Patent Grant
12042160
Stroke is the third most common cause of death in the United States and the most disabling neurologic disorder. Approximately 700,000 patients suffer from stroke annually. Stroke is a syndrome characterized by the acute onset of a neurological deficit that persists for at least 24 hours, reflecting focal involvement of the central nervous system, and is the result of a disturbance of the cerebral circulation. Its incidence increases with age. Risk factors for stroke include systolic or diastolic hypertension, hypercholesterolemia, cigarette smoking, heavy alcohol consumption, and oral contraceptive use.
Hemorrhagic stroke accounts for 20% of the annual stroke population. Hemorrhagic stroke often occurs due to rupture of an aneurysm or arteriovenous malformation bleeding into the brain tissue, resulting in cerebral infarction. The remaining 80% of the stroke population are ischemic strokes and are caused by occluded vessels that deprive the brain of oxygen-carrying blood. Ischemic strokes are often caused by emboli or pieces of thrombotic tissue that have dislodged from other body sites or from the cerebral vessels themselves to occlude in the narrow cerebral arteries more distally. When a patient presents with neurological symptoms and signs which resolve completely within 1 hour, the term transient ischemic attack (TIA) is used. Etiologically, TIA and stroke share the same pathophysiologic mechanisms and thus represent a continuum based on persistence of symptoms and extent of ischemic insult.
Emboli occasionally form around the valves of the heart or in the left atrial appendage during periods of irregular heart rhythm and then are dislodged and follow the blood flow into the distal regions of the body. Those emboli can pass to the brain and cause an embolic stroke. As will be discussed below, many such occlusions occur in the middle cerebral artery (MCA), although such is not the only site where emboli come to rest.
When a patient presents with neurological deficit, a diagnostic hypothesis for the cause of stroke can be generated based on the patient's history, a review of stroke risk factors, and a neurologic examination. If an ischemic event is suspected, a clinician can tentatively assess whether the patient has a cardiogenic source of emboli, large artery extracranial or intracranial disease, small artery intraparenchymal disease, or a hematologic or other systemic disorder. A head CT scan is often performed to determine whether the patient has suffered an ischemic or hemorrhagic insult. Blood would be present on the CT scan in subarachnoid hemorrhage, intraparenchymal hematoma, or intraventricular hemorrhage.
Traditionally, emergent management of acute ischemic stroke consisted mainly of general supportive care, e.g. hydration, monitoring neurological status, blood pressure control, and/or anti-platelet or anti-coagulation therapy. In 1996, the Food and Drug Administration approved the use of Genentech Inc.'s thrombolytic drug, tissue plasminogen activator (t-PA) or Activase®, for treating acute stroke. A randomized, double-blind trial, the National Institute of Neurological Disorders and t-PA Stroke Study, revealed a statistically significant improvement in stoke scale scores at 24 hours in the group of patients receiving intravenous t-PA within 3 hours of the onset of an ischemic stroke. Since the approval of t-PA, an emergency room physician could, for the first time, offer a stroke patient an effective treatment besides supportive care.
However, treatment with systemic t-PA is associated with increased risk of intracerebral hemorrhage and other hemorrhagic complications. Patients treated with t-PA were more likely to sustain a symptomatic intracerebral hemorrhage during the first 36 hours of treatment. The frequency of symptomatic hemorrhage increases when t-PA is administered beyond 3 hours from the onset of a stroke. Besides the time constraint in using t-PA in acute ischemic stroke, other contraindications include the following: if the patient has had a previous stroke or serious head trauma in the preceding 3 months, if the patient has a systolic blood pressure above 185 mm Hg or diastolic blood pressure above 110 mmHg, if the patient requires aggressive treatment to reduce the blood pressure to the specified limits, if the patient is taking anticoagulants or has a propensity to hemorrhage, and/or if the patient has had a recent invasive surgical procedure. Therefore, only a small percentage of selected stroke patients are qualified to receive t-PA.
Obstructive emboli have also been mechanically removed from various sites in the vasculature for years. Mechanical therapies have involved capturing and removing the clot, dissolving the clot, disrupting and suctioning the clot, and/or creating a flow channel through the clot. One of the first mechanical devices developed for stroke treatment is the MERCI Retriever System (Concentric Medical, Redwood City, Calif.). A balloon-tipped guide catheter is used to access the internal carotid artery (ICA) from the femoral artery. A microcatheter is placed through the guide catheter and used to deliver the coil-tipped retriever across the clot and is then pulled back to deploy the retriever around the clot. The microcatheter and retriever are then pulled back, with the goal of pulling the clot, into the balloon guide catheter while the balloon is inflated and a syringe is connected to the balloon guide catheter to aspirate the guide catheter during clot retrieval. This device has had initially positive results as compared to thrombolytic therapy alone.
Other thrombectomy devices utilize expandable cages, baskets, or snares to capture and retrieve clot. Temporary stents, sometimes referred to as stentrievers or revascularization devices, are utilized to remove or retrieve clot as well as restore flow to the vessel. A series of devices using active laser or ultrasound energy to break up the clot have also been utilized. Other active energy devices have been used in conjunction with intra-arterial thrombolytic infusion to accelerate the dissolution of the thrombus. Many of these devices are used in conjunction with aspiration to aid in the removal of the clot and reduce the risk of emboli. Suctioning of the clot has also been used with single-lumen catheters and syringes or aspiration pumps, with or without adjunct disruption of the clot. Devices which apply powered fluid vortices in combination with suction have been utilized to improve the efficacy of this method of thrombectomy. Finally, balloons or stents have been used to create a patent lumen through the clot when clot removal or dissolution was not possible.
Notwithstanding the foregoing, there remains a need for new devices and methods for treating vasculature occlusions in the body, including acute ischemic stroke and occlusive cerebrovascular disease.
There is provided in accordance with one aspect of the present invention a neurovascular catheter having an angled, atraumatic navigational tip. The catheter comprises an elongate flexible tubular body, having a proximal end, a distal end and a side wall defining a central lumen. A distal zone of the tubular body comprises a tubular inner liner; a helical coil surrounding the inner liner and having a distal end, and a tubular jacket surrounding the helical coil, and extending distally beyond the helical coil distal end to terminate in a catheter distal face. A tubular radiopaque marker is embedded in the tubular jacket in between the distal end of the coil and the distal face. The distal face resides on a plane which crosses a longitudinal axis of the tubular body at an angle within the range of from about 35 degrees to about 55 degrees; and the marker has a proximal face that is approximately perpendicular to the longitudinal axis and a distal face that resides on a plane which crosses the longitudinal axis at an angle within the range of from about 35 degrees to about 55 degrees. The distal face defines a leading edge of the tubular body which extends distally of a trailing edge of the tubular body, the leading edge and training edge spaced about 180 degrees apart from each other around the longitudinal axis.
An advance segment of the tubular body extends distally beyond the marker band. The advance segment may have an axial length within the range of from about 1 mm to about 3 mm on the leading edge side of the tubular body. The length of the advance segment on the leading edge side of the tubular body may be greater than the length of the advance segment on the trailing edge side of the tubular body.
The axial length of the marker band on the leading edge side of the tubular body may be at least about 20% longer than the axial length of the marker band on the trailing edge side of the tubular body. The axial length of the marker band on the leading edge side of the tubular body may be within the range of from about 1 mm to about 5 mm. The marker band comprises at least one axial slit.
The tubular liner may be formed by dip coating a removable mandrel. The tubular liner may comprises PTFE. The tubular body may further comprise a tie layer between the inner liner and the helical coil. The tie layer may have a wall thickness of no more than about 0.005 inches, and may extend along at least the most distal 20 cm of the flexible body.
The coil may comprise Nitinol, and may comprise an Austenite state at body temperature. The outer jacket may be formed from at least five discrete axially adjacent tubular segments. In some implementations, the outer jacket may be formed from at least nine discrete axially adjacent tubular segments. The difference in durometer between a proximal one of the tubular segments and a distal one of the tubular segments is at least about 20 D, and in some implementations the difference in durometer between a proximal one of the tubular segments and a distal one of the tubular segments is at least about 30 D.
The tubular body may additionally comprise a tension support for increasing the tension resistance in the distal zone. The tension support may comprise an axially extending filament. The axially extending filament may be carried between the inner liner and the helical coil. The axially extending filament may increase the tensile strength of the tubular body to at least about 2 pounds before failure.
Any feature, structure, or step disclosed herein can be replaced with or combined with any other feature, structure, or step disclosed herein, or omitted. Further, for purposes of summarizing the disclosure, certain aspects, advantages, and features of the embodiments have been described herein. It is to be understood that not necessarily any or all such advantages are achieved in accordance with any particular embodiment disclosed herein. No individual aspects of this disclosure are essential or indispensable. Further features and advantages of the embodiments will become apparent to those of skill in the art in view of the Detailed Description which follows when considered together with the attached drawings and claims.
Referring to
The catheters disclosed herein may readily be adapted for use throughout the body wherever it may be desirable to distally advance a low profile distal catheter segment from a larger diameter proximal segment. For example, axially extendable catheter shafts in accordance with the present invention may be dimensioned for use throughout the coronary and peripheral vasculature, the gastrointestinal tract, the urethra, ureters, Fallopian tubes and other lumens and potential lumens, as well. The telescoping structure of the present invention may also be used to provide minimally invasive percutaneous tissue access, such as for diagnostic or therapeutic access to a solid tissue target (e.g., breast or liver or brain biopsy or tissue excision), delivery of laparoscopic tools or access to bones such as the spine for delivery of screws, bone cement or other tools or implants.
The catheter 10 generally comprises an elongate tubular body 16 extending between a proximal end 12 and a distal functional end 14. The length of the tubular body 16 depends upon the desired application. For example, lengths in the area of from about 120 cm to about 140 cm or more are typical for use in femoral access percutaneous transluminal coronary applications. Intracranial or other applications may call for a different catheter shaft length depending upon the vascular access site, as will be understood in the art.
In the illustrated embodiment, the tubular body 16 is divided into at least a fixed proximal section 33 and an axially extendable and retractable distal section 34 separated at a transition 32.
Referring to
The inner diameter of the distal section 34 may be between about 0.030 inches and about 0.112 inches, between about 0.040 inches and about 0.102 inches, between about 0.045 inches and about 0.097 inches, between about 0.050 inches and about 0.092 inches, between about 0.055 inches and about 0.087 inches, between about 0.060 inches and about 0.082 inches, between about 0.062 inches and about 0.080 inches, between about 0.064 inches and about 0.078 inches, between about 0.066 inches and about 0.076 inches, between about 0.068 inches and about 0.074 inches, or between about 0.070 inches and about 0.072 inches.
The inner diameter and the outer diameter of the distal section 34 may be constant or substantially constant along its longitudinal length. Alternatively, the distal section 34 may be tapered near its distal end. The distal section 34 may be tapered at less than or equal to about 5 cm, about 10 cm, about 15 cm, about 20 cm, about 23 cm, about 25 cm, about 30 cm, about 31 cm, about 35 cm, about 40 cm, about 45 cm, about 50 cm, about 60 cm, or about 70 cm from its distal end. In some embodiments, the taper may be positioned between about 25 cm and about 35 cm from the distal end of the distal section 34.
The inner diameter of the distal section 34 may be tapered or decreased in the distal direction near the distal end to an internal diameter that is less than or equal to about 95%, about 90%, about 85%, about 80%, about 75%, about 70%, about 65%, about 60%, about 55%, or about 50% of the adjacent, untampered internal diameter. In some embodiments, the internal diameter of the tapered distal section 34 may be between about 50% and about 70% of the adjacent, untampered internal diameter. For example, the untapered internal diameter at the proximal end of the distal section 34 may be about 0.071 inches and the tapered internal diameter at the distal end of the distal section 34 may be about 0.035 inches, 0.045 inches, or 0.055 inches. The inner diameter of the distal section 34 may be tapered or increased near the distal end by greater than or equal to about 102%, 104%, 106%, 108%, or more of the internal diameter just proximal to a transition into the taper. The tapered inner diameter of the distal section 34 may be less than or equal to about 0.11 inches, about 0.1 inches, about 0.090 inches, about 0.080 inches, about 0.070 inches, about 0.065 inches, about 0.060 inches, about 0.055 inches, about 0.050 inches, about 0.045 inches, about 0.040 inches, about 0.035 inches, about 0.030 inches, about 0.025 inches, about 0.020 inches, about 0.015 inches, or about 0.010 inches. In some embodiments, the length of the distal tapered portion of the distal section 34 may be between about 25 cm and about 35 cm, between about 25 cm and about 30 cm, between about 30 cm and 35 cm, or approximately 30 cm.
The length of the distal section 34 may be between about 13 cm and about 53 cm, between about 18 cm and about 48 cm, between about 23 cm and about 43 cm, between about 28 cm and about 38 cm, between about 29 cm and about 39 cm, between about 30 cm and about 40 cm, between about 31 cm and about 41 cm, or between about 32 cm and about 42 cm. The length of the distal section 34 may be less than or equal to about 20 cm, about 25 cm, about 30 cm, about 33 cm, about 35 cm, about 40 cm, about 41 cm, about 45 cm, about 50 cm, about 55 cm, about 60 cm, about 70 cm, or about 80 cm. The length of the distal section 34 may depend on the degree of tapering of the internal diameter of the distal section 34.
The proximal end 36 of distal section 34 is provided with a proximally extending pull wire 42. Pull wire 42 extends proximally throughout the length of the tubular body 16, to control 24 which may be carried by manifold 18. Axial movement of control 24 produces a corresponding axial movement of distal section 34 with respect to proximal section 33 as has been discussed. Alternatively, the proximal end of pull wire 42 may exit through a port on manifold 18, such that it may be manually grasped and pulled or pushed by the clinician to extend or retract the distal section 34. The length of the pull wire 42 may be between about 700 mm and about 1556 mm, between about 800 mm and about 1456 mm, between about 850 mm and about 1406 mm, between about 900 mm and about 1356 mm, between about 950 mm and about 1306 mm, between about 1000 mm and about 1256 mm, between about 1020 mm and about 1236 mm, between about 1040 mm and about 1216 mm, between about 1060 mm and about 1196 mm, between about 1080 mm and about 1176 mm, between about 1100 mm and about 1156 mm, between about 1110 mm and about 1146 mm, or between about 1120 mm and about 1136 mm.
Upon distal advance of pull wire 42 to its limit of travel, an overlap 44 remains between the proximal end 36 of distal section 34 and the proximal section 33. This overlap 44 is configured to provide a seal to enable efficient transmission of vacuum from proximal section 33 to distal section 34. Overlap 44 may be provided with any of a variety of additional features to facilitate a seal, such as a gasket, coating or tightly toleranced sliding fit, as described elsewhere herein. Preferably the clearance between the OD of the distal section 34 and ID of the proximal section 33, at least in the vicinity of transition 32, will be no more than about 0.005 inches and preferably no more than about 0.003 inches to provide an effective seal in a blood environment. A larger clearance may be more feasible in embodiments comprising a sealing feature as described elsewhere herein.
Following positioning of the distal end of proximal section 33 within the vasculature, such as within the cervical carotid artery, the control 24 is manipulated to distally advance distal section 34 deeper into the vasculature. For this purpose, the pull wire 42 will be provided with sufficient column strength to enable distal advance of the distal tip 38 as will be discussed below.
The pull wire 42 and distal section 34 may be integrated into a catheter as illustrated in
Referring to
In some embodiments, the central lumen 45 may terminate proximal to the opening of the lumen 40. In some embodiments, the central lumen 45 may terminate distal to the opening of the lumen 40 and/or the proximal end of the distal section 34 (e.g., at a point within the lumen 40). For example, the central lumen 45 may terminate at the distal end of the distal section or just short of the distal end (e.g., no more than approximately 1 cm from the distal end). In some implementations, the portion of the pull wire 42, with or without a central lumen 45, which extends beyond the proximal end of the distal section 34 (e.g., into lumen 40) may decrease in stiffness (durometer) in a distal direction. The pull wire 42 may be relatively stiff along the portion proximal to the proximal end of the distal section 34 in order to provide sufficient pushability of the extension catheter. The stiffness of the portion of the pull wire 42 distal of the proximal end of the distal section 34 may substantially match or be less than the stiffness of the distal section 34 along the length of the distal section 34. The portion of the pull wire 42 distal of the proximal end of the distal section 34 may have a uniform stiffness less than the stiffness of the portion proximal of the proximal end of the distal section 34 or it may have a gradated or gradually decreasing stiffness in the distal direction, decreasing from the stiffness of the portion proximal of the proximal end of the distal section 34. For example, the pull wire 42 may comprise metal along the portion proximal to the proximal end of the distal section 34 and may comprise a polymer, softer than the metal, along the portion distal to the proximal end of the distal section 34. The portion distal to the proximal end, in some embodiments, may be extruded with decreasing stiffness in the distal direction.
Referring to
Alternatively, referring to
In some implementations of the present invention, the distal tip 14 is preferably provided with the capability to dilate beyond the nominal diameter of distal section 34. This provides a conical funnel like tip with an enlarged distal opening, to facilitate introduction of thrombotic material into the lumen 40. See
The flexible petals may be retained in a radially inwardly inclined configuration such as by application of negative pressure via lumen 40 during transluminal navigation of the distal section 34. Upon removal of the negative pressure, the panels may incline radially outwardly in response to a preset bias. Application of pulsatile vacuum may thereafter cause the panels to close radially inwardly to perform the biting function described previously.
The distal funnel opening may be actuated in a variety of other ways as will be apparent to those of skill in the art, such as by providing a pull wire or axially slideable outer or inner sleeve to open and close the funnel in response to mechanical movement of the wire or sleeve. Alternatively the funnel opening may be controlled by rotation of a control wire or tubular sleeve relative to the distal section 34, to activate an iris or spiral mechanism such as a helical ribbon or wire carried by the distal tip.
The normal state of the distal funnel may be a cylindrical configuration, and a mechanical, thermal or electrical actuator may be utilized to enlarge the distal funnel opening. Alternatively, the normal state of the funnel may be conical, and a mechanical, thermal or electrical actuator may be utilized to reduce the diameter such as for transluminal navigation. The petals or other wall of the funnel or elements disposed within the wall of the funnel may comprise a shape memory material such as a shape memory polymer or metal alloy such as nitinol, which may be laser cut from tube stock or woven into a fine mesh. The geometry of the funnel may be transformed by application of heat, such as body heat, or heat from a heat source carried by the catheter such as an electrical resistance wire within the wall or adjacent the catheter tip. Heat may alternatively be applied from a heat source introduced by way of central lumen 40, such as a heated fluid, or a removable heater such as an elongate flexible body carrying a resistance coil. Transformation of the funnel from one configuration to the other may alternatively be accomplished by reducing the temperature of the funnel below body temperature such as by introducing a cooled fluid into thermal communication with the funnel tip or providing the catheter or a removable cooling catheter with a Joule—Thomson expansion chamber located near the distal end.
In an alternate configuration, the sidewall of the funnel is provided with an inflatable balloon in the form of a ring or hoop, in communication with an inflation lumen extending throughout the length of the catheter. Introduction of inflation media inflates the annular balloon, transforming the configuration of the funnel tip from a reduced diameter to an enlarged diameter.
In an alternate configuration, the distal tip is biased into the funnel configuration, and restrained into a cylindrical configuration such as for transluminal navigation. When the funnel tip is desired to be enlarged, the restraint can be removed. The restraint may comprise an outer tubular covering membrane or loop configured to be removed by pulling a pull wire in a proximal direction. Alternatively, the restraint may be a bioabsorbable material, which dissolves following a preset amount of time that exceeds the anticipated time from vascular access to reach the final intravascular position.
Referring to
Referring to
Referring to
The proximal end 12 of catheter 10 is additionally provided with a manifold 18 having one or more access ports as is known in the art. Generally, manifold 18 is provided with a proximal port such as a guidewire port 20 in an over-the-wire construction, and at least one side port such as aspiration port 22. Alternatively, the aspiration port 22 may be omitted if the procedure involves removal of the guidewire proximally from the guidewire port 20 following placement of the aspiration catheter, and aspiration through the guidewire port. Additional access ports and lumen may be provided as needed, depending upon the functional capabilities of the catheter. Manifold 18 may be injection molded from any of a variety of medical grade plastics, or formed in accordance with other techniques known in the art.
Manifold 18 may additionally be provided with a control 24, for controlling the axial position of the distal segment 34 of the catheter. Control 24 may take any of a variety of forms depending upon the mechanical structure and desired axial range of travel of the distal segment 34. In the illustrated embodiment, control 24 comprises a slider switch which is mechanically axially movably linked to the distal segment such that proximal retraction of the slider switch 24 produces a proximal movement of the distal segment 34. This retracts the distal segment 34 into the proximal section 33 as illustrated in
Any of a variety of controls may be utilized, including switches, buttons, levers, rotatable knobs, pull/push wires, and others which will be apparent to those of skill in the art in view of the disclosure herein. The control will generally be linked to the distal segment by a control wire 42.
Alternatively, the proximal section 33 and distal section 34 maybe provided as separate devices, in which construction the proximal control may be omitted. The distal end of proximal section 33 may be provided with one or more jaws as has been discussed previously herein, for morcellating or otherwise breaking thrombus or other obstruction into pieces or otherwise facilitating aspiration. The proximal section 33 may additionally be mechanically coupled to or adapted for coupling to a source of vibrational or rotational movement, such as to provide the intermittent or pulsatile movement discussed elsewhere herein to facilitate navigation into the vasculature.
Using axial reciprocation, and/or rotation, and/or biting action of the distal jaws, the clinician may be able to reach the obstruction using proximal section 33. See, for example,
The cerebral circulation is regulated in such a way that a constant total cerebral blood flow (CBF) is generally maintained under varying conditions. For example, a reduction in flow to one part of the brain, such as in acute ischemic stroke, may be compensated by an increase in flow to another part, so that CBF to any one region of the brain remains unchanged. More importantly, when one part of the brain becomes ischemic due to a vascular occlusion, the brain compensates by increasing blood flow to the ischemic area through its collateral circulation.
When an occlusion occurs acutely, for example, in left carotid siphon 70, as depicted in
As illustrated in
The distal end of the proximal section 33 of aspiration catheter 10 is inserted typically through an incision on a peripheral artery over a guidewire and advanced as far as deemed safe into a more distal carotid or intracranial artery, such as the cervical carotid, terminal ICA, carotid siphon, MCA, or ACA. The occlusion site can be localized with cerebral angiogram or IVUS. In emergency situations, the catheter can be inserted directly into the symptomatic carotid artery after localization of the occlusion with the assistance of IVUS or standard carotid doppler and TCD.
If it does not appear that sufficient distal navigation of the proximal section 33 to reach the occlusion can be safely accomplished, the distal section 34 is inserted into the proximal port 20 and/or distally extended beyond proximal section 33 until distal tip 38 is positioned in the vicinity of the proximal edge of the obstruction.
Referring to
Referring to
Aspiration may be applied via lumen 40, either in a constant mode, or in a pulsatile mode. Preferably, pulsatile application of vacuum will cause the distal tip 38 to open and close like a jaw, which facilitates reshaping the thrombus or biting or nibbling the thrombus material into strands or pieces to facilitate proximal withdrawal under negative pressure through lumen 40. Application of aspiration may be accompanied by distal advance of the distal tip 38 into the thrombotic material.
Pulsatile application of a vacuum may oscillate between positive vacuum and zero vacuum, or between a first lower negative pressure and a second higher negative pressure. Alternatively, a slight positive pressure may be alternated with a negative pressure, with the application of negative pressure dominating to provide a net aspiration through the lumen 40. Pulse cycling is discussed in greater detail in connection with
The proximal manifold and/or a proximal control unit (not illustrated) connected to the manifold may enable the clinician to adjust any of a variety of pulse parameters including pulse rate, pulse duration, timing between pulses as well as the intensity of the pulsatile vacuum.
The distal section may thereafter be proximally retracted into proximal section 33 and the catheter proximally retracted from the patient. Alternatively, proximal retraction of the catheter 10 may be accomplished with the distal section 34 in the distally extended position. A vasodilator, e.g., nifedipine or nitroprusside, may be injected through a second lumen to inhibit vascular spasm induced as a result of instrumentation.
Pressure may be monitored by a manometer carried by the catheter or a wire positioned in a lumen of the catheter. A pressure control and display may be included in the proximal control unit or proximal end of the catheter, allowing suction within the vessel to be regulated.
Focal hypothermia, which has been shown to be neuroprotective, can be administered by perfusing hypothermic oxygenated blood or fluid. Moderate hypothermia, at approximately 32 to 34° C., can be introduced during the fluid infusion. Perfusion through a port on manifold 18 can be achieved by withdrawing venous blood from a peripheral vein and processing through a pump oxygenator, or by withdrawing oxygenated blood from a peripheral artery, such as a femoral artery, and pumping it back into the carotid artery.
If continuous and/or intermittent suction fails to dislodge the occlusion, a thrombolytic agent, e.g., t-PA, can be infused through central lumen 40 or a second lumen to lyse any thrombotic material with greater local efficacy and fewer systemic complications. Administration of thrombolytic agent, however, may not be recommended for devices which are inserted directly into the carotid artery due to increased risk of hemorrhage.
The intensity of intermittent or pulsatile vacuum applied to lumen 40 may be adjusted to cause the distal tip 38 of the catheter 10 to experience an axial reciprocation or water hammer effect, which can further facilitate both translumenal navigation as well as dislodging or breaking up the obstruction. Water hammer, or more generally fluid hammer, is a pressure surge or wave caused when a fluid in motion is forced to stop or change direction suddenly, creating a momentum change. A water hammer commonly occurs when a valve closes suddenly at the end of a pipeline system, and a pressure wave propagates in the pipe. A pressure surge or wave is generated inside the lumen 40 of the aspiration catheter 10 when a solenoid or valve closes and stops the fluid flow suddenly, or other pulse generator is activated. As the pressure wave propagates in the catheter 10, it causes the catheter 10 to axially vibrate. Since vibration can reduce surface friction between the outer diameter of the catheter 10 and the inner diameter of the vessel wall, it enables catheter to track through tortuous anatomies as well as assist capturing thrombus.
Referring to
The procedural steps for aspirating a thrombotic occlusion are described as follows. Referring to
Referring to
Referring to
Referring to
Referring to
A preferable, simplified method for aspirating a thrombotic occlusion in accordance with the present invention is described in connection with
Referring to
The transitional guide sheath 1222, the insert catheter 1224, and optionally the first guidewire are tracked up to the aortic arch 1214. See
Referring to
Referring to
Referring to
If the guide sheath 1222 is not able to track deep enough into the distal vasculature to reach the clot or other desired target site, a telescopic extension segment as discussed elsewhere herein may be introduced into the proximal end of sheath 1222 and advanced distally to extend beyond the distal end of the sheath 1222 and thereby extend the reach of the aspiration system. In one implementation of the invention, the extension segment has an ID of about 0.070″.
If thrombotic material is not able to be drawn into the sheath 1222 or extension segment under constant vacuum, pulsatile vacuum may be applied as discussed below. If pulsatile vacuum does not satisfactorily capture the clot, an agitator may be advanced through the sheath 1222 and extension segment to facilitate drawing the clot into the central lumen. Additional details of the agitator and its use are disclosed below.
A pulsatile vacuum pressure aspirator may be used in order to improve effectiveness of aspiration for vascular thrombectomy and to improve catheter trackability through tortuous vasculatures.
Vacuum generator 302 comprises a vacuum pump 304, a vacuum gauge 306, and a pressure adjustment control 308. The vacuum pump 304 generates vacuum. The vacuum gauge 306 is in fluid connection with the vacuum pump 304 and indicates the vacuum pressure generated by the pump 304. The pressure adjustment control 308 allows the user to set to a specific vacuum pressure. Any of a variety of controls may be utilized, including switches, buttons, levers, rotatable knobs, and others which will be apparent to those of skill in the art in view of the disclosure herein.
Vacuum chamber 310 is in fluid connection with the vacuum generator 302 and acts as a pressure reservoir and/or damper. Collection canister 312 is in fluid connection with the vacuum chamber 310 and collects debris. The collection canister 312 may be a removable vial that collects debris or tissues, which may be used for pathologic diagnosis. Vacuum chamber 310 and collection canister 312 may be separate components that are in fluid connection with each other or a merged component. In the illustrated embodiment, the vacuum chamber 310 and the collection canister 312 is a merged component and is in fluid connection with the vacuum generator 302.
Solenoid valve 314 is located in the fluid connection path between a luer or other connector configured to releasably connect to an access port of the catheter 10 and the vacuum chamber 310/collection canister 312. The solenoid valve 314 controls the fluid flow from the catheter 10 to the vacuum chamber 310/collection canister 312.
Pulsatile vacuum pressure aspirator 300 may comprise frequency modulator 316 for control of the solenoid valve 314. The frequency modulator 316 generates different electrical wave frequencies and forms, which are translated into the movement of the solenoid valve 314 by the valve controller 318. The wave forms generated from the frequency modulator 316 comprise sinusoidal, square, and sawtooth waves. The wave forms generated from the frequency modulator 316 typically have frequencies less than about 500 Hz, in some modes of operation less than about 20 Hz or less than about 5 Hz. The wave forms have duty cycles ranging from 0%, in which the solenoid valve 314 is fully shut, to 100%, in which the solenoid valve 314 is fully open.
Valve controller 318 modulates the solenoid valve 314 on and off. The valve controller 318 may be electrically or mechanically connected to the solenoid valve 314. Any of a variety of controls may be utilized, including electrical controllers, switches, buttons, levers, rotatable knobs, and others which will be apparent to those of skill in the art in view of the disclosure herein. The valve controller 318 may be mechanically controlled by users or may be electrically controlled by the frequency modulator 316. The frequency modulator 316 and the valve controller 318 may be separate components that are electrically or mechanically connected or a merged component.
Remote control 320 enables physicians to control the frequency modulator 316 and/or the valve controller 318 for various purposes, such as turning the valve on/off, selecting different wave frequencies, and selecting different wave forms, while manipulating the catheter 10 at the patient side. Remote control 320 may be in wired or wireless communication with aspirator 300.
By tuning frequency, duty cycle, and wave form, one skilled in the art may match or approximate the resonating frequency to the natural frequency of the catheter. This may further enhance the efficacy of aspiration. The natural frequency of the catheter is typically less than about 260 Hz.
In another embodiment, shown in
In yet another embodiment, shown in
Tortuous vasculature is a common reason for failure to treat vasculature occlusions in the body due to inability to track the catheter to the location of the disease. Navigating catheters through tortuous anatomy such as neurovasculature can be a challenge. The catheter has to be very soft as not to damage the vessel wall. At the same time, it also has to be able to negotiate multiple tight turns without kinking. In addition, it has to have sufficient column strength to transmit force axially for advancing through the vasculature. All these performance characteristics are competing design requirements. It is difficult to optimize one performance characteristic without sacrificing the others.
Reducing friction between the inner diameter of the vessel and the outer diameter of the catheter can minimize axial force required to advance catheter through tortuous vasculature. Therefore, the column strength of the catheter may be traded off for optimizing other performance requirements of the catheter. An example of a method to reduce friction between the inner diameter of the blood vessel and the outer diameter of the catheter is to apply a thin layer of coating, usually hydrophilic in nature, to the outer diameter of the catheter to reduce its surface friction coefficient while in vivo.
In addition or as an alternative to the water hammer construction discussed above, axial mechanical vibration or shock waves may be propagated to or generated at the distal end of the catheter using a variety of vibration generators, such as spark gap generators, piezoelectric pulse generators, electric solenoids, rotational shaft (wire) having one or more bends or carrying an eccentric weight, or any of a variety of other impulse generating sources well understood for example in the lithotripsy arts. Mechanical shock wave or pulse generators may be built into the proximal manifold 18, and or mechanically coupled to the manifold or proximal catheter shaft as desired. Preferably, controls are provided on the manifold or on a proximal control coupled to the manifold, to enable the clinician to vary the intensity and time parameters of the mechanical pulses. Shock waves may be propagated along the proximal section 33 to assist in translumenal advance, and/or distal section 34 by way of pull wire 42, depending upon the desired clinical performance.
In an embodiment shown in
In the illustrated embodiment, the proximal end 602 of the vibrating device 600 may be connected to a vacuum pressure source such as a vacuum generator. The proximal connector 604 is attached to the housing 606. In at least one embodiment, the proximal connector 604 may be a luer connector. The distal end 608 of the vibrating device 600 is connected to the catheter 10. The distal connector 610 is held in place by a flexible seal 612 that is attached to the housing 606. In at least one embodiment, the distal connector 610 may be a luer connector. The flexible seal 612 allows the distal connector 610 to move longitudinally as well as transversely. The flexible tubing links the proximal connector 604 and the distal connector 610, creating an aspiration channel 614 for the fluid to travel through.
The vibrating device has a controller 616 to turn on/off the vibrating action as well as to vary its frequency. In this embodiment, the controller 616 is drawn as a sliding switch. Any of a variety of controls may be utilized, including electrical controllers, switches, buttons, levers, rotatable knobs, and others which will be apparent to those of skill in the art in view of the disclosure herein.
A vibration generator such as a motor 618 has an eccentrically mounted inertial weight on its shaft generating vibration. Any of a variety of motors may be used, including an electric motor, an electro-magnetic actuator, and a piezoelectric transducer. The frequency of the vibration is related to the RPM of the motor 618. A driving circuit 620 is connected to the motor 618 and the controller 616 and drives the motor 618 at different RPMs based on the manipulation of the controller 616. In the illustrated embodiment, the circuit 620 drives the motor 618 at different RPMs based on the position of the sliding switch. A battery 622 is connected to and powers the driving circuit 620 and the motor 618.
The motor 618 may be mounted perpendicularly to the length of the aspiration channel 614 to create longitudinal vibration. Also, a mechanical cam may be attached to the motor 618 to create larger magnitude longitudinal reciprocating motion. The frequency range generated by the electric motor is typically less than about 85 Hz. To achieve sonic frequencies in the range from about 85 Hz to about 260 Hz, one might replace the electric motor with an electro-magnetic actuator. To achieve ultrasonic frequencies in the range of about 20 Hz to about 1.6 MHz, one might employ a piezoelectric transducer.
In yet another embodiment, shown in
Alternatively, the stylet 702 may have an asymmetric weight such as a bead at a distal vibration zone or at its distal end. The stylet 702 may comprise a monofilament or braided or woven filaments or wires.
In another alternative, the stylet 702 may have a heater (e.g., an electric coil) at its distal end that facilitates the dissolution of the thrombus or changes the size of the thrombus that is aspirated into the catheter.
The proximal end of the stylet is attached to a motor driver 704 capable of generating rotational and or axially reciprocating motion at various frequencies to form a motor driver-stylet assembly 700. The assembly 700 has a controller 706 to turn on/off the rotating action as well as to vary its frequency. In this embodiment, the controller 706 is drawn as an on/off button. Any of a variety of controls may be utilized, including electrical controllers, switches, buttons, levers, rotatable knobs, and others which will be apparent to those of skill in the art in view of the disclosure herein. The proximal luer 708 or other connector of the catheter 10 reversibly attaches the catheter 10 to the motor driver 804.
Once the catheter 10 has reached its intended location, the entire motor driver-stylet assembly 700 may be detached and removed from the catheter 10 leaving a central aspiration lumen.
In patients with vertebral artery occlusions, treatment with angioplasty can result in complications due to embolization of the occlusive lesion downstream to the basilar artery. Emboli small enough to pass through the vertebral arteries into the larger basilar artery are usually arrested at the top of the basilar artery, where it bifurcates into the posterior cerebral arteries. The resulting reduction in blood flow to the ascending reticular formation of the midbrain and thalamus produces immediate loss of consciousness. The devices described herein can be used to remove thromboembolic material from the vertebral artery or more distally such as in M1, M2, or M3 arteries.
Agitators for providing vibratory assistance for navigation and/or assisting in the capture and aspiration of debris are described further in connection with
In one implementation of the invention, the agitator and drive system are configured as a stand-alone device. Once the distal section 34 (
The agitator 1900 may be rotated manually or via a motor 1906 driven from the catheter 1902's proximal end to rotate or translate the distal end of the agitator 1900. The driver 1906 may be connected to the proximal end of the agitator 1900 either permanently or removably. The driver 1906 may be a manual driver that is manually controlled such as a guidewire torquer. The driver 1906 may be a motorized driver. The motorized driver may be manually controlled with respect to one or more factors such as rotational direction (CCW/CW), speed, duration, etc. The motorized driver may be automatically controlled with respect to one or more factors such as direction (CCW/CW), speed, duration, etc. In one mode, the rotational direction of the agitator is periodically reversed.
The automatically controlled driver may comprise an actuator, and actuating the actuator may execute a pre-programmed series of steps. The actuator may be a button, a dial, a knob, a switch, a lever, a valve, a slide, a keypad, or any combinations thereof. The driver 1906 may also be under synchronized control, in which the driver 1906 drives the agitator 1900 in synchronization with aspiration and media injection. The agitator 1900 may be configured to promote motion at the distal end to help engage and move the clot.
Media may be infused into/around the clot area to help liberate the clot from the vasculature.
The agitator 1900 comprises a distal end 1912, a proximal end 1914 and a distal tip 1905. The proximal end 1914 of the agitator 1900 has a cross-section and/or wall thickness that is large enough to transmit the torque required to rotate the distal end 1912 of the agitator 1900 when placed in the catheter 1902, within the curved vasculature. The outer diameter of the agitator 1900 may be from about 0.25 mm to about 0.65 mm, from about 0.3 mm to about 0.6 mm, from about 0.35 mm to about 0.55 mm, from about 0.4 mm to about 0.5 mm, from about 0.42 mm to about 0.48 mm, or from about 0.44 mm to about 0.46 mm. In case of the hypo tube 1904, the wall thickness of the hypo tube 1904 may be from about 0.01 mm to about 0.29 mm, from about 0.05 mm to about 0.25 mm, from about 0.1 mm to about 0.2 mm, from about 0.12 mm to about 0.18 mm, from about 0.13 mm to about 0.17 mm, or from about 0.14 mm to about 0.16 mm.
The agitator 1900 may additionally be provided with a guide tube 1910, such as a hypo tube, to allow the agitator to spin, or axially or rotationally reciprocate, while constraining a proximal drive segment of the agitator 1900 against lateral motion. A distal end 1911 of guide tube 1910 may be positioned within about 25 cm or within about 20 cm or 15 cm or less of the distal end of the agitator 1900, depending upon desired performance. The distal section of the agitator 1900, extending beyond distal end 1911 of guide tube 1910, is laterally unconstrained within the ID of distal segment 34 and available to agitate and facilitate aspiration of material into and through the central lumen.
The diameter of the agitator 1900 may be constant along its longitudinal length. The diameter of the agitator 1900 may increase or decrease along its longitudinal length to coincide with features of the catheter 1902. In one implementation, the diameter of the agitator 1900 decreases in the distal direction along its longitudinal length by at least one step or tapered zone to provide increasing flexibility.
The distal end 1912 of the agitator 1900 may be straight. Alternatively, the distal end 1912 of the agitator 1900 may be curved or formed into different shapes to interact with the clot.
The agitator 1900 may be comprise a single, uniform material or multiple materials. The materials of the agitator 1900 may be processed (e.g., heat treatment/annealing) to give varying properties for the local performance requirements. The agitator 1900 may be structured to provide flexibility while exhibiting high torque transmission. The agitator 1900 may made of Nitinol, 304 Stainless Steel, 316 LVM Stainless Steel, PTFE, Parylene, or any combinations thereof. At least a portion of the surface of the agitator 1900 may be coated. The entire length of the agitator 1900 may be coated. The coating on the agitator 1900 may provide lubrication between the ID wall of the catheter 1902 and the agitator 1900. In a case that an intermediate hypotube is placed between the wall of the catheter 1902 and the agitator 1900, e.g., constraining tube 1910 or tubular pull wire 42, the coating on the agitator 1900 may provide lubrication between the intermediate hypotube and the proximal drive portion of the agitator 1900. The coating materials of the wire or hypo tube 1904 include PTFE, Parylene, Teflon, or any combinations thereof.
Any of the ID or OD of any of the catheter shafts or other catheter components disclosed herein may be provided with a lubricious coating or may be made from a lubricious material. For example, a hydrophilic polymer such as Polyacrylamide, PEO, thermoplastic starch, PVP, copolymers of hydrophilic polymer can be extruded with hydrophobic polymers such as PEO soft segmented polyurethane blended with Tecoflex. The lubricious coating or the lubricious material may include surface modifying additive (SMA) during melt processing. The lubricious coating or the lubricious material contributes to at least ease of navigation, lower ID skin friction, or better clot removal. In some embodiments, post processing wire ebeam, Gamma, UV, etc. additionally may be desirable to expose to moisture, temperature, etc. Catheters may be made from PEO impregnated polyurethanes such as Hydrothane, Tecophilic polyurethane for both OD and ID lubricity and inherent thromboresistant property without requiring a secondary coating process.
Referring to
Referring to
Referring to
Referring to
Alternatively, the distal tip 2110 of the catheter 2102 may move or wiggle by pulsed media jets existing one or more holes near the distal end of the hypo tube 2124. The hypo tube 2124 has an inside lumen extending along the longitudinal length of the hypo tube 2124. One or more side holes 2128 may be placed near the distal end of the hypo tube 2124 and allow fluid communication between the lumen of the hypo tube 2124 and the outside of the hypo tube 2124 (i.e., the lumen of the catheter 2102). Media (e.g. saline) may be introduced under pressure into the proximal end of the hypo tube 2124, through the lumen of the hypo tube 2124, and then through the one or more holes of the hypo tube 2124. When media is injected into the hypo tube 2124 in a pulsed manner, pulsed media jets eject from the holes of the hypo tube 2124 and transmit forces on the wall of the catheter 2102, resulting in a wiggle motion of the catheter 2102. The hypo tube 2124 may additionally rotate (e.g., via a driver 2106) to facilitate a wiggle motion of the catheter 2102.
Referring to
As the hypo tube 2204 rotates, the hypo tube 2204 ejects media and simultaneously makes the distal tip of the catheter 2202 wriggle. When the distal tip of the catheter 2202 wriggles by the rotation of the hypo tube 2204, the wriggle of the catheter 2202 may push the clot 2214 from side to side, and the hypo tube 2204 simultaneously ejects media at the interface between the clot 2214 and the catheter 2202, providing a lubricious avenue for the clot 2214 to release and flow into the catheter 2202.
With or without injection of media, rotation of the motion segment 1909 helps to break up or reshape the thrombus and facilitate entry into the aspiration lumen. In certain situations, the clot can be aspirated completely within the central lumen. In other situations, the clot may only be able to be partially drawn into the central lumen, such as illustrated in
Referring to
Referring to
Referring to
Referring to
In the illustrated implementation, the distal restraint or restriction element comprises at least one projection extending radially inwardly from the inside surface of the tubular body, configured to restrict the inside diameter of the aspiration lumen and provide an interference surface to engage a distal face carried by the agitator. The restraint may comprise one or two or three or four or more projections such as tabs, or, as illustrated, may comprise an annular ring providing a continuous annular proximally facing restraint surface. The proximal bearing surface of the axial restraint may be located within about 50 cm or 30 cm or 15 cm from the distal end of the tubular body. In order to optimize alignment of the distal rotatable tip 450 with the distal port of the catheter, and decouple that axial alignment from the tortuosity of the vascular path which otherwise changes the relative axial positions of the catheter exit port and the tip, the proximal bearing surface of the axial restraint is often within the range of from about 3 mm to about 50 mm, in some implementations about 5 mm to about 20 mm and in one implementation from about 6 mm to about 14 mm from the distal port on the catheter.
The distal restraint may be a metallic (e.g., nitinol, stainless steel, aluminum, etc.) circular band or ring or protrusion 2402 mounted on or built into a sidewall 2403 of the catheter near the distal tip, the distal restriction element 2402 extending into the ID of the catheter. Further, the distal restriction element 2402 may be radiopaque for visibility under fluoroscopy. The distal restriction element 2402 carries a proximally facing surface 2405 for example an annular circumferential bearing surface that extends into the inner diameter of the catheter to interface with a distal stopper 2414 on the rotating assembly. For example, the distal stopper 2414 may be a circular feature on the rotating assembly which interfaces with the distal restriction element 2402 of the catheter to stop the distal advancement and prevent distal tip displacement beyond the catheter distal tip.
In one implementation, in its relaxed form prior to securing within the catheter lumen, the ring 2402 is a C-shaped or cylinder shaped with an axially extending slit to form a split ring. The ring 2402 is compressed using a fixture that collapses the ring to a closed circle shape, allowing it to slide inside the (e.g., 0.071″) catheter. When the ring is released from the fixture, the ring expands radially to the largest diameter permitted by the inside diameter of the catheter. The radial force of the ring engages the insider surface of the catheter and resists axial displacement under the intended use applied forces. In another implementation, the ring is a fully closed, continuous annular structure (like a typical marker band) and its distal end is slightly flared in a radially outwardly direction to create a locking edge. The ring is inserted into the catheter from the distal end. The flared section with the locking edge keeps the ring in place when axial force is applied from the proximal side.
Referring to
As illustrated further in
The torque coil 2412 may additionally be provided with a proximal radiopaque marker and/or connector such as a solder joint 438. In the illustrated implementation, the proximal connector 438 is in the form of an annular silver solder band, surrounding the inner coil 415 and abutting a proximal end of the outer coil 2413.
The axial length of the torque coil 2412 is within the range of from about 10 mm to about 50 mm and in some embodiments within the range of from about 20 mm to about 40 mm. The distal transition 436 and the distal stopper 2414 may be positioned within the range of from about 5 mm to about 20 mm and in some implementations within the range of from about 8 mm to about 12 mm from the proximal end of the distal cap 2420.
Referring to
The distal stopper 2414 carries a plurality of distal surfaces 446, such as on the slider 441. The distal surface 446 is configured to slidably engage a proximal surface of a stop on the inside diameter of the delivery catheter, such as a proximally facing surface 2405 on a radially inwardly extending annular flange or ring 2402. See
Referring to
The agitator tip 2416 is provided with a distal end 450, and a proximally extending helical flange 452 that increases in diameter in the proximal direction. The flange may extend at least about one full revolution and generally less than about five or four or three revolutions about an extension of the longitudinal axis of the core wire 2410. The helical flange is provided with a rounded, blunt edge 454, configured for slidably rotating within the tubular delivery catheter.
The maximum OD for the tip 2416 is generally at least about 0.005 inches and preferably at least about 0.01 inches or 0.015 inches or more smaller than the ID of the catheter aspiration lumen through which the embolism treatment system 2401 is intended to advance, measured at the axial operating location of the tip 2416 when the stopper 2414 is engaged with the stop ring. For example, a tip having a maximum OD in the range of from about 0.050-0.056 inches will be positioned within a catheter having a distal ID within the range of from about 0.068 to about 0.073 inches, and in one embodiment about 0.071 inches. With the tip centered in the lumen of the delivery (aspiration) catheter, the tip is spaced from the inside wall of the catheter by a distance in all directions of at least about 0.005 inches and in some embodiments at least about 0.007 inches or 0.010 inches or more.
Thus an unimpeded flow path is created in the annular space between the maximum OD of the tip, and the ID of the catheter lumen. This annular flow path cooperates with the vacuum and helical tip to grab and pull obstructive material into the catheter under rotation and vacuum. The annular flow path is significantly greater than any flow path created by manufacturing tolerances in a tip configured to shear embolic material between the tip and the catheter wall.
Additional aspiration volume is obtained as a result of the helical channel defined between each two adjacent threads of the tip. A cross sectional area of the helical flow path of a tip having a maximum OD in the range of from about 0.050 to about 0.056 inches will generally be at least about 0.0003 square inches, and in some embodiments at least about 0.00035 or at least about 0.000375 inches. The total aspiration flow path across the helical tip is therefore the sum of the helical flow path through the tip and the annular flow path defined between the OD of the tip and the ID of the catheter lumen.
The combination of a rounded edge 454 on the thread 452, slow, manual rotation of the tip through less than about 20 or 10 or 5 or less rotations, and space between the thread 452 and catheter inside wall enables aspiration both through the helical channel formed between adjacent helical threads as well as around the outside of the tip 2416 such that the assembly is configured for engaging and capturing embolic material but not shearing it between a sharp edge and the inside wall of the catheter. Once engaged, additional rotation draws the aspiration catheter distally over the clot to ensconce a proximal portion of the clot to facilitate proximal retraction and removal. The axial length of the tip 2416 including the attachment sleeve 2417 is generally less than about 6 mm, and preferably less than about 4 mm or 3 mm or 2.5 mm or less depending upon desired performance.
The pitch of the thread 452 may vary generally within the range of from about 35 degrees to about 80 degrees, depending upon desired performance. Thread pitches within the range of from about 40-50 degrees may work best for hard clots, while pitches within the range of from about 50 to 70 degrees may work best for soft clots. For some implementations the pitch will be within the range of from about 40-65 degrees or about 40-50 degrees.
The tip 2416 may additionally be provided with a feature for attracting and/or enhancing adhesion of the clot to the tip. For example, a texture such as a microporous, microparticulate, nanoporous or nanoparticulate surface may be provided on the tip, either by treating the material of the tip or applying a coating. A coating of a clot attracting moiety such as a polymer or drug may be applied to the surface of the tip. For example, a roughened Polyurathane (Tecothane, Tecoflex) coating may be applied to the surface of at least the threads and optionally to the entire tip. The polyurethane may desirably be roughened such as by a solvent treatment after coating, and adhesion of the coating to the tip may be enhanced by roughening the surface of the tip prior to coating.
Alternatively, the core wire 2410 may be provided with an insulating coating to allow propagation of a negative electric charge to be delivered to the tip to attract thrombus. Two conductors may extend throughout the length of the body, such as in a coaxial configuration. Energy parameters and considerations are disclosed in U.S. Pat. No. 10,028,782 to Orion and US patent publication No. 2018/0116717 to Taff et al., the disclosures of each of which are hereby expressly incorporated by reference in their entireties herein. As a further alternative, the tip 2416 can be cooled to cryogenic temperatures to produce a small frozen adhesion between the tip and the thrombus. Considerations for forming small cryogenic tips for intravascular catheters are disclosed in US patent publication Nos. 2015/0112195 to Berger et al., and 2018/0116704 to Ryba et al., the disclosures of each of which are hereby expressly incorporated by reference in their entireties herein.
Referring to
In an embodiment having a torque coil 2412 with an OD of about 0.028 inches, the OD of the stopper 2414 is about 0.068 inches. The wall thickness of the struts is generally less than about 0.015 inches and typically less than about 0.010 inches and in some implementations less than about 0.008 inches or 0.005 inches or less. The struts 440 have a length in the catheter axial direction that is sufficient to support the assembly against distal travel beyond the catheter stop ring, and may be at least about 50% of the OD of the stopper 2414. In a stopper 2414 having an OD of about 0.68 inches, the struts 2440 have an axial length of at least about 0.75 mm or 0.95 mm.
Referring to
One method for using the system described above is described below. An 0.088 LDP guide catheter is introduces and if possible, advanced until catheter tip is slightly proximal to occlusion site. An 0.071 aspiration catheter of
The aspiration catheter is at this point anchored to the clot. The 0.088 LDP catheter is then advanced over the aspiration catheter which functions like a guidewire, until the 0.088 catheter reaches the face of the clot. Vacuum is applied to the 088 LDP guide catheter using a vacuum source such as a VacLok syringe. The aspiration catheter with clot secured on its tip, is proximally retracted through the 088 LDP guide, while maintaining position of the 088 LDP at the occlusion site.
If flow has not been restored through the 088 LDP, the core wire may be removed from the aspiration catheter. If necessary, the helical tip of the core wire may be wiped to remove residual clot, and the core wire and aspiration catheter returned to the occlusion site to repeat the clot retrieval sequence until flow is restored. Once flow is restored, remove the 0.088 LDP guide catheter.
Referring to
In the first step as shown in
Referring to
The rotating hemostasis valve (RHV) 2620 comprises a distal connector 2630 at its distal end, which is configured to couple the rotating hemostasis valve to the proximal end of the catheter (not shown). The distal connector 2630 may be a luer connector. The rotating hemostasis valve 2620 comprises a central lumen along its longitudinal length, through which a proximal section of agitator 1900 passes. The rotating hemostasis valve 2620 further comprises an aspiration port 2622, which bifurcates from the central lumen of the rotating hemostasis valve 2620 and provides the aspiration flow path. The rotating hemostasis valve 2620 comprises a RHV seal 2626 and a proximal rotating collar 2628 at its proximal end. The proximal rotating collar 2628 controls the opening and closing of the RHV seal 2626. The user (e.g., physician) can either open or close the RHV seal 2626 by rotating the proximal rotating collar 2628. The RHV seal 2626, when closed, does not allow fluid communication between the inside lumen distal of the RHV seal 262 and the inside lumen proximal of the RHV seal 262. At the same time, the RHV seal 262 does not hamper the longitudinal movement of the distal portion of the proximal drive assembly 2602 inside the rotating hemostasis valve 2629.
Experiments showed that as the wire or hypo tube 1900 is rotated back and forth (i.e., oscillating), the distal end of the agitator 1900 changes its position relative to the catheter. The distal end of the agitator 1900 was shown to foreshorten/lengthen as the wire or hypo tube 2624 wound/unwound within the catheter due to the rotation of the agitator 1900 or the increase/decrease in media injection pressure. The proximal rotating collar 2628 and the RHV seal 2626 permit the user (e.g., physician) to account for this variance in length and advance/withdraw the agitator 1900 relative to the catheter and fix it in place by simply moving the proximal drive assembly 2602 in/out of the rotating hemostasis valve 2629. If the agitator 1900 is preloaded into the catheter, the distance may be initially set at a nominal position. In another embodiment, the proximal rotating collar 2628 of the rotating hemostasis valve 2620 may be part of the proximal drive assembly 2602.
The proximal drive assembly 2602 comprises a proximal drive connector 2604, to which the driver is connected, and a media injection port 2610, into which media is injected. The proximal drive assembly also comprises a bearing 2606, which allows free rotation of the proximal drive connector 2604 with respect to the proximal drive assembly 2602. The proximal drive connection 2604 may be coupled to the proximal end of the agitator 1900 such that the rotation of the proximal drive connector 2604 is translated to the rotation of the wire or hypo tube 1900. The proximal drive assembly further comprises a drive tube seal 2608, which prevents fluid communication between the inside lumen (of the proximal drive assembly 2602) distal of the drive tube seal 2608 and the inside lumen proximal of the drive tube seal 2608.
Referring to
The system for retrieving clots comprises the aspiration catheter; the agitator 1900 longitudinally extendable inside the lumen of the aspiration catheter; and the driver connectable to the proximal end of the agitator 1900 (e.g., via the rotating hemostasis valve or the proximal drive assembly) with or without a synchronization port. The system may allow impulse aspiration and/or impulse injection of media. The media may comprise water, saline solution, or media with an effective amount of drug (e.g., drug therapy such as heparin, plavix, tPA). The components may be manipulated individually or in a synchronized manner using predetermined operating parameters (e.g., for synchronized aspiration, injection, and rotation).
The method of retrieving a clot may comprise providing the aspiration catheter, the agitator longitudinally extending or positionable inside the lumen of the aspiration catheter; and the driver coupled to the proximal end of the agitator; placing the catheter adjacent to the clot; attempting to aspirate clot; if not successful, advancing an agitator distally through the catheter; activating the driver to rotate the agitator and loosen the clot; optionally injecting media through the agitator to lubricate the clot and/or create a media jet from the distal end of the agitator, configured to help aspirate the clot; transporting the clot proximally inside the lumen of the catheter by applying the vacuum at the proximal end of the catheter; and optionally pulsing the vacuum. As pieces of the clot separate, transport may be assisted by the rotating agitator and/or injection media.
In order to detach a more stubborn clot, aspiration, media injection, and/or rotation of the wire or hypo tube may be timed. Building up a surplus of media around the clot will form a plug. When aspiration is activated and/or pulsed, the vacuum can draw the “plug” proximally inside the lumen of the wire or hypo tube like a syringe plunger. A higher local vacuum around the clot is maintained, and more momentum is added to the “plug” as more media is added. Timing the rotation of the wire or hypo tube with aspiration and media injection may help wiggle or fatigue the clot and detach it out of the vasculature.
Any of the catheter shaft or sections of the catheter shaft or telescoping extensions in accordance with the present invention may comprise a multi-layer construct having a high degree of flexibility and sufficient push ability to reach deep into the cerebral vasculature, such as at least as deep as the petrous, cavernous, or cerebral segment of the internal carotid artery (ICA).
In one example, referring to
A braid such as a 75 ppi stainless steel braid 3010 may thereafter be wrapped around the inner liner 3014 through a proximal zone up to a distal transition 3011. From the distal transition 3011 to the distal end of the catheter 3000, a coil 3024 comprising a shape memory material such as a Nitinol alloy may thereafter be wrapped around the inner liner 3014. In one implementation, the Nitinol coil has a transition temperature below body temperature so that the Nitinol resides in the austinite (springy) state at body temperature. Adjacent loops or filars of the coil 3024 may be closely tightly wound in a proximal zone with a distal section having looser spacing between adjacent loops. In an embodiment having a coil section 3024 with an axial length of at least between about 20% and 30% of the overall catheter length, (e.g., 28 cm coil length in a 110 cm catheter shaft 3000), at least the distal 1 or 2 or 3 or 4 cm of the coil will have a spacing that is at least about 130%, and in some implementations at least about 150% or more than the spacing in the proximal coil section. In a 110 cm catheter shaft 3000 having a Nitinol coil the spacing in the proximal coil may be about 0.004 inches and in the distal section may be at least about 0.006 inches or 0.007 inches or more. In embodiments comprising an extension catheter, the distal extendable section of the catheter may be constructed according to the foregoing. The length of the coil 3024 may be proportioned to the length of the extendable catheter segment or the total (e.g., extended) length of the catheter 3000. The coil 3024 may extend from a distal end of the extendable segment over at least about 50%, 60%, 70%, 80%, or 90% of the length of the extendable segment. In some embodiments, the catheter 3000 or the extendable segment may not comprise a braid and the coil 3024 may extend to the proximal end of the extendable segment (100% of the length).
The distal end of the coil 3024 can be spaced proximally from the distal end of the inner liner 3014, for example, to provide room for an annular radiopaque marker 3040. The coil 3024 may be set back proximally from the distal end, in some embodiments, by approximately no more than 1 cm, 2 cm, or 3 cm. In one embodiment, the distal end of the catheter 3000 is provided with a beveled distal surface 3006 residing on a plane having an angle of at least about 10° or 20° and in one embodiment about 30° with respect to a longitudinal axis of the catheter 3000. The radiopaque marker 3040 may reside in a plane that is transverse to the longitudinal axis. Alternatively, at least the distally facing edge of the annular radiopaque marker 3040 may be an ellipse, residing on a plane which is inclined with respect to the longitudinal axis to complement the bevel angle of the distal surface 3006. Additional details are described in connection with
After applying the proximal braid 3010, the distal coil 3024 and the RO marker 3040 an outer Jacket 3020 maybe applied such as a shrink wrap tube to enclose the catheter body 3000. The outer shrink-wrapped sleeve 3020 may comprise any of a variety of materials, such as polyethylene, polyurethane, polyether block amide (e.g., PEBAX™) nylon or others known in the art. Sufficient heat is applied to cause the polymer to flow into and embed the proximal braid and distal coil.
In one implementation, the outer shrink wrap jacket 3020 is formed by sequentially advancing a plurality of short tubular segments 3022, 3026, 3028, 3030, 3032, 3034, 3036, 3038 concentrically over the catheter shaft subassembly, and applying heat to shrink the sections on to the catheter 3000 and provide a smooth continuous outer tubular body. The foregoing construction may extend along at least the most distal 10 cm, and preferably at least about the most distal 20 cm, 25 cm, 30 cm, 35 cm, 40 cm, or more than 40 cm of the catheter body 3000. The entire length of the outer shrink wrap jacket 3020 may be formed from tubular segments and the length of the distal tubular segments (e.g., 3022, 3026, 3028, 3030, 3032, 3034, 3036, 3038) may be shorter than the one or more tubular segments forming the proximal portion of the outer shrink wrap jacket 3020 in order to provide steeper transitions in flexibility toward the distal end of the catheter 3000.
The durometer of the outer wall segments may decrease in a distal direction. For example, proximal segments such as 3022 and 3026, may have a durometer of at least about 60 or 70 D, with gradual decrease in durometer of successive segments in a distal direction to a durometer of no more than about 35 D or 25 D or lower. A 25 cm section may have at least about 3 or 5 or 7 or more segments and the catheter 3000 overall may have at least about 6 or 8 or 10 or more distinct flexibility zones. The distal 1 or 2 or 4 or more segments 3036, 3038, may have a smaller OD following shrinking than the more proximal segments 3022-3034 to produce a step down in OD for the finished catheter body 3000. The length of the lower OD section 3004 may be within the range of from about 3 cm to about 15 cm and in some embodiments is within the range of from about 5 cm to about 10 cm such as about 7 or 8 cm, and may be accomplished by providing the distal segments 3036, 3038 with a lower wall thickness.
Referring to
At least one of the one or more axially extending filaments 3042 may proximally extend along the length of the catheter wall from within about 1.0 cm from the distal end of the catheter to less than about 5 cm from the distal end of the catheter, less than about 10 cm from the distal end of the catheter, less than about 15 cm from the distal end of the catheter, less than about 20 cm from the distal end of the catheter, less than about 25 cm from the distal end of the catheter, less than about 30 cm from the distal end of the catheter, less than about 35 cm from the distal end of the catheter, less than about 40 cm from the distal end of the catheter, or less than about 50 cm from the distal end of the catheter.
The one or more axially extending filaments 3042 may have a length greater than or equal to about 50 cm, greater than or equal to about 40 cm, greater than or equal to about 35 cm, greater than or equal to about 30 cm, greater than or equal to about 25 cm, greater than or equal to about 20 cm, greater than or equal to about 15 cm, greater than or equal to about 10 cm, or greater than or equal to about 5 cm.
At least one of the one or more axially extending filaments 3042 may have a length less than or equal to about 50 cm, less than or equal to about 40 cm, less than or equal to about 35 cm, less than or equal to about 30 cm, less than or equal to about 25 cm, less than or equal to about 20 cm, less than or equal to about 15 cm, less than or equal to about 10 cm, or less than or equal to about 5 cm. At least one of the one or more axially extending filaments 3042 may extend at least about the most distal 50 cm of the length of the catheter, at least about the most distal 40 cm of the length of the catheter, at least about the most distal 35 cm of the length of the catheter, at least about the most distal 30 cm of the length of the catheter, at least about the most distal 25 cm of the length of the catheter, at least about the most distal 20 cm of the length of the catheter, at least about the most distal 15 cm of the length of the catheter, at least about the most distal 10 cm of the length of the catheter, or at least about the most distal 5 cm of the length of the catheter.
In some implementations, the filament extends proximally from the distal end of the catheter along the length of the coil 24 and ends proximally within about 5 cm or 2 cm or less either side of the transition 3011 between the coil 3024 and the braid 3010. The filament may end at the transition 3011, without overlapping with the braid 3010.
In another embodiment, the most distal portion of the catheter 3000 may comprise a durometer of less than approximately 35 D (e.g., 25 D) to form a highly flexible distal portion of the catheter and have a length between approximately 25 cm and approximately 35 cm. The distal portion may comprise one or more tubular segments of the same durometer (e.g., segment 3038). A series of proximally adjacent tubular segments may form a transition region between a proximal stiffer portion of the catheter 3000 and the distal highly flexible portion of the catheter. The series of tubular segments forming the transition region may have the same or substantially similar lengths, such as approximately 1 cm.
The relatively short length of the series of tubular segments may provide a steep drop in durometer over the transition region. For example, the transition region may have a proximal tubular segment 3036 (proximally adjacent the distal portion) having a durometer of approximately 35 D. An adjacent proximal segment 3034 may have a durometer of approximately 55 D. An adjacent proximal segment 3032 may have a durometer of approximately 63 D. An adjacent proximal segment 3030 may have a durometer of approximately 72 D.
More proximal segments may comprise a durometer or durometers greater than approximately 72 D and may extend to the proximal end of the catheter or extension catheter segment. For instance, an extension catheter segment may comprise a proximal portion greater than approximately 72 D between about 1 cm and about 3 cm. In some embodiments, the proximal portion may be about 2 cm long. In some embodiments, the most distal segments (e.g., 3038-3030) may comprise PEBAX™ and more proximal segments may comprise a generally stiffer material, such as Vestamid®.
The inner diameter of the catheter 3000 or catheter extension segment may be between approximately 0.06 and 0.08 inches, between approximately 0.065 and 0.075 inches, or between 0.068 and 0.073 inches. In some embodiments, the inner diameter is approximately 0.071 inches.
In some embodiments, the distal most portion may taper to a decreased inner diameter as described elsewhere herein. The taper may occur approximately between the distal highly flexible portion and the transition region (e.g., over the most proximal portion of the distal highly flexible portion). The taper may be relatively gradual (e.g., occurring over approximately 10 or more cm) or may be relatively steep (e.g., occurring over less than approximately 5 cm). The inner diameter may taper to an inner diameter between about 0.03 and 0.06 inches. For example, the inner diameter may be about 0.035 inches, about 0.045 inches, or about 0.055 inches at the distal end of the catheter 3000. In some embodiments, the inner diameter may remain constant, at least over the catheter extension segment.
In some embodiments, the coil 3024 may extend proximally from a distal end of the catheter 3000 along the highly flexible distal portion ending at the distal end of the transition region. In other embodiments, the coil 3024 may extend from a distal end of the catheter to the proximal end of the transition region, to a point along the transition region, or proximally beyond the transition region. In other embodiments, the coil 3024 may extend the entire length of the catheter 3000 or catheter extension segment as described elsewhere herein. The braid 3010, when present, may extend from the proximal end of the coil 3024 to the proximal end of the catheter 3000 or catheter extension segment.
The one or more axially extending filaments 3042 may be placed near or radially outside the tie layer 3012 or the inner liner 3014. The one or more axially extending filaments 3042 may be placed near or radially inside the braid 3010 and/or the coil 3024. The one or more axially extending filaments 3042 may be carried between the inner liner 3014 and the helical coil 3024.
When more than one axially extending filaments 3042 are placed in the catheter wall, the axially extending filaments 3042 may be placed in a radially symmetrical manner. For example, the angle between the two axially extending filaments 3042 with respect to the radial center of the catheter may be about 180 degree. Alternatively, depending on desired clinical performances (e.g., flexibility, trackability), the axially extending filaments 3042 may be placed in a radially asymmetrical manner. The angle between any two axially extending filaments 3042 with respect to the radial center of the catheter may be less than about 180 degree, less than or equal to about 165 degree, less than or equal to about 150 degree, less than or equal to about 135 degree, less than or equal to about 120 degree, less than or equal to about 105 degree, less than or equal to about 90 degree, less than or equal to about 75 degree, less than or equal to about 60 degree, less than or equal to about 45 degree, less than or equal to about 30 degree, less than or equal to about 15 degree, less than or equal to about 10 degree, or less than or equal to about 5 degree.
The one or more axially extending filaments 3042 may be made of materials such as Kevlar, Polyester, Meta-Para-Aramide, or any combinations thereof. At least one of the one or more axially extending filaments 3042 may comprise a single fiber or a multi-fiber bundle, and the fiber or bundle may have a round or rectangular cross section. The terms fiber or filament do not convey composition, and they may comprise any of a variety of high tensile strength polymers, metals or alloys depending upon design considerations such as the desired tensile failure limit and wall thickness. The cross-sectional dimension of the one or more axially extending filaments 3042, as measured in the radial direction, may be no more than about 1%, 2%, 3%, 4%, 5%, 6%, 7%, 8%, 9%, 10%, 11%, 12%, 13%, 14%, 15%, 20%, 25%, or 30% of that of the catheter 3000. The cross-sectional dimension of the one or more axially extending filaments 3042, as measured in the radial direction, may be no more than about 0.001 inches, about 0.002 inches, about 0.003 inches, about 0.004 inches, about 0.005 inches, about 0.006 inches, about 0.007 inches, about 0.008 inches, about 0.009 inches, about 0.010 inches, about 0.015 inches, about 0.020 inches, about 0.025 inches, or about 0.030 inches.
The one or more axially extending filaments 3042 may increase the tensile strength of the distal zone of the catheter to at least about 1 pound, at least about 2 pounds, at least about 3 pounds, at least about 4 pounds, at least about 5 pounds, at least about 6 pounds, at least about 7 pounds, at least about 8 pounds, or at least about 10 pounds or more.
Any of the aspiration catheters or tubular extension segments disclosed herein, whether or not an axial filament is included, may be provided with an angled distal tip. Referring to
A reinforcing element 3122 such as a braid or spring coil is embedded in an outer jacket 3124 which may extend the entire length of the distal catheter tip 3110.
The advance segment 3114 terminates distally in an angled face 3126, to provide a leading side wall portion 3128 having a length measured between the distal end 3130 of the marker band 3116 and a distal tip 3132. A trailing side wall portion 3134 of the advance segment 3114, has an axial length in the illustrated embodiment of approximately equal to the axial length of the leading side wall portion 3128 as measured at approximately 180 degrees around the catheter from the leading side wall portion 3128. The leading side wall portion 3128 may have an axial length within the range of from about 0.1 mm to about 5 mm and generally within the range of from about 1 to 3 mm. The trailing side wall portion 3134 may be at least about 0.1 or 0.5 or 1 mm or 2 mm or more shorter than the axial length of the leading side wall portion 3128, depending upon the desired performance.
The angled face 3126 inclines at an angle A within the range of from about 45 degrees to about 80 degrees from the longitudinal axis of the catheter. For certain implementations, the angle is within the range of from about 55 degrees to about 65 degrees or within the range of from about 55 degrees to about 65 degrees from the longitudinal axis of the catheter. In one implementation the angle A is about 60 degrees. One consequence of an angle A of less than 90 degrees is an elongation of a major axis of the area of the distal port which increases the surface area of the port and may enhance clot aspiration or retention. Compared to the surface area of the circular port (angle A is 90 degrees), the area of the angled port is generally at least about 105%, and no more than about 130%, in some implementations within the range of from about 110% and about 125% and in one example is about 115%.
In the illustrated embodiment, the axial length of the advance segment is substantially constant around the circumference of the catheter, so that the angled face 3126 is approximately parallel to the distal surface 3136 of the marker band 3116. The marker band 3116 has a proximal surface approximately transverse to the longitudinal axis of the catheter, producing a marker band 3116 having a right trapezoid configuration in side elevational view. A short sidewall 3138 is rotationally aligned with the trailing side wall portion 3134, and has an axial length within the range of from about 0.2 mm to about 4 mm, and typically from about 0.5 mm to about 2 mm. An opposing long sidewall 3140 is rotationally aligned with the leading side wall portion 3128. Long sidewall 3140 of the marker band 3116 is generally at least about 10% or 20% longer than short sidewall 3138 and may be at least about 50% or 70% or 90% or more longer than short sidewall 3138, depending upon desired performance. Generally the long sidewall 3140 will have a length of at least about 0.5 mm or 1 mm and less than about 5 mm or 4 mm.
The marker band may have at least one and optionally two or three or more axially extending slits throughout its length to enable radial expansion. The slit may be located on the short sidewall 3138 or the long sidewall 3140 or in between, depending upon desired bending characteristics. The marker band may comprise any of a variety of radiopaque materials, such as a platinum/iridium alloy, with a wall thickness preferably no more than about 0.003 inches and in one implementation is about 0.001 inches.
The marker band zone of the assembled catheter will have a relatively high bending stiffness and high crush strength, such as at least about 50% or at least about 100% less than proximal segment 18 but generally no more than about 200% less than proximal segment 3118. The high crush strength may provide radial support to the adjacent advance segment 3114 and particularly to the leading side wall portion 3128, to facilitate the functioning of distal tip 3132 as an atraumatic bumper during transluminal advance and to resist collapse under vacuum. The proximal segment 3118 preferably has a lower bending stiffness than the marker band zone, and the advance segment 3114 preferably has even a lower bending stiffness and crush strength than the proximal segment 3118.
The advance segment 3114 may comprise a distal extension of the outer jacket 3124 and optionally the inner liner 3120, without other internal supporting structures distally of the marker band 3116. Outer jacket may comprise extruded Tecothane. The advance segment 3114 may have a bending stiffness and radial crush stiffness that is no more than about 50%, and in some implementations no more than about 25% or 15% or 5% or less than the corresponding value for the proximal segment 3118.
A support fiber 3142 as has been discussed elsewhere herein extends through at least a distal portion of the length of the proximal segment 3118. As illustrated, the support fiber 3142 may terminate distally at a proximal surface of the marker band 3116 and extend axially radially outwardly of the tubular liner 3120 and radially inwardly from the support coil 3122. Fiber 3142 may extend substantially parallel to the longitudinal axis, or may be inclined into a mild spiral having no more than 10 or 7 or 3 or 1 or less complete revolutions around the catheter along the length of the spiral. The fiber may comprise a high tensile strength material such as a multifilament yarn spun from liquid crystal polymer such as a Vectran multifilament LCP fiber.
Referring to
The intraluminal catheter 3200 incorporates characteristics of the side wall construction of the catheter 3000 described herein. The axial length of the tubular extension segment may be less than about 50% and typically less than about 25% of the length of the catheter 3000. The axial length of the tubular extension segment will generally be at least about 10 cm or 15 cm or 20 cm or 25 cm or more but generally no more than about 70 cm or 50 cm or 30 cm.
Referring to
Referring to
Performance metrics of a catheter include back-up support, trackability, pushability, and kink resistance. Back-up support means ability of the catheter to remain in position within anatomy and provide a stable platform through which endoluminal devices may advance. Referring to
Trackability means ability of the catheter to track further distally than other catheters (e.g., to M1). For example, a catheter that can reach a cerebral segment of the internal carotid artery (ICA) has better trackability than a catheter that can reach a cavernous or petrous segment of the ICA. Trackability of the catheter may be improved by using a catheter wall with low durometer or modulus or by adding a coating (e.g., a hydrophilic coating) on at least a portion of the catheter wall. In one embodiment, the hydrophilic coating may be placed along the distal most region of the catheter. The hydrophilic coating on the catheter may extend to about 1 cm, about 5 cm, about 10 cm, about 15 cm, or about 20 cm from the distal end of the catheter. The region with lower durometer or modulus may locate at the distal most region of the catheter. The region with lower durometer or modulus may extend to about 1 cm, about 5 cm, about 10 cm, about 15 cm, or about 20 cm from the distal end of the catheter.
Pushability means rigidity of the catheter sufficient to push through anatomy without “buckling”. Pushability of the catheter may be improved by increasing its durometer or modulus. Pushability of the catheter may also be improved by providing a proximal region with high durometer or modulus and a distal region with low durometer or modulus. A transition region of the catheter in which durometer or modulus changes along its longitudinal length (e.g., decreasing durometer or modulus from the proximal end to the distal end) may begin at about 50%, 60%, 70%, 75%, 80%, or more of the length of the catheter from its proximal end.
Kink resistance means resistance of the catheter to kinking. In addition, if the catheter does kink, kink resistance of the catheter helps it return to its original shape. Kink resistance is important in the distal segment of the catheter, which is more prone to kinking than the proximal segment. Kink resistance of the catheter may be improved by adding one or more NiTi coils (or a coil at least portion of which is Nitinol) to the catheter wall.
Catheters according to the present invention have a flexural load that is substantially constant along the longitudinal length near the proximal end and a rapidly decreasing flexural load near the distal end. In a catheter having a length of about 125 cm, the catheters may have a flexural load greater than or equal to about 1.0 lbF, about 1.5 lbF, about 2.0 lbF, about 2.5 lbF, about 3.0 lbF, or about 3.5 lbF at about 85 cm from the proximal end. The catheters may have a flexural load less than or equal to about 2.5 lbF, about 2.0 lbF, about 1.5 lbF, about 1.0 lbF, or about 0.5 lbF at about 95 cm from the proximal end. The catheters may have a flexural load less than or equal to about 1.5 lbF, about 1.0 lbF, about 0.75 lbF, about 0.5 lbF, about 0.25 lbF, or about 0.1 lbF at about 105 cm from the proximal end. The catheters may have a flexural load less than or equal to about 1.0 lbF, about 0.75 lbF, about 0.5 lbF, about 0.4 lbF, about 0.3 lbF, about 0.2 lbF, or about 0.1 lbF at about 115 cm from the proximal end. For catheters having different lengths, the foregoing dimensions can be scaled from the distal end of the catheter as a percentage of catheter length.
In certain implementations constructed in accordance with
In other embodiments, the catheters may have a flexural load greater than or equal to about 1.0 lbF, about 1.5 lbF, about 2.0 lbF, about 2.5 lbF, about 3.0 lbF, or about 3.5 lbF at about 60 cm from the proximal end. The catheters may have a flexural load less than or equal to about 2.0 lbF, about 1.5 lbF, about 1.0 lbF, or about 0.5 lbF at about 70 cm from the proximal end. The catheters may have a flexural load less than or equal to about 1.0 lbF, about 0.75 lbF, about 0.5 lbF, about 0.4 lbF, about 0.3 lbF, about 0.2 lbF, or about 0.1 lbF at about 80 cm from the proximal end. The catheters may have a flexural load less than or equal to about 1.0 lbF, about 0.75 lbF, about 0.5 lbF, about 0.4 lbF, about 0.3 lbF, about 0.2 lbF, or about 0.1 lbF at about 90 cm from the proximal end.
The catheters may have a transition region, in which its flexural load changes by greater than or equal to about 1.0 lbF, about 1.5 lbF, about 2.0 lbF, about 2.5 lbF, about 3.0 lbF, or about 3.5 lbF. The longitudinal length of the transition region may be less than or equal to about 20 cm, about 15 cm, about 10 cm, about 5 cm, about 3 cm, or about 1 cm.
Compared to Neuron Max (Penumbra, Inc.) 3402, catheters according to the present invention (e.g., 3404, 3406, 3408, 3410) have comparable modulus near its proximal end. This way, the catheters according to the present invention provide back-up support comparable to that of Neuron Max. In addition, the catheters have modulus that falls more rapidly near the transition region (between the proximal end and the distal end) than that of Neuron Max.
Compared to Ace 68 catheter (Penumbra) 3412, Ace 64 catheter (Penumbra) 3414, Benchmark 71 catheter (Penumbra) 3416, and Sofia Plus (MicroVention) 3418, the catheters according to the present inventions have greater modulus near its proximal end and comparable modulus near its distal end. This way, the catheters according to the present invention provide superior back-up support with comparable trackability compared to conventional catheters. The catheters according to the present invention may achieve this modulus profile even when their inner diameters (and thus lumen volumes) are greater than or equal to those of Ace 68, Ace 64, Benchmark 71, and Sofia Plus, which range from 0.064 inch to 0.071 inch.
Referring to
At least one transition zone 214 is provided on the tubular body 202. Transition zone 214 is controllably transformable between a relatively stiff configuration and a relatively flexible configuration. The access sheath 200 may be distally advanced through tortuous anatomy with at least one transition zone 214 in a relatively stiff configuration as desired such as to provide column strength or to facilitate the introduction of instruments therethrough. The transition zone 214 may be controllably transformed to a relatively flexible configuration as desired, such as to navigate tight bends in the vasculature.
In the illustrated embodiment, three transition zones 214 are shown. However, one or two or three or four or more transition zones may be utilized, depending upon the desired clinical performance. The transition zone 214 may be from about 1 cm to about 20 or 30 cm or more in length. In certain embodiments, the transition zones will be within the range of from about 2 cm to about 10 cm in length. The length and location of the transition zones may depend upon the target anatomy for the access catheter, and can be located accordingly.
Referring to
Alternatively, an electrically conductive polymer may be utilized to form the sidewall 216. Electrically conductive coatings may alternatively be printed, laminated, embedded or otherwise applied to the outside, the inside, or laminated within an inner layer and an outer layer of the sidewall 216. In at least one embodiment, the resistance of the heater 218 may be calibrated to a specific heating temperature, such as 40-80° C., for a predetermined voltage level of the power source. This may eliminate the need for a thermocouple and prevent potential overheating.
One or more electrical conductors may extend between the transition zone 214 and a proximal activation port 215, adapted for coupling to a source of electricity from an external controller. In a mono polar construction, a single conductor for each transition zone 214 may extend proximally to the activation port 215. A second conductor may lead to or comprise an electrically conductive surface on the tubular body 202, for conducting electricity through the body of the patient to an external electrode as is understood in the art. Alternatively, in a bipolar embodiment, each transition zone 214 may be provided with at least two electrical conductors extending proximally to the activation port 215.
At least the transition zone comprises a biocompatible material that is relatively firm at body temperature (e.g., 37° C.) but transitions to a relatively soft, flexible material upon application of heat. Typical suitable materials have a relatively low melting point so as to be softenable at temperatures not so high as to damage living vessels. In any event the material will have a softening point or a glass transition temperature above body temperature, with a melting point significantly above body temperature and above the temperature reached by activating the heating element 218. In one embodiment, the biocompatible material preferably has a glass transition temperature from about 40° C. to about 80° C. Suitable materials may include polymers with a polymer chain orientation that causes the polymer to break when heated.
Examples of suitable biostable materials are polymers, typically thermoplastic polymers such as polyolefins and polyurethanes and most other biocompatible polymers. Typical suitable bioabsorbable materials include polyglycolide (PGA), poly(L-lactide) (PLLA), poly(.epsilon.-caprolactone) (PCL), and blends or combinations thereof. Polyglycolide for example has a glass transition temperature between 35-40° C., such having a considerably higher melting point.
Typical operating (softening) temperatures in this regard are on the order of between about 40 and 80° C., often between about 40° C. and 60° C. to cause a softening transition of the transition zone 214, and allow a transition back to a firm state upon removal of power and reversion of the transition zone 214 back to body temperature. A temperature higher than about 80° C. may be acceptable for a short period of time, depending upon the total energy delivered. Any temperature to which the heater 218 is elevated is limited by what the body of the patient can handle without causing damage to the vessel wall or causing thrombus to form. For this reason, it may be desirable to remain within the lower end of the temperature ranges illustrated above if the eligible polymers exhibit suitable flexibility at the softening point temperature and suitable firmness at the lower body temperature.
Upon being heated, the biocompatible energy-activated transition zone 214 softens so that it may be navigated through a tight bend for example. The material is to be softened enough by the energy application so that it increases in flexibility, but retains the structural integrity necessary for navigation and retains its shape so that upon interruption of the heat source it will harden back to its original configuration. To maintain the integrity of the tubular body, side wall 216 may be provided with flexible reinforcing structures such as a helically wrapped wire, ribbon or polymeric strand such as polyimide, or other braid or weave as is understood in the neurovascular catheter arts. A resistance coil or other resistance filaments may also provide the mechanical reinforcing function while the transition zone is in the softened state.
Heating may alternatively be provided by positioning a heat source such as a resistance heat element carried by a heater catheter within the central lumen 212. Once the catheter has reached its final position in the vasculature, the heater catheter may be proximally withdrawn from the central lumen 212, which is now available for aspiration or to receive a distal section 34 therethrough. In either heater configuration, a power source may be provided within or electrically coupled to a proximal manifold on the aspiration catheter or heater catheter.
Access for the catheter of the present invention can be achieved using conventional techniques through an incision on a peripheral artery, such as right femoral artery, left femoral artery, right radial artery, left radial artery, right brachial artery, left brachial artery, right axillary artery, left axillary artery, right subclavian artery, or left subclavian artery. An incision can also be made on right carotid artery or left carotid artery in emergency situations.
Avoiding a tight fit between the guidewire 40 and inside diameter of guidewire lumen 28 enhances the slidability of the catheter over the guidewire. In ultra small diameter catheter designs, it may be desirable to coat the outside surface of the guidewire 40 and/or the inside surface of the wall defining lumen 38 with a lubricous coating to minimize friction as the catheter 10 is axially moved with respect to the guidewire 40. A variety of coatings may be utilized, such as Paralene, Teflon, silicone, polyimide-polytetrafluoroethylene composite materials or others known in the art and suitable depending upon the material of the guidewire or inner tubular wall 38.
Aspiration catheters of the present invention which are adapted for intracranial applications generally have a total length in the range of from 60 cm to 250 cm, usually from about 135 cm to about 175 cm. The length of the proximal segment 33 will typically be from 20 cm to 220 cm, more typically from 100 cm to about 120 cm. The length of the distal segment 34 will typically be in the range from 10 cm to about 60 cm, usually from about 25 cm to about 40 cm.
The catheters of the present invention may be composed of any of a variety of biologically compatible polymeric resins having suitable characteristics when formed into the tubular catheter body segments. Exemplary materials include polyvinyl chloride, polyethers, polyamides, polyethylenes, polyurethanes, copolymers thereof, and the like. In one embodiment, both the proximal body segment 33 and distal body segment 34 will comprise a polyvinyl chloride (PVC), with the proximal body segment being formed from a relatively rigid PVC and the distal body segment being formed from a relatively flexible, supple PVC. Optionally, the proximal body segment may be reinforced with a metal or polymeric braid or other conventional reinforcing layer.
The proximal body segment will exhibit sufficient column strength to permit axial positioning of the catheter through a guide catheter with at least a portion of the proximal body segment 33 extending beyond the guide catheter and into the patient's vasculature. The proximal body segment may have a shore hardness in the range from 50 D to 100 D, often being about 70 D to 80 D. Usually, the proximal shaft will have a flexural modulus from 20,000 psi to 1,000,000 psi, preferably from 100,000 psi to 600,000 psi. The distal body segment 34 will be sufficiently flexible and supple so that it may navigate the patient's more narrow distal vasculature. In highly flexible embodiments, the shore hardness of the distal body segment 34 may be in the range of from about 20 A to about 100 A, and the flexural modulus for the distal segment 34 may be from about 50 psi to about 15,000 psi.
The catheter body may further comprise other components, such as radiopaque fillers; colorants; reinforcing materials; reinforcement layers, such as braids or helical reinforcement elements; or the like. In particular, the proximal body segment may be reinforced in order to enhance its column strength and torqueability (torque transmission) while preferably limiting its wall thickness and outside diameter.
Usually, radiopaque markers will be provided at least at the distal end 14 and the transition region 32 at the distal end of proximal segment 33. One radiopaque marker comprises a metal band which is fully recessed within or carried on the outside of the distal end of the proximal body segment 33. Suitable marker bands can be produced from a variety of materials, including platinum, gold, and tungsten/rhenium alloy. Preferably, the radiopaque marker band will be recessed in an annular channel to produce a smooth exterior surface.
The proximal section 33 of tubular body 16 may be produced in accordance with any of a variety of known techniques for manufacturing interventional catheter bodies, such as by extrusion of appropriate biocompatible polymeric materials. Alternatively, at least a proximal portion or all of the length of tubular body 16 may comprise a polymeric or metal spring coil, solid walled hypodermic needle tubing, or braided reinforced wall, as is known in the microcatheter arts.
In a catheter intended for neurovascular applications, the proximal section 33 of body 16 will typically have an outside diameter within the range of from about 0.117 inches to about 0.078 inches. In one implementation, proximal section 33 has an OD of about 0.104 inches and an ID of about 0.088 inches. The distal section 34 has an OD of about 0.085 inches and an ID of about 0.070 inches.
Diameters outside of the preferred ranges may also be used, provided that the functional consequences of the diameter are acceptable for the intended purpose of the catheter. For example, the lower limit of the diameter for any portion of tubular body 16 in a given application will be a function of the number of fluid or other functional lumen contained in the catheter, together with the acceptable minimum aspiration flow rate and collapse resistance.
Tubular body 16 must have sufficient structural integrity (e.g., column strength or “pushability”) to permit the catheter to be advanced to distal locations without buckling or undesirable bending of the tubular body. The ability of the body 16 to transmit torque may also be desirable, such as to avoid kinking upon rotation, to assist in steering. The tubular body 16, and particularly the distal section 34, may be provided with any of a variety of torque and/or column strength enhancing structures. For example, axially extending stiffening wires, spiral wrapped support layers, braided or woven reinforcement filaments may be built into or layered on the tubular body 16. See, for example, U.S. Pat. No. 5,891,114 to Chien, et al., the disclosure of which is incorporated in its entirety herein by reference.
In many applications, the proximal section 33 will not be required to traverse particularly low profile or tortuous arteries. For example, the proximal section 33 will be mostly or entirely within the relatively large diameter guide catheter. The transition 32 can be located on the catheter shaft 16 to correspond approximately with or beyond the distal end of the guide catheter.
For certain applications, such as intracranial catheterizations, the distal section 34 is preferably at least about 5 cm or 10 cm long and small enough in diameter to pass through vessels as low as 3 mm or 2 mm or lower. The distal section may have a length of at least about 20 cm or 30 cm or 40 cm or more, depending upon the intended target vessel or treatment site.
The distal section, whether carried within the proximal section as an integrated device, or is a separate device to be inserted into the proximal section during a procedure, is substantially shorter than the proximal section. When the distal end of the distal section and the distal end of the proximal section are axially aligned, the proximal end of the distal section is spaced distally apart from the proximal end of the proximal section. The control element such as a control wire or tube spans the distance between the proximal end of the distal section and the proximal manifold or proximal control.
In the foregoing configuration, the proximal end of the distal section will generally be spaced apart distally from the proximal end of the proximal section by at least about 25%, and in some embodiments at least about 50% or 70% or more of the length of the proximal section.
There is provided in according with one aspect, a telescoping catheter, comprising: an elongate, flexible tubular body, comprising a proximal section having at least one lumen and a distal section axially movably positioned within the lumen; and a control for advancing the distal section from a first, proximally retracted position within the proximal section to a second, extended position, extending distally beyond the proximal section; and an active tip on the distal end of the distal section, comprising a distal opening that is movable between a smaller and a larger configuration.
In one aspect of present disclosure, the control comprises a pull wire extending through the proximal section. In another aspect of present disclosure, the distal section is distally advanceable to extend beyond the proximal section for a distance of at least about 10 cm. In yet another aspect of present disclosure, the distal section is distally advanceable to extend beyond the proximal section for a distance of at least about 25 cm.
In one aspect of present disclosure, the distal opening is movable in response to movement of a control wire. In another aspect of present disclosure, the distal opening is movable between a smaller and a larger configuration in response to application of vacuum to the lumen. In yet another aspect of present disclosure, the size of the distal opening is changed by lateral movement of a side wall on the distal section. In yet another aspect of present disclosure, the distal opening comprises at least one movable jaw. In another aspect of present disclosure, the distal end of the distal section comprises a duck bill valve configuration.
In one aspect of present disclosure, the telescoping catheter may further comprise a controller for applying intermittent vacuum to the lumen. The controller may be configured to apply pulses of vacuum to the lumen spaced apart by spaces of neutral pressure. The controller may be configured to alternate between applying pulses of higher negative pressure and lower negative pressure. The distal tip of the catheter may axially reciprocate in response to application of pulses of vacuum to the lumen.
In accordance with one aspect, there is provided a system for aspirating a vascular occlusion from a remote site, comprising: an elongate, flexible tubular body, comprising at least one central lumen extending along its longitudinal length; an agitator extendable through the central lumen of the tubular body to position a distal end of the agitator near a distal end of the tubular body; a driver connectable to a proximal end of the agitator and configured to actuate the agitator; and a vacuum port near the proximal end of the tubular body and in fluid communication with the central lumen of the tubular body.
In one aspect of present disclosure, the agitator comprises an elongate tube. The agitator may comprise a wire extending through the elongate tube and having at least one bend near its distal end. In another aspect of present disclosure, the agitator comprises a proximal end, a distal end, and a loop at the distal end. In yet another aspect of present disclosure, the driver is configured to rotate the agitator cyclically in alternating directions.
In one aspect of present disclosure, the agitator comprises: at least one lumen along its longitudinal length, an influent port near its proximal end configured to allow fluid communication between the lumen of the agitator and a source of media, and at least one effluent port configured to allow fluid communication between the lumen of the agitator and the central lumen of the tubular body. The system for aspirating a vascular occlusion may further comprise a control, for expressing media from the effluent port of the agitator into the central lumen of the tubular body. The distal portion of the tubular body may be configured to vibrate in a transverse direction in response to the injection of media.
In one aspect of present disclosure, the system for aspirating a vascular occlusion further comprises a controller for applying a pulsatile vacuum cycle to the central lumen. In another aspect of present disclosure, the system for aspirating a vascular occlusion further comprises a rotating hemostasis valve coupled to the proximal end of the tubular body, the rotating hemostasis valve comprising: at least one main lumen along its longitudinal length, through which the proximal portion of the agitator is configured to pass, and an aspiration lumen bifurcating from the main lumen and provided with a vacuum port. In yet another aspect of present disclosure, the system further comprises a proximal drive assembly coupled to the proximal end of the tubular body, the proximal drive assembly comprising: at least one main lumen along its longitudinal length for receiving the agitator; a media injection port, into which media is injected, in fluid communication with the central lumen of the tubular body, and a proximal drive connection at the proximal end, which operably connects between the agitator and the driver.
In accordance with another aspect, there is provided a method of aspirating a vascular occlusion from a remote site, comprising: providing the system for aspirating a vascular occlusion; placing the tubular body adjacent to the occlusion; activating the driver to actuate the agitator and loosen the occlusion; and drawing occlusive material into the central lumen by applying vacuum to the central lumen. In one aspect of present disclosure, there is provided a method of aspirating a vascular occlusion from a remote site, comprising: providing the system for aspirating a vascular occlusion; placing the tubular body adjacent to the occlusion; activating the driver to cause the distal tip of the agitator to rotate; injecting media through the influent port; and aspirating occlusive material into the central lumen by applying vacuum to the central lumen. Actuation of the driver, aspiration, and media injection may be synchronized to facilitate the removal and/or aspiration of the occlusion.
In accordance with one aspect, there is provided a method of aspirating a vascular occlusion from a remote site, comprising: advancing a guidewire to a site at least as distal as the cavernous segment of the internal carotid artery; advancing a tubular body directly over the guidewire to a site at least as distal as the cavernous segment; removing the guidewire from the tubular body; and aspirating thrombus into the tubular body by applying vacuum to the tubular body. In one aspect of present disclosure, the method of aspirating a vascular occlusion comprises advancing the tubular body at least as distal as the cerebral segment of the internal carotid artery. In another aspect of present disclosure, the method of aspirating a vascular occlusion comprises advancing the guidewire at least as distal as the middle cerebral artery.
In yet another aspect of present disclosure, the method of aspirating a vascular occlusion further comprises providing sufficient back up support to the tubular body to resist prolapse of the tubular body into the aorta. In one aspect, the back up support may be provided by advancing the tubular body over a guidewire having a distal end positioned at least as distal as the cavernous segment of the internal carotid artery, and a diameter at the point the guidewire enters the brachiocephalic artery of at least about 0.030 inches. In another aspect, the back up support may be provided by advancing the tubular body over a guidewire having a distal end positioned at least as distal as the cavernous segment of the internal carotid artery, and a diameter at the point the guidewire enters the brachiocephalic artery of about 0.038 inches. The guidewire may be navigable to at least the cerebral segment of the internal carotid artery by having a distal segment having a diameter of no more than about 0.020 inches. The guidewire may be navigable to at least the cerebral segment of the internal carotid artery by having a distal segment having a diameter of about 0.016 inches. The distal segment may have a length of no more than about 25 cm. The distal segment may have a length of no more than about 20 cm.
In accordance with another aspect, there is provided a method of tracking an aspiration catheter from a femoral access site to at least as distal as the cavernous segment of the internal carotid artery, comprising the steps of: advancing a guidewire from the femoral access site to at least as distal as the cerebral segment of the internal carotid artery, the guidewire having a proximal section having a diameter of at least about 0.030 inches and a distal section having a length of no more than about 25 cm and a diameter of no more than about 0.020 inches; tracking an aspiration catheter directly over the guidewire and to a site at least as distal as the cavernous segment, the aspiration catheter having a distal end and a central lumen at the distal end with a diameter of at least about 0.080 inches and a beveled distal tip. In one aspect of present disclosure, the diameter of the proximal section of the guidewire is about 0.038 inches, and the diameter of the distal section is about 0.016 inches.
In another aspect of present disclosure, a distal segment of the catheter comprises a side wall defining the central lumen, the side wall comprising: a tubular inner liner; a soft tie layer separated from the lumen by the inner liner; a helical coil surrounding the tie layer, adjacent windings of the coil spaced progressively further apart in the distal direction; and an outer jacket surrounding the helical coil, the outer jacket formed from a plurality of tubular segments positioned coaxially about the coil; wherein a proximal one of the tubular segments has a durometer of at least about 60 D and a distal one of the tubular segments has a durometer of no more than about 35 D. The tubular liner may be formed by dip coating a removable mandrel and may comprise PTFE. The tie layer may comprise polyurethane. The tie layer may have a wall thickness of no more than about 0.005 inches and may extend along at least the most distal 20 cm of the flexible body. The coil may comprise a shape memory material.
In accordance with one aspect, there is provided an enhanced flexibility neurovascular catheter, comprising: an elongate flexible body, having a proximal end, a distal end and a side wall defining a central lumen, a distal zone of the side wall comprising: a tubular inner liner; a soft tie layer separated from the lumen by the inner liner; a helical coil surrounding the tie layer, adjacent windings of the coil spaced progressively further apart in the distal direction; and an outer jacket surrounding the helical coil, the outer jacket formed from a plurality of tubular segments positioned coaxially about the coil; wherein a proximal one of the tubular segments has a durometer of at least about 60 D and a distal one of the tubular segments has a durometer of no more than about 35 D. In one aspect of present disclosure, the tubular liner is formed by dip coating a removable mandrel. In another aspect of present disclosure, the tubular liner comprises PTFE.
In yet another aspect of present disclosure, the tie layer comprises polyurethane. The tie layer may have a wall thickness of no more than about 0.005 inches and may extend along at least the most distal 20 cm of the flexible body. In one aspect of present disclosure, the coil comprises a shape memory material. The coil may comprise Nitinol, and the Nitinol may comprise an Austenite state at body temperature.
In one aspect of present disclosure, the outer jacket is formed from at least five discrete tubular segments. The outer jacket may be formed from at least nine discrete tubular segments. The difference in durometer between a proximal one of the tubular segments and a distal one of the tubular segments may be at least about 20 D. The difference in durometer between a proximal one of the tubular segments and a distal one of the tubular segments may be at least about 30 D.
In another aspect of present disclosure, the enhanced flexibility neurovascular catheter, further comprises a tension support for increasing the tension resistance in the distal zone. The tension support may comprise a filament and may comprise an axially extending filament. The axially extending filament may be carried between the inner liner and the helical coil. The axially extending filament may increase the tensile strength to at least about 1 pound, at least about 2 pounds, at least about 3 pounds, at least about 4 pounds, at least about 5 pounds at least about 6 pounds, at least about 7 pounds, at least about 8 pounds, or at least about 10 pounds or more.
In accordance with one aspect, there is provided an enhanced flexibility neurovascular catheter, comprising: an elongate flexible body, having a proximal end, a distal end and a side wall defining a central lumen, a distal zone of the side wall comprising: an outer jacket surrounding a helical coil, the outer jacket formed from a plurality of tubular segments positioned coaxially about the coil; wherein a proximal one of the tubular segments has a durometer of at least about 60 D and a distal one of the tubular segments has a durometer of no more than about 35 D; and an axially extending filament within the side wall, extending at least about the most distal 10 cm of the length of the catheter. The filament may extend at least about the most distal 15 cm of the length of the catheter. The filament may extend at least about the most distal 20 cm of the length of the catheter. The filament may comprise multiple fibers and may extend axially in between the coil and the inner liner.
In one aspect of present disclosure, the side wall further comprises: a tubular inner liner; a soft tie layer separated from the lumen by the inner liner; wherein the helical coil surrounds the tie layer, and adjacent windings of the coil are spaced progressively further apart in the distal direction. The tubular liner may be formed by dip coating a removable mandrel and may comprise PTFE. The tie layer may comprise polyurethane and may have a wall thickness of no more than about 0.005 inches. The tie layer may extend along at least the most distal 20 cm of the flexible body. The coil may comprise a shape memory material and may comprise Nitinol. The Nitinol may comprise an Austenite state at body temperature.
In one aspect of present disclosure, the outer jacket may be formed from at least five discrete tubular segments. In another aspect of present disclosure, the outer jacket may be formed from at least nine discrete tubular segments. The difference in durometer between a proximal one of the tubular segments and a distal one of the tubular segments may be at least about 20 D. The difference in durometer between a proximal one of the tubular segments and a distal one of the tubular segments may be at least about 30 D. In another aspect of present disclosure, the catheter can withstand at least about 3.5 pounds tension before failure. In yet another aspect, the catheter can withstand at least about 5 pounds tension before failure.
In accordance with one aspect, there is provided a method of making a high flexibility distal zone on a neurovascular catheter, comprising the steps of: dip coating a removable mandrel to form a tubular inner layer on the mandrel; coating the tubular inner layer with a soft tie layer; applying a helical coil to the outside of the tie layer; positioning a plurality of tubular segments on the helical coil; the plurality of segments having durometers that decrease in a distal direction; heating the tubular segments to form the high flexibility distal zone on the neurovascular catheter; and removing the mandrel. In one aspect of present disclosure, removing the mandrel step includes axially elongating the mandrel. In another aspect of present disclosure, the method of making a high flexibility distal zone on a neurovascular catheter comprises positioning at least seven segments on the helical coil. In yet another aspect of present disclosure, the method of making a high flexibility distal zone on a neurovascular catheter comprises positioning at least nine segments on the helical coil.
In one aspect of present disclosure, the difference in durometer between a proximal one of the tubular segments and a distal one of the tubular segments is at least about 20 D. The difference in durometer between a proximal one of the tubular segments and a distal one of the tubular segments may be at least about 30 D. The tubular inner layer may comprise PTFE. In another aspect of present disclosure, the tie layer comprises polyurethane. The tie layer may have a wall thickness of no more than about 0.005 inches. The tie layer may extend along at least the most distal 20 cm of the flexible body.
In one aspect of present disclosure, the coil comprises a shape memory material. The coil may comprise Nitinol. The Nitinol may comprise an Austenite state at body temperature. In another aspect of present disclosure, the method of making a high flexibility distal zone on a neurovascular catheter further comprises the step of positioning at least one tensile strength enhancing filament in between the coil and the tie layer prior to heat shrinking the tubular segments. The filament may extend along at least about the most distal 15 cm of the length of the catheter. The filament may extend along at least about the most distal 20 cm of the length of the catheter. The filament may comprise multiple fibers. In yet another aspect of present disclosure, the method of making a high flexibility distal zone on a neurovascular catheter further comprises the step of positioning at least one tensile strength enhancing filament over the tie layer before the applying a helical coil step.
In accordance with one aspect, there is provided a method of aspirating a vascular occlusion from a remote site, comprising the steps of: advancing an elongate tubular body through a vascular access site and into a body vessel, the tubular body comprising a proximal end, a distal end and a central lumen; positioning the distal end at least as far distally as the cavernous segment of the middle cerebral artery; applying vacuum to the lumen to draw thrombus into the lumen; and mechanically disrupting the thrombus to facilitate entry into the lumen.
In one aspect of present disclosure, the mechanically disrupting step comprises introducing vibration at the distal end of the tubular body. The vibration may be introduced by rotating an agitator within the tubular body. The method of aspirating a vascular occlusion may comprise rotating a wire within the tubular body. The method of aspirating a vascular occlusion may comprise rotating a tube within the tubular body and may further comprise the step of introducing media through the tube. The method of aspirating a vascular occlusion may comprise the step of introducing a lubricant through the tube to facilitate advancing thrombus through the lumen and may comprise the step of introducing polyethylene glycol through the tube.
In another aspect of present disclosure, the applying vacuum step comprises applying pulsatile vacuum. In yet another aspect of present disclosure, the advancing an elongate tubular body step is accomplished directly over a guidewire without any intervening tubular bodies. The method of aspirating a vascular occlusion may comprise advancing the tubular body at least as distal as the cavernous segment of the internal carotid artery. The method of aspirating a vascular occlusion may comprise advancing the tubular body at least as distal as the cerebral segment of the internal carotid artery. The method of aspirating a vascular occlusion may comprise advancing the guidewire at least as distal as the middle cerebral artery.
In one aspect of present disclosure, the method of aspirating a vascular occlusion further comprises providing sufficient back up support to the tubular body to resist prolapse of the tubular body into the aorta. The back up support may be provided to the tubular body by advancing the tubular body over a guidewire having a distal end positioned at least as distal as the cavernous segment of the internal carotid artery, and a diameter at the point the guidewire enters the brachiocephalic artery of at least about 0.030 inches. The back up support may be provided to the tubular body by advancing the tubular body over a guidewire having a distal end positioned at least as distal as the cavernous segment of the internal carotid artery, and a diameter at the point the guidewire enters the brachiocephalic artery of about 0.038 inches.
In one aspect of present disclosure, the guidewire is navigable to at least the cerebral segment of the internal carotid artery by having a distal segment having a diameter of no more than about 0.020 inches. The guidewire may be navigable to at least the cerebral segment of the internal carotid artery by having a distal segment having a diameter of about 0.016 inches. In yet another aspect of present disclosure, the method of aspirating a vascular occlusion further comprises the step of introducing an agitator into the tubular body subsequent to the positioning step. A proximal section of the agitator may extend through a constraint tube, and a distal section of the agitator may extend beyond a distal end of the constraint tube.
In accordance with one aspect, there is provided a method of aspirating a vascular occlusion from a remote site, comprising: advancing a guidewire through a vascular access point and transvascularly to a site at least as distal as the cavernous segment of the internal carotid artery; accessing a site at least as distal as the cavernous segment by advancing a combined access and aspiration catheter directly over the guidewire; removing the guidewire; and aspirating thrombus through the combined access and aspiration catheter. In one aspect of present disclosure, the method of aspirating a vascular occlusion comprises advancing the combined access and aspiration catheter at least as distal as the cerebral segment of the internal carotid artery. In another aspect of present disclosure, the method of aspirating a vascular occlusion comprises advancing the guidewire at least as distal as the middle cerebral artery.
In yet another aspect of present disclosure, the method of aspirating a vascular occlusion further comprises providing sufficient back up support to the combined access and aspiration catheter to resist prolapse of the catheter into the aorta. The back up support may be provided to the combined access and aspiration catheter by advancing the combined access and aspiration catheter over a guidewire having a distal end positioned at least as distal as the cavernous segment of the internal carotid artery, and a diameter at the point the guidewire enters the brachiocephalic artery of at least about 0.030 inches. The back up support is provided to the combined access and aspiration catheter by advancing the combined access and aspiration catheter over a guidewire having a distal end positioned at least as distal as the cavernous segment of the internal carotid artery, and a diameter at the point the guidewire enters the brachiocephalic artery of about 0.038 inches.
In one aspect of present disclosure, the guidewire is navigable to at least the cerebral segment of the internal carotid artery by having a distal segment having a diameter of no more than about 0.020 inches. The guidewire may be navigable to at least the cerebral segment of the internal carotid artery by having a distal segment having a diameter of about 0.016 inches. The diameter of the proximal section of the guidewire may be about 0.038 inches, and the diameter of the distal section may be about 0.016 inches.
In another aspect of present disclosure, a distal segment of the combined access and aspiration catheter comprises a side wall defining a central lumen, the side wall comprising: a tubular inner liner; a tie layer separated from the lumen by the inner liner; a helical coil surrounding the tie layer, adjacent windings of the coil spaced progressively further apart in the distal direction; and an outer jacket surrounding the helical coil, the outer jacket formed from a plurality of tubular segments positioned coaxially about the coil; wherein a proximal one of the tubular segments has a durometer of at least about 60 D and a distal one of the tubular segments has a durometer of no more than about 35 D. The tubular liner may be formed by dip coating a removable mandrel. The tubular liner may comprise PTFE. The tie layer may comprise polyurethane, and may have a wall thickness of no more than about 0.005 inches. The tie layer may extend along at least the most distal 20 cm of the flexible body.
In one aspect of present disclosure, the coil comprises a shape memory material. In another aspect of present disclosure, the method of aspirating a vascular occlusion further comprises introducing an agitator into the combined access and aspiration catheter. The method of aspirating a vascular occlusion may further comprise vibrating a distal portion of the agitator during the aspirating step. The method of aspirating a vascular occlusion may further comprise introducing a fluid media through the agitator during the aspirating step. The method of aspirating a vascular occlusion may further comprise introducing polyethylene glycol through the agitator during the aspirating step.
In accordance with one aspect, there is provided a neurovascular catheter, comprising: an elongate flexible tubular body, having a proximal end, a distal end and a side wall defining a central lumen, a distal zone of the tubular body comprising: a tubular inner liner; a tie layer separated from the lumen by the inner liner; a helical coil surrounding the tie layer, adjacent windings of the coil spaced progressively further apart in the distal direction; an outer jacket surrounding the helical coil, and an opening at the distal end which is enlargeable from a first inside diameter for transluminal navigation to a second, larger inside diameter to facilitate aspiration of thrombus into the lumen. In one aspect of present disclosure, the distal opening is enlargeable in response to exposure to blood. In another aspect of present disclosure, the distal opening is enlargeable in response to exposure to body temperature. In yet another aspect of present disclosure, the distal opening is enlargeable in response to removal of a constraint. The constraint may comprise a polymer having a structural integrity that decreases in the intravascular environment.
In one aspect of present disclosure, the catheter body adjacent the distal opening comprises a radially outwardly biased embedded support. The catheter body adjacent the distal opening may comprise an embedded Nitinol frame. The support may comprise a wire mesh. The support may comprise a stent. In another aspect of present disclosure, the catheter body adjacent the distal opening comprises a hydrophilic blend. In yet another aspect of present disclosure, the tubular liner is formed by dip coating a removable mandrel. The tubular liner may comprise PTFE.
In one aspect of present disclosure, the tie layer comprises polyurethane. The tie layer may have a wall thickness of no more than about 0.005 inches. The tie layer may extend along at least the most distal 20 cm of the flexible body. In another aspect of present disclosure, the coil comprises a shape memory material. The coil may comprise Nitinol. The Nitinol may comprise an Austenite state at body temperature. In one aspect of present disclosure, the outer jacket is formed from at least five discrete tubular segments. The outer jacket may be formed from at least nine discrete tubular segments. The difference in durometer between a proximal one of the tubular segments and a distal one of the tubular segments may be at least about 20 D. The difference in durometer between a proximal one of the tubular segments and a distal one of the tubular segments may be at least about 30 D.
In accordance with one aspect, there is provided a neurovascular catheter extension segment, comprising: an elongate flexible control wire, having a proximal end and a distal end; a tubular extension segment having a side wall defining a central lumen carried by the distal end of the control wire, the side wall comprising: a tubular inner liner; a tie layer separated from the lumen by the inner liner; a helical coil surrounding the tie layer; and an outer jacket surrounding the helical coil. In one aspect of present disclosure, the outer jacket is formed from a plurality of tubular segments positioned coaxially about the coil. A proximal one of the tubular segments may have a durometer of at least about 60 D, and a distal one of the tubular segments may have a durometer of no more than about 35 D.
In another aspect of present disclosure, the tubular liner is formed by dip coating a removable mandrel. The tubular liner may comprise PTFE. In yet another aspect of present disclosure, the tie layer comprises polyurethane. The tie layer may have a wall thickness of no more than about 0.005 inches. The tie layer may extend along at least the most distal 20 cm of the tubular extension segment. In one aspect of present disclosure, the coil comprises a shape memory material. The coil may comprise Nitinol. The Nitinol may comprise an Austenite state at body temperature.
In one aspect of present disclosure, the outer jacket is formed from at least five discrete tubular segments. The outer jacket may be formed from at least nine discrete tubular segments. The difference in durometer between a proximal one of the tubular segments and a distal one of the tubular segments may be at least about 20 D. The difference in durometer between a proximal one of the tubular segments and a distal one of the tubular segments may be at least about 30 D. In another aspect of present disclosure, the control wire comprises a central lumen. The control wire central lumen may be in communication with the central lumen of the tubular extension segment. In yet another aspect of present disclosure, the inside diameter of the neurovascular catheter extension segment is at least 2× the inside diameter of the control wire central lumen. The inside diameter of the neurovascular catheter extension segment may be at least 3× the inside diameter of the control wire central lumen.
In accordance with another aspect, there is provided a neurovascular catheter extension segment system, comprising the neurovascular catheter extension segment described above and an agitator configured to extend through the control wire central lumen and into the central lumen of the tubular extension segment.
Although the present invention has been described in terms of certain preferred embodiments, it may be incorporated into other embodiments by persons of skill in the art in view of the disclosure herein. The scope of the invention is therefore not intended to be limited by the specific embodiments disclosed herein, but is intended to be defined by the full scope of the following claims.
This application is a continuation of U.S. patent application Ser. No. 16/400,263, filed on May 1, 2019, which is a continuation of U.S. patent application Ser. No. 16/398,626, filed on Apr. 30, 2019, now U.S. Pat. No. 10,835,272, issued on Nov. 17, 2020, which claims the benefit of U.S. Provisional Application No. 62/665,369, filed May 1, 2018, the entirety of each of the applications is hereby incorporated by reference herein.
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