 (en) | 2004-04-27 |
JP2002543875A (en) | 2002-12-24 |
US20020062133A1 (en) | 2002-05-23 |
EP1176924A1 (en) | 2002-02-06 |
EP1176924B1 (en) | 2005-01-12 |
DE20080298U1 (en) | 2001-12-20 |
WO2000067670A1 (en) | 2000-11-16 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US7491215B2 (en) | Filter element for embolic protection device | |
EP1176924B1 (en) | Improved filter element for embolic protection device | |
US7316702B2 (en) | Methods and apparatus for distal protection during a medical procedure | |
US8236024B2 (en) | Low profile emboli capture device | |
US5980555A (en) | Method of using cannula with associated filter during cardiac surgery | |
US10004531B2 (en) | Methods and apparatus for treating embolism | |
US6511496B1 (en) | Embolic protection device for use in interventional procedures | |
US20070100372A1 (en) | Embolic protection device having a filter | |
US20140081315A1 (en) | Multi-Layer Filtration Device | |
US20070100373A1 (en) | Embolic protection device having reduced profile | |
WO2000067664A1 (en) | An embolic protection device | |
IE20000341A1 (en) | A Filter Element | |
IE20000343A1 (en) | A Filter Element |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
STCB | Information on status: application discontinuation |
Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION |