Patent Grant
10864351
The present disclosure relates generally to medical methods and devices for the treatment of acute ischemic stroke. More particularly, the present disclosure relates to methods and systems for transcarotid access of the cerebral arterial vasculature and treatment of cerebral occlusions.
Acute ischemic stroke is the sudden blockage of adequate blood flow to a section of the brain, usually caused by thrombus or other emboli lodging or forming in one of the blood vessels supplying the brain. If this blockage is not quickly resolved, the ischemia may lead to permanent neurologic deficit or death. The timeframe for effective treatment of stroke is within 3 hours for intravenous (IV) thrombolytic therapy and 6 hours for site-directed intra-arterial thrombolytic therapy or interventional recanalization of a blocked cerebral artery. Re-perfusing the ischemic brain after this time period has no overall benefit to the patient, and may in fact cause harm due to the increased risk of intracranial hemorrhage from fibrinolytic use. Even within this time period, there is strong evidence that the shorter the time period between onset of symptoms and treatment, the better the results. Unfortunately, the ability to recognize symptoms, deliver patients to stroke treatment sites, and finally to treat these patients within this timeframe is rare. Despite treatment advances, stroke remains the third leading cause of death in the United States.
Endovascular treatment of acute stroke is comprised of either the intra-arterial administration of thrombolytic drugs such as recombinant tissue plasminogen activator (rtPA), mechanical removal of the blockage, or a combination of the two. As mentioned above, these interventional treatments must occur within hours of the onset of symptoms. Both intra-arterial (IA) thrombolytic therapy and interventional thrombectomy involve accessing the blocked cerebral artery via endovascular techniques and devices.
Like IV thrombolytic therapy, IA thrombolytic therapy alone has the limitation in that it may take several hours of infusion to effectively dissolve the clot. 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. Frank 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.
Disclosed are methods and devices that enable safe, rapid and relatively short transcarotid access to the cerebral and intracranial arteries to treat acute ischemic stroke. The methods and devices include one or more transcarotid access devices, catheters, and thrombectomy devices to remove the occlusion. Methods and devices are also included to provide aspiration and passive flow reversal for the purpose of facilitating removal of the occlusion as well as minimizing distal emboli. The system offers the user a degree of flow control so as to address the specific hemodynamic requirements of the cerebral vasculature. The disclosed methods and devices also include methods and devices to protect the cerebral penumbra during the procedure to minimize injury to brain. In addition, the disclosed methods and devices provide a way to securely close the access site in the carotid artery to avoid the potentially devastating consequences of a transcarotid hematoma.
In one aspect, there is disclosed a system of devices for treating an artery, comprising: an arterial access sheath adapted to introduce an interventional catheter into an artery, the arterial access sheath including a sheath body sized and shaped to be introduced into a common carotid artery via a carotid artery access site, the sheath body defining an internal lumen that provides a passageway for introducing a catheter into the common carotid artery when the first elongated body is positioned in the common carotid artery, wherein the sheath body has a proximal section and a distalmost section that is more flexible than the proximal section, and wherein a ratio of an entire length of the distalmost section to an overall length of the sheath body is one tenth to one half the overall length of the sheath body; an elongated dilator positionable within the internal lumen of the sheath body, wherein the arterial access sheath and the dilator can be collectively introduced into the common carotid artery; and a catheter formed of an elongated catheter body sized and shaped to be introduced via a carotid artery access site into a common carotid artery through the internal lumen of the arterial access sheath, the catheter body sized and shaped to be navigated distally to a intracranial artery through the common carotid artery via the access location in the carotid artery, wherein the catheter body has a length of 40 cm to 70 cm, and wherein the catheter body has a proximal most section and a distal most section wherein the proximal most section is a stiffest portion of the catheter body, and wherein the catheter body has an overall length and a distal most section length such that the distal most section can be positioned in an intracranial artery and at least a portion of the proximal most section is positioned in the common carotid artery during use.
Other features and advantages should be apparent from the following description of various embodiments, which illustrate, by way of example, the principles of the invention.
Interventions in the cerebral or intracranial vasculature often have special access challenges. Most neurovascular interventional procedures use a transfemoral access to the carotid or vertebral artery and thence to the target cerebral or intracranial artery. In recent years, interventional devices such as wires, guide catheters, stents and balloon catheters, have all been scaled down and been made more flexible to better perform in the neurovascular anatomy. Currently, access and treatment catheters to treat stroke range in length from 105 to 135 cm in length, with microcatheters up to 150 cm in length. These catheters access the arterial system from the femoral artery and must navigate the aortic arch and cervical and intracranial arteries to reach the occlusion in the cerebral artery. The access route is long, often tortuous and may contain stenosis plaque material in the aortic arch and carotid and brachiocephalic vessel origins, presenting a risk of embolic complications during the access portion of the procedure. In patients with tortuous anatomy, access to the occlusion may be difficult or impossible with existing catheters and devices. In addition, the cerebral vessels are usually more delicate and prone to perforation than coronary or other peripheral vasculature. Many neurovascular interventional procedures remain either more difficult or impossible because of device access challenges.
One severe drawback to current acute stroke interventions is the amount of time required to restore blood perfusion to the brain, which can be broken down to time required to access to the blocked cerebral artery, and time required to restore flow through the occlusion. Restoration of flow, either through thrombolytic therapy, mechanical thrombectomy, or other means, often takes hours during which time brain tissue is deprived of adequate oxygen. During this period, there is a risk of permanent injury to the brain tissue. In the setting of acute ischemic stroke where “time is brain,” these extra difficulties have a significant clinical impact.
Another challenge of neurovascular interventions is the risk of cerebral emboli. In order to reach cerebral vessels from a transfemoral access site, catheters must traverse peripheral arteries, the aortic arch, and the carotid arteries. In many patients, there is disease in the form of atherosclerosis in these arteries. Navigating catheters across these arteries may cause fragments to break off and flow to the brain, causing cerebral emboli. Often these emboli lead to procedure-related strokes, but even sub-clinical embolic burdens to the brain have been known to lead to altered mental states.
Once a target site has been reached, there is still a risk of cerebral emboli. During the effort to remove or dissolve clot blockages in the cerebral artery, for example, there is a significant risk of thrombus fragmentation creating embolic particles which can migrate downstream and compromise cerebral perfusion, leading to neurologic events. In carotid artery stenting procedures CAS, embolic protection devices and systems are commonly used to reduce the risk of embolic material from entering the cerebral vasculature. The types of devices include intravascular filters, and reverse flow or static flow systems. Unfortunately, because of the delicate anatomy and access challenges as well as the need for rapid intervention, these embolic protection systems are not used in interventional treatment of acute ischemic stroke.
Some of the current mechanical clot retrieval procedures for stroke treatment use aspiration as a means to reduce the risk of emboli and facilitate the removal of the clot. For example, some clot retrieval procedures include attaching a large syringe to the guide catheter, and then blocking the proximal artery and aspirating the guide catheter during pull back of the clot into the guide. The guide catheter may or may not have an occlusion balloon. However, this step requires a second operator, may require an interruption of aspiration if the syringe needs to be emptied and reattached, and does not control the rate or timing of aspiration. This control may be important in cases where there is some question of patient tolerance to reverse flow. Furthermore, there is no protection against embolic debris during the initial crossing of the clot with the microcatheter and deployment of the retrieval device. Aspiration devices such as the Penumbra System utilize catheters which aspirate at the face of the clot while a separate component is sometimes additionally used to mechanically break up the clot. Aspiration methods and devices can have the potential to more rapidly restore flow and reduce the level of distal emboli, as there is no requirement to cross or disrupt the clot to remove it. However, the efficacy of aspiration with current catheter designs is limited and often requires multiple attempts and/or adjunct mechanical thrombectomy devices, thus diminishing the time and reduced distal emboli benefits.
Disclosed are methods and devices that enable safe, rapid and relatively short and straight transcarotid access to the carotid arteries and cerebral vasculature for the introduction of interventional devices for treating ischemic stroke. Transcarotid access provides a short length and non-tortuous pathway from the vascular access point to the target cerebral vascular treatment site, thereby easing the time and difficulty of the procedure, compared for example to a transfemoral approach. Additionally, this access route reduces the risk of emboli generation from navigation of diseased, angulated, or tortuous aortic arch or carotid artery anatomy. Further, this access route may make some or all aspects of the procedure faster, safer, and more accurate, as described in more detail below. The devices and associated methods include transcarotid access devices, guide catheters, catheters, and guide wires specifically to reach a cerebral target anatomy via a transcarotid access site, and associated stroke treatment devices which have been optimized for delivery through a transcarotid access site also known as a transcervical access site.
Disclosed also are methods and devices to provide aspiration and passive flow reversal either from the access sheath, a guide catheter, or a catheter for the purpose of minimizing distal emboli. Disclosed also are methods and devices that optimize clot aspiration through either transfemoral or transcarotid access approaches. Included in this disclosure are kits of various combinations of these devices to facilitate transcarotid neurovascular interventional procedures.
In another aspect, there is disclosed methods and devices for additionally providing active aspiration as well as passive retrograde flow during the procedure to minimize distal emboli. The system offers the user a degree of blood flow control so as to address the specific hemodynamic requirements of the cerebral vasculature. The system may include a flow controller, which allows the user to control the timing and mode of aspiration.
In an embodiment, transcarotid access to the common carotid artery directly with the arterial access device 2010 is achieved percutaneously via an incision or puncture in the skin. In an alternate embodiment, the arterial access device 2010 accesses the common carotid artery CCA via a direct surgical cut down to the carotid artery. In another embodiment, the arterial access device provides access to the basilar artery BA or posterior cerebral arteries PCA via a cut down incision in the vertebral artery or a percutaneous puncture of the vertebral artery for access to occlusions in the posterior cerebral vasculature such as the posterior cerebral artery or basilar artery. For entry into the common carotid artery, the arterial access device can be inserted into an opening directly in the common carotid artery, the opening being positioned above the patient's clavicle and below a bifurcation location where the patient's common carotid artery bifurcates into an internal carotid artery and external carotid artery. For example, the opening may be located at a distance of around 3 cm to 7 cm below a bifurcation location where the patient's common carotid artery bifurcates into an internal carotid artery and external carotid artery.
The system may also include an intermediate guide catheter.
The systems shown in
The disclosed methods and devices also include devices to protect the cerebral penumbra during the procedure to minimize injury to the brain. A distal perfusion device may be used during the procedure to provide perfusion to the brain beyond the site of the occlusion, thereby reducing the injury to the brain from lack of blood. These perfusion devices may also provide a way to reduce the forward blood pressure on the occlusion in the vessel and thus assist in removing the occlusion, for example using either aspiration, a mechanical element, or both.
The system may also include accessory devices such as guidewires and microcatheters, and stroke treatment devices such as stent retrievers, snares, or other thrombectomy devices, which have been optimally configured for reaching a target cerebral or intracranial treatment site via a transcarotid access site. For example, the system may include a thrombectomy device 4100. In addition, the disclosed methods and devices provide for securely closing the access site to the cerebral arteries to avoid the potentially devastating consequences of a transcarotid hematoma. The present disclosure provides additional methods and devices.
Exemplary Embodiments of Arterial Access Devices
Described herein are arterial access devices, also referred to herein as arterial access sheaths or sheath systems. U.S. Patent Publication No. 2014/02196769; and U.S. Provisional Application Ser. No. 62/075,169 entitled “METHODS AND DEVICES FOR TRANSCAROTID ACCESS” and filed Nov. 4, 2014; and U.S. patent application Ser. No. 14/537,316 entitled “METHODS AND DEVICES FOR TRANSCAROTID ACCESS” and filed Nov. 10, 2014 which are each incorporated by reference herein, also describe arterial access devices of consideration herein.
As described above,
In an alternate embodiment, the arterial access device 2010 may be configured for access to the common carotid artery CCA from a femoral artery access site, also without the use of a separate introducer sheath. As above, the access device includes a proximal adaptor with a proximal port 2015 with a hemostasis valve and a connection to a flow line 2025 (or shunt) which may be connected to means for passive or active reverse flow. The flow line 2025 has an internal lumen that communicates with an internal lumen of the arterial access device 2010 for shunting blood from the arterial access device. In both transfemoral and transcarotid embodiments, the connection to the flow line is optimized for aspiration of thrombus with flow lumens at least as large as the ID of the arterial access device 2010.
Upon establishment of access to the carotid artery using the initial access system 100, an arterial access sheath of a sheath system such as those described herein may be inserted into the carotid artery at the access site.
In an embodiment, some or all of the components of transcarotid initial access system 100 and the transcarotid access sheath system 200 may be combined into one transcarotid access system kit such as by combining the components into a single, package, container or a collection of containers that are bundled together.
The arterial access sheath systems described herein can include a distal portion configured to be inserted in the vessel and a proximal portion configured to extend outward from the access site when the distal portion of the arterial access sheath is positioned in the arterial pathway. For example with reference to
In an embodiment, the sheath body 222 can have an inner diameter of about 0.087″ and an outer diameter of about 0.104″, corresponding to a 6 French sheath size. In another embodiment, the sheath body 222 has an inner diameter of about 0.113″ and an outer diameter of about 0.136″, corresponding to an 8 French sheath size. In an embodiment, the sheath length is between 10 and 12 cm. In another embodiment, the sheath length is between 15 and 30 cm. The diameter and length most suitable to a particular embodiment is dependent on the location of the target site and nature of the devices and flow requirements through the lumen of the access device 200.
In some instances it is desirable to move the proximal port and/or the hemostasis valve away from the distal tip of the arterial access sheath effectively elongating or lengthening the proximal portion (also called a proximal extension herein) that is outside the body while maintaining the length of the insertable distal portion. This allows the user to insert devices into the proximal port of the proximal extension and from there into the lumen of the arterial access device from a point further away from the target site and from the image intensifier used to image the target site fluoroscopically thereby minimizing radiation exposure of the user's hands and also his or her entire body. The proximal extension can be configured such that the length between the proximal port and the arterial access site is between about 30 cm and about 50 cm. The proximal extension can be removable from the arterial access device. An example of a proximal extension design is described in co-pending U.S. Application Publication No. 2010/0042118, filed Aug. 12, 2009, which is incorporated herein by reference. U.S. Pat. No. 8,574,245, U.S. Application Publication No. 2010/0217276, and U.S. Application Publication No. 2011/0087147, which each are also incorporated by reference herein.
The proximal extension and/or proximal adaptor 224 can have a larger inner and outer diameter than the sheath body 222 or the portion of the access sheath configured to be inserted arterially. In instances where the outer diameter of the catheter being inserted into the sheath is close to the inner diameter of the sheath body, the annular space of the lumen that is available for flow is restrictive. Minimizing the sheath body length is thus advantageous to minimize this resistance to flow, such as during flushing of the sheath with saline or contrast solution, or during aspiration or reverse flow out of the sheath. Again with respect to
The proximal extension 905 on the arterial access sheath 220 may be removable. Typically, vessel closure devices requires an arterial access sheath with a maximum distance of about 15 cm between distal tip of the sheath body to the proximal aspect of the hemostasis valve, with sheath body of about 11 cm and the remaining 4 cm comprising the length of the proximal hemostasis valve; thus if the access sheath has a distance of greater than 15 cm it is desirable to remove the proximal extension at the end of the procedure. Again with respect to
The arterial access sheath systems described herein are suitable or particularly optimized to provide transcarotid arterial access for reaching various treatment sites from that access site. The working length of the arterial access sheath or sheath/guide catheter system described herein can be considerably shorter than that of long sheaths or sheath guide systems placed, for example, from an access location in the femoral artery. The distance from the femoral artery to the common carotid artery (CCA) is about 60-80 cm moving through the artery. Thus, arterial access devices using a CCA access site may be shorter by at least this amount. Femoral arterial access used to access or deploy a device in the cervical ICA (e.g. the Balloon Guide, Concentric, Inc.) are typically 80-95 cm in length. Femoral arterial access used to access or deploy a device in the petrous ICA (e.g. the Neuron 6F Guide, Penumbra, Inc.) are typically 95-105 cm in length. The shorter lengths of access devices disclosed herein reduces the resistance to flow through the lumen of these devices and increases the rate at which aspiration and/or reverse flow may occur. For example, in an embodiment, the elongated sheath body 222 has a length in the range of about 10 cm to about 12 cm. For access to a same target site from a femoral access site, the access sheaths are typically between 80 cm and 110 cm, or a guide catheter is inserted through an arterial access sheath and advanced to the target site. However, a guide catheter through an access sheath takes up luminal area and thus restricts the size of devices that may be introduced to the target site. Thus, an access sheath that allows interventional devices to reach a target site without a guide catheter has advantages over an access sheath that requires use of a guide catheter to allow interventional devices to the target site.
It should be appreciated that the length and inner diameter of the arterial access sheaths described herein can vary depending on the desired target position of the sheath distal tip. In one embodiment, an access sheath is adapted to be inserted into the common carotid artery (CCA) with the distal tip positioned in the CCA or proximal ICA. In this embodiment, the sheath can have an elongated sheath body 222 having a length in the range of from about 7 cm to about 15 cm, usually being from about 10 cm to about 12 cm, The length considered herein can be the length extending from the proximal adapter 224 to a distal tip of the elongated sheath body 222. For a sheath adapted to be inserted via the common carotid artery (CCA) to a more distal site in the mid or distal internal carotid artery the length of the elongated sheath body 222 can be in the range from about 10 cm to about 30 cm, usually being from about 15 cm to about 25 cm. In another example embodiment, the arterial access device has a length of about 10 cm to about 40 cm. In another embodiment, the length of the arterial access device is about 10.5 cm and a separate guide catheter inserted through the access device has a length of about 32 cm.
In some procedures it may be desirable to incorporate features on the arterial access sheath in order to minimize flow resistance through the insertable portion of the access sheath, for example, as described in U.S. Pat. No. 7,998,104 to Chang and U.S. Pat. No. 8,157,760 to Criado, which are both incorporated by reference herein. For example,
In some instances it may be desirable to connect the access sheath to a flow line, for example for the purposes of passive or active aspiration to reduce the risk of distal emboli during the procedure. In an embodiment shown in
The flow line can be connected to an element configured for passive and/or active reverse flow such that blood from the arterial access sheath can be shunted. Connecting the flow line to a lower pressure system, such as a central vein or a reservoir, is an example of passive reverse flow. The reservoir may be positioned on a table near the patient, for a pressure of approximately zero, or positioned below the table to create negative pressure. Examples of devices for active reverse flow are a syringe or other manual aspiration device, or an aspiration pump. The passive or active reverse flow device may be actuated via a stopcock or other flow control switch during critical periods of the procedure, for example when thrombus is being pulled out of the occluded area, into the sheath, and out of the patient. In an embodiment, the flow control switch is integral to the arterial access device. In an alternate embodiment, the flow control switch is a separate component. Because it may be desirable to remove all thrombus from the device with minimal to no chance of material being caught in irregular surfaces or connection surfaces, an embodiment of the access device is constructed such that there is a continuous inner surface with no ledges or crevices at the junction(s) between the lumen of the sheath body, the Y-arm, the flow control switch, the flow line, and the aspiration source.
In some instances it is desirable for the sheath body to also be able to occlude the artery in which it is positioned, for examples in procedures that may create distal emboli. In these cases, occluding the artery stops antegrade blood flow in the artery and thereby reduces the risk of distal emboli that may lead to neurologic symptoms such as TIA or stroke. The arterial access device 2010 of
In some configurations, an intermediate guide catheter may be inserted through the arterial access device to provide additional catheter support and potentially distal occlusion.
In yet another embodiment, as shown in
In yet another embodiment, as shown in
The arterial access devices described herein may be configured so that it can be passed through or navigate bends in the artery without kinking. For example, when the access sheath is being introduced through the transcarotid approach, above the clavicle but below the carotid bifurcation, it is desirable that the elongated sheath body 222 be flexible while retaining hoop strength to resist kinking or buckling. This can be especially important in procedures that have limited amount of sheath insertion into the artery and/or where there is a steep angle of insertion as with a transcarotid access in a patient with a deep carotid artery and/or with a short neck. In these instances, there is a tendency for the sheath body tip to be directed towards the back wall of the artery due to the stiffness of the sheath. This causes a risk of injury from insertion of the sheath body itself, or from devices being inserted through the sheath into the arteries, such as guide wires. Alternately, the distal region of the sheath body may be placed in a distal carotid artery which includes one or more bends, such as the petrous ICA. Thus, it is desirable to construct the sheath body 222 such that it can be flexed when inserted in the artery, while not kinking. In an embodiment, the arterial access device can be and is passed through bends of less than or equal to 45 degrees wherein the bends are located within 5 cm, 10 cm, or 15 cm of the arteriotomy measured through the artery.
The working portion of the arterial access sheath, such as the sheath body which enters the artery, can be constructed in two or more layers. An inner liner can be constructed from a low friction polymer such as PTFE (polytetrafluoroethylene) or FEP (fluorinated ethylene propylene) to provide a smooth surface for the advancement of devices through the inner lumen. An outer jacket material can provide mechanical integrity to the inner liner and may be constructed from materials such as Pebax, thermoplastic polyurethane, polyethylene, nylon, or the like. A third layer can be incorporated that can provide reinforcement between the inner liner and the outer jacket. The reinforcement layer can prevent flattening or kinking of the inner lumen of the sheath body as the device navigates through bends in the vasculature. The reinforcement layer can also provide for unimpeded lumens for device access as well as aspiration or reverse flow. In an embodiment, the sheath body 222 is circumferentially reinforced. The reinforcement layer can be made from metal such as stainless steel, Nitinol, Nitinol braid, helical ribbon, helical wire, cut stainless steel, or the like, or stiff polymer such as PEEK. The reinforcement layer can be a structure such as a coil or braid, or tubing that has been laser-cut or machine-cut so as to be flexible. In another embodiment, the reinforcement layer can be a cut hypotube such as a Nitinol hypotube or cut rigid polymer, or the like.
The arterial access sheaths described herein can have a sheath body that varies in flexibility over its length. As described above, a distal-most portion of the arterial access device may be configured to be more flexible than a proximal section of the device. In one embodiment, there is a distal-most section of sheath body 222 that is more flexible than the remainder of the sheath body. The distal section may be at least 10% of the length of the working portion of the catheter wherein the working portion is the portion that is configured to be inserted into an artery. In other embodiments, the distal section is at least 20% or at least 30% of the length of the working portion of the catheter. The variability in flexibility may be achieved in various ways. For example, the outer jacket may change in durometer and/or material at various sections. A lower durometer outer jacket material can be used in a distal section of the sheath compared to other sections of the sheath. Alternately, the wall thickness of the jacket material may be reduced, and/or the density of the reinforcement layer may be varied to increase the flexibility. For example, the pitch of the coil or braid may be stretched out, or the cut pattern in the tubing may be varied to be more flexible. Alternately, the reinforcement structure or the materials may change over the length of the sheath body. For example, the flexural stiffness of the distal-most section can be one third to one tenth the flexural stiffness of the remainder of the sheath body 222. In an embodiment, the distal-most section has a flexural stiffness (E*I) in the range 50 to 300 N-mm2 and the remaining portion of the sheath body 222 has a flexural stiffness in the range 500 to 1500 N-mm2, where E is the elastic modulus and I is the area moment of inertia of the device. For a sheath configured for a CCA access site, the flexible, distal most section comprises a significant portion of the sheath body 222 which may be expressed as a ratio. In an embodiment, the ratio of length of the flexible, distal-most section to the overall length of the sheath body 222 is at least one tenth and at most one half the length of the entire sheath body 222.
In some instances, the arterial access sheath is configured to access a carotid artery bifurcation or proximal internal carotid artery ICA from a CCA access site. As best shown in
In some instances, the sheath body 222 of the arterial access sheath is configured to be inserted more distally into the internal carotid artery relative to the arterial access location, and possibly into the intracranial section of the internal carotid artery. For example, a distal-most section 223 of the elongated sheath body 222 is about 2.5 cm to about 5 cm and the overall sheath body 222 is about 15 cm to about 30 cm in length. In this embodiment, the ratio of length of the flexible, distal-most section to the overall length of the sheath body is one tenth to one quarter of the entire sheath body 222. In another embodiment, there is a transition section 225 between the distal-most flexible section and the proximal section 231, in which the distal-most section is about 2.5 cm to about 5 cm, the transition section is about 2 cm to about 10 cm and the overall sheath body 222 is about 15 cm to about 30 cm. In this embodiment, the distal-most flexible section and the transition section collectively form at least one sixth and at most one half the entire length of the sheath body.
In some instances it is desirable to keep the sheath tip as small as possible during sheath insertion to minimize the diameter of the arterial puncture, but to expand the opening of the sheath after it has been inserted into the vessel. At least one purpose of this feature is to minimize the effect or creation of distal emboli during pull back of an aspiration catheter or other thrombectomy device into the sheath. During a thrombectomy procedure, the thrombus may be “pulled back” into a distal opening of the sheath on a device that has captured the thrombus. If the distal tip of the sheath is enlarged relative to its initial size, the chance of pieces of the thrombus breaking off and causing emboli is minimized because the larger size of the sheath tip is more likely to accommodate the emboli being drawn into it without being split into multiple pieces. This creates a better clinical outcome for the patient. In an embodiment of the arterial access device, the arterial access device is made of a material and/or constructed such that a tip of the sheath body of the access device can be expanded to a larger diameter once inserted into the artery and positioned in its desired location. In an embodiment, the distal region of the sheath has an ID of about 0.087″ can be enlarged to a diameter of about 0.100″ to 0.120″ although the size may vary.
Examples of expanding distal tip constructions include covered braided tips that can be shortened to expand. Another example of an expanding distal tip construction is an umbrella or similar construction that can open up with mechanical actuation or elastic spring force when unconstrained. Other mechanisms of expandable diameter tubes are well known in the art. One particular embodiment is a sheath made of material that is deformable when expanded using a high pressure balloon.
The arterial access devices described herein can also be adapted to reduce, minimize or eliminate a risk of injury to the artery caused by the distal-most sheath tip facing and contacting the posterior arterial wall. In some embodiments, the sheath has a structure configured to center the sheath body tip in the lumen of the artery such that the longitudinal axis of the distal region of the sheath body is generally parallel with the longitudinal or center axis of the lumen of the vessel. The sheath alignment feature 508 can be one or more mechanical structures on the sheath body 222 that can be actuated to extend outward from the sheath tip (see
In another embodiment, at least a portion of the sheath body 222 is pre-shaped so that after sheath insertion the tip is more aligned with a long axis of the vessel within which it is inserted, even at a steep sheath insertion angle. In this embodiment, the sheath body 222 is generally straight when the dilator 260 is assembled with the sheath 220 during sheath insertion over the sheath guide wire 300, but once the dilator 260 and guidewire 300 are removed, the distal-most section of the sheath body 222 can assume a curved or angled shape. In an embodiment, the sheath body 222 is shaped such that the distal-most 0.5 cm to 1 cm section is angled from 10 to 30 degrees, as measured from the main axis of the sheath body 220, with a radius of curvature about 0.5″. To retain the curved or angled shape of the sheath body 220 after having been straightened during insertion, the sheath 220 may be heat set in the angled or curved shape during manufacture. Alternately, a reinforcement structure may be constructed out of nitinol and heat-shaped into the curved or angled shape during manufacture. Alternately, an additional spring element may be added to the sheath body 220, for example a strip of spring steel or nitinol, with the correct shape, added to the reinforcement layer of the sheath 220.
In some procedures, it may be desirable to limit the amount of sheath body 222 insertion into the artery, for example in procedures where the target area is very close to the arterial access site. In a stent procedure of the carotid artery bifurcation, for example, the sheath tip should be positioned proximal of the treatment site (relative to the access location) so that it does not interfere with stent deployment or enter the diseased area and possibly cause emboli to get knocked loose. In an embodiment of arterial sheath 220 shown in
In situations where the insertion of the sheath body is limited to between about 2 cm and about 3 cm, and particularly when the sheath body 222 is inserted at a steep angle, the sheath 220 may conform to a bayonet shape when secured to the patient. For example, the bayonet shape may comprise a first portion that extends along a first axis and a second portion that extends along a second axis that is axially offset from the first axis and/or non-parallel to the first axis. The springiness of the sheath body 222 causes this shape to exert a force on the vessel at the site of insertion and increase the tendency of the sheath 220 to come out of the vessel if not properly secured. To reduce the stress on the vessel, the sheath stopper may be pre-shaped into a curved or bayonet shape so that the stress of the sheath body when curved is imparted onto the sheath stopper rather than on the vessel. The sheath stopper 1005 may be made from springy but bendable material or include a spring element such as a stainless steel or nitinol wire or strip, so that when the dilator 260 is inserted into the sheath 220 and sheath stopper 1005, the sheath 220 is relatively straight, but when the dilator 260 is removed the sheath stopper 1005 assumes the pre-curved shape to reduce the force the sheath 220 imparts on the vessel wall. Alternately, the sheath stopper 1005 may be made of malleable material or include a malleable element such as a bendable metal wire or strip, so that it can be shaped after the sheath 220 is inserted into a desired curvature, again to reduce the stress the sheath 220 imparts on the vessel wall.
The access sheaths described herein can have a lubricious or hydrophilic coating to reduce friction during insertion into the artery and improve the ease of advancement of the device through the vasculature. The hydrophilic coating can be limited to the working portion of the device. In an embodiment, the distal portion of the shaft is dip-coated with a polymer material such as polyurethane. The dip coating may have gradual transitions between sections of varying thickness moving along the length of the device. In an embodiment, the distal coating is limited to the distal-most 0.5 cm to 3 cm of the elongated sheath body 222, so that it facilitates insertion without compromising security of the sheath in the puncture site or the ability of the operator to firmly grasp the sheath during insertion. In an alternate embodiment, the sheath has no coating. The access sheaths described herein may also include a radiopaque tip marker to facilitate placement of the device using fluoroscopy. For example,
As mentioned above, the arterial access device systems described herein can include one or more tapered dilators to improve entry into the artery. The entry or distal tip of the arterial access sheaths described herein can be tapered so as to allow smooth introduction of the sheath over a guide wire into the artery. The distal tip of the arterial access sheath itself can be configured such that when the access sheath is assembled with the sheath dilator to form a sheath assembly, the sheath assembly can be inserted smoothly over the sheath guide wire through the arterial puncture with minimal resistance.
In an embodiment, the arterial access device may be supplied in a kit that includes two or more tapered dilators. The first tapered dilator is used with the arterial access device to gain entry into the artery, for example the tapered dilator 260 of
The second dilator (which has a distal section with a lower bending stiffness) may be exchanged with the initial, first dilator such that the arterial access device may be inserted into the internal carotid artery and around curvature in the artery without undue force or trauma on the vessel due to the softer distal section of the second dilator. The distal section of the soft, second dilator may be, for example, 35 or 40D Pebax, with a proximal portion made of, for example 72D Pebax. An intermediate mid portion or portions may be included on the second dilator to provide a smooth transition between the soft distal section and the stiffer proximal section. In an embodiment, both dilators may have radiopaque tip markers so that the dilator tip position is visible on fluoroscopy. In an embodiment, the distal most edge of one or both catheters is atraumatic and configured to reduce the likelihood of the distal most edge damaging or cutting tissue while being moved through the artery. The distal most edge may be rounded or may have any shape that reduces the likelihood of the distal most edge damaging tissue.
To facilitate exchange of the first dilator for the second dilator, one or both dilators may be constructed such that the distal section of the dilator is constructed from a tapered single-lumen tube, but the proximal portion of the dilator and any adaptor on the proximal end has a side opening.
A method of use of this embodiment of an arterial access device kit is now described. A guide wire, such as an 0.035″ guidewire, is inserted into the common carotid artery, either using a Modified Seldinger technique or a micropuncture technique. The distal end of the guidewire can be positioned into the internal or external carotid artery, or stop in the common carotid artery short of the bifurcation. The arterial access device with the first, stiffer dilator, is inserted over the 0.035″ wire into the artery. The arterial access device is inserted such that at least 2.5 cm of sheath is in the artery. If additional purchase is desired, the arterial access device may be directed further, and in to the internal carotid artery. The first dilator is removed while keeping both the arterial access device and the 0.035″ wire in place. The side opening 4010 in the proximal portion of the dilator allows the dilator to be removed in a “rapid exchange” fashion such that most of the guidewire outside the access device may be grasped directly during dilator removal. The second dilator is then loaded on to the 0.035″ wire and inserted into the sheath. Again, a dilator with a side opening 4010 in the proximal portion of the dilator may be used to allow the 0.035″ wire to be grasped directly during guide wire insertion in a “rapid exchange” technique. Once the second dilator is fully inserted into the arterial access device, the arterial access device with the softer tipped, second dilator is advanced up the internal carotid artery and around bends in the artery without undue force or concern for vessel trauma. This configuration allows a more distal placement of the arterial access device without compromising the ability of the device to be inserted into the artery.
Alternately, one or more standard dilators may be used without side openings. If a standard dilator without a side opening is used, after the access device is inserted into the artery over a guide wire with the first dilator, the first dilator may be removed together with the guidewire, leaving only the access device in place. The second dilator with a guide wire preloaded into the central lumen may be inserted together into the arterial access device. Once fully inserted, the access device and second dilator with softer tip may be advanced distally up the internal carotid artery as above. In this alternate method, the initial guide wire may be used with both dilators, or may be exchanged for a softer tipped guide wire when inserted with the second softer tipped dilator.
Catheter Exemplary Embodiments
Described herein are catheters configured to be inserted through an arterial access device. Examples of catheters are described in U.S. Provisional Application Ser. No. 62/029,799, filed Jul. 28, 2014 and U.S. Provisional Application Ser. No. 62/075,101 entitled “Transcarotid Neurovascular Catheter” and filed Nov. 4, 2014, which are both incorporated by reference herein in their entirety.
As described above,
The catheter 105 may be made with a two or more layer construction. In an embodiment, the catheter has a PTFE inner liner, an outer jacket layer, and at least a portion of the catheter has a reinforcement structure, such as a tubular structure formed of, for example, a wound coil, braid or cut hyptotube. In addition, the catheter may have a radiopaque marker at the distal tip to facilitate placement of the device using fluoroscopy.
The catheter 105 has an insertable portion (i.e. working length) that is sized to be inserted through an access sheath in the carotid artery and passed through an arterial pathway (through the artery) to the distal ICA or cerebral vessels. In an embodiment the catheter 105 has a working length ranging from 40 to 70 cm. In an embodiment, the catheter has a working length of less than 70 cm, less than 60 cm, or less than 50 cm. Alternately, the length of catheter can be defined relative to the location of the access site and the target cerebral artery site. In an embodiment, the catheter is configured to be introduced into the artery at a location in the artery that is less than 40 cm, less than 30 cm, or less than 20 cm from the location of the target site as measured through the arterial pathway. The distance may further be defined by a ratio of working length to the distance between the location where the catheter enters the arteriotomy and the target site. In an embodiment, this ratio is less than 2×. In an embodiment, the working portion of the device may have a hydrophilic coating to improve the ease of advancement of the device through the vasculature. In an embodiment, at least 40% of the working length of the catheter is coated with a hydrophilic material. In other embodiments, at least 50% or at least 60% of the working length of the catheter is coated with a hydrophilic material.
In an embodiment, the distal-most portion is constructed to be more flexible than the proximal portion, with one or more flexible sections, to successfully navigate the internal carotid artery curvature to reach target sites in the distal ICA or cerebral arteries. The shaft may have a transition section of one or more increasingly stiff sections towards the more proximal section of the shaft, with the proximal most portion having the stiffest shaft section. Alternately, the transition section is a section of continuously variable stiffness from the distal section stiffness to the proximal section stiffness. In an embodiment, the distal most flexible section is 5 to 15 cm, a transition section is 5 to 15 cm, and a proximal stiff section takes up the remainder of the working length. In an embodiment where the catheter has a working length of 40 cm, the proximal stiff section is in a range 10 to 30 cm. In an embodiment where the catheter has a working length of 70 cm, the proximal stiff section is in a range from 40 to 60 cm.
Alternately, the flexible distal section and transition section may be described as a portion of the overall catheter working portion wherein the working portion is the portion that is configured to be inserted into an artery. In an embodiment, the flexible distal section may be between 3 to 10% of the length of the working portion of the catheter and the transition section may be between 15-35% of the length of the working portion of the catheter. In other embodiments, the distal section is at least 20% or at least 25% of the length of the working portion of the catheter.
In an embodiment, the flexibility of the distal most section is in the range 3 to 10 N-mm2 and the flexibility of the proximal post section is in the range 100 to 500 N-mm2, with the flexibility/flexibilities of the transition section falling between these two values.
As noted above, the catheter may have sections with discreet and/or continuously variable stiffness shaft. The sections of varying flexibility may be achieved by multiple methods. For example, the outer jacket layer may be composed of discreet sections of polymer with different durometers, composition, and/or thickness. In another embodiment, the outer layer has one or more sections of continuously variable outer layer material that varies in flexibility. The catheter may be equipped with the continuously variable outer layer material by dip coating the outer layer rather than laminating a jacket extrusion onto a PTFE-liner and reinforcement assembly of the catheter. The dip coating may be, for example, a polymer solution that polymerizes to create the outer jacket layer of the catheter. The smooth transition from one flexibility (e.g., durometer) to another flexibility along the length of the catheter can be accomplished via dipping the catheter assembly in multiple varying durometer materials whereby the transition from one durometer to another can be accomplished in a graded pattern, for example by dipping from one side of the catheter in one durometer with a tapering off in a transition zone, and dipping from the other side in another durometer with a tapering off in the same transition zone, so there is a gradual transition from one durometer to the other. In this embodiment, the dip coating can create a thinner walled outer jacket than a lamination assembly. In another embodiment, the catheter has an outer jacket layer that is extruded with variable durometer along the length, to provide variable flexibility along the length of the catheter.
In an embodiment, at least a portion of the catheter has a reinforcement structure, such as a tubular structure formed of, for example, a wound coil, braid that is composed of discreet or continuously varying structure to vary the stiffness, for example a variable coil or braid pitch. In an embodiment, the reinforcement structure is a cut hyptotube, with a cut pattern that is graded along the length, for example cut in a spiral pattern with continuously variable pitch or continually variable cut gap, or a repeating cut pattern that allows the tube to flex whereby the repeating pattern has a continuously variable repeat distance or repeat size or both. A cut hypotube-reinforced catheter may also have superior pushability than a coil-reinforced catheter, as it is a structure with potentially greater stability in the axial direction than a wound coil. The material for the reinforcement structure may be stainless steel, for example 304 stainless steel, nitinol, cobalt chromium alloy, or other metal alloy that provides the desired combination of strengths, flexibility, and resistance to crush. In an embodiment, the reinforcement structure comprises multiple materials along the different sections of flexibility
In another embodiment the catheter has a PTFE inner liner with one or more thicknesses along variable sections of flexibility. In an embodiment, the PTFE inner liner is constructed to be extremely thin, for example between 0.0005″ and 0.0010″. This embodiment provides the catheter with a high level of flexibility as well as the ability to construct a thinner-walled catheter. For example, the PTFE liner is constructed by drawing a mandrel through a liquid PTFE liquid solution rather than the conventional method of thin-walled PTFE tubing manufacture, namely extrusion of a PTFE paste which is then dried and sintered to create a PTFE tube. The draw method allows a very thin and controlled wall thickness, such as in the range of 0.0005″-0.0010″.
Any one of the aforementioned manufacturing methods may be used in combination to construct the desired flexibility and kink resistance requirement. Current tri-layer catheters have wall thicknesses ranging from 0.005″ to 0.008″. These manufacturing techniques may results in a catheter with better catheter performance at the same wall thickness, or with equal or better catheter performance at lower wall thicknesses for example between 0.003″ to 0.005″.
In an embodiment, the distal flexible section of the catheter may be constructed using one or more of: a dip coated outer layer, an extremely thin drawn PTFE layer, and a cut hypotube reinforcement layer, with a gradual transition from the flexible section to a stiffer proximal section. In an embodiment, the entire catheter is constructed with one or more of these elements
In some instances, there is a need to reach anatomic targets with the largest possible internal lumen size for the catheter. For example the catheter may be used to aspirate an occlusion in the blood vessel. Thus there is a desire to have a very flexible, kink resistant and collapse resistant catheter with a thin wall and large inner diameter. A catheter using the construction techniques disclosed herein meets these requirements. For example, the catheter may have an inner diameter of 0.070″ to 0.095″ and a working length of 25-50 cm. In another embodiment, the catheter may be sized to reach the more distal cerebral arteries, with an inner diameter of 0.035″ to 0.060″ and a working length of 40-80 cm. In an embodiment, the catheter is configured to navigate around a 180° bend around a radius as small as 0.050″ or 0.100″ without kinking, wherein the bends are located within 5 cm, 10 cm, or 15 cm of the arteriotomy measured through the artery. In an embodiment, the catheter can resist collapsing whilst in a tortuous anatomy up to 180°×0.050″ radius bend without collapsing when connected to a vacuum up to 20 inHg. In an embodiment, the catheter can resist collapse in the same conditions when connected to a vacuum up to 25 inHg.
In another embodiment, the inner and/or outer diameter of the catheter is stepped up at a proximal region of the catheter such that the proximal region of the catheter has a larger inner and/or outer diameter than a remaining distal region of the catheter.
In some instances, the catheter is used to aspirate a clot in an artery.
A cause of difficulty in advancing catheters through severe bends and across side branches is the mismatch between the catheter and the inner guiding components such as smaller catheters, microcatheters, or guidewires. One technique for advancing a catheter is called a tri-axial technique in which a smaller catheter or microcatheter is placed between the catheter and the guide wire. However, with current systems the smaller catheter has a diameter mismatch between either the larger catheter, the guide wire, or both, which creates a step in the system's leading edge as the system is advanced in the vasculature. This step may cause difficulty when navigating very curved vessels, especially at a location where there is a side-branch, for example the ophthalmic artery. In an embodiment, as shown in Figure A, the catheter 105 is supplied with a tapered co-axial inner member 2652 that replaces the smaller catheter generally used. The inner member 2652 is sized and shaped to be inserted through the internal lumen of the catheter. The inner member 2652 has a tapered region with an outer diameter that forms a smooth transition between the inner diameter of the catheter 203 and the outer diameter of a guidewire 2515 or microcatheter that extends through an internal lumen of the inner member 2652. In an embodiment, the tapered dilator or inner member 2652, when positioned within the catheter, creates a smooth transition between the distal-most tip of the larger catheter 105 and the outer diameter of a guide wire 2515 which may be in the range of 0.014″ and 0.018″ diameter for example. For example, the inner luminal diameter may be between 0.020″ and 0.024″. In another embodiment, the inner diameter is configured to accept a microcatheter with an outer diameter in the range of 0.030″ to 0.040″ or an 0.035″ guide wire in the inner lumen, for example the inner luminal diameter may be 0.042″ to 0.044″.
In a variation of this embodiment, shown in
The material of the dilator (inner member 2652) is flexible enough and the taper is long enough to create a smooth transition between the flexibility of the guide wire and the catheter. This configuration will facilitate advancement of the catheter through the curved anatomy and into the target cerebral vasculature. In an embodiment, the dilator is constructed to have variable stiffness, for example the distal most section is made from softer material, with increasingly harder materials towards the more proximal sections. In an embodiment, distal end of the tapered dilator has a radiopaque marker such as a platinum/iridium band, a tungsten, platinum, or tantalum-impregnated polymer, or other radiopaque marker.
In another embodiment, a catheter system includes an anchor device which is configured to be easily navigable through the vasculature to a location distal to the cerebral occlusion. When the anchor is deployed, it may be used as a rail and counter force to facilitate advancement of the catheter to the proximal face of the occlusion. In an example shown in
The atraumatic distal anchor can be a device other than a balloon. For example, other atraumatic distal anchors may include microcatheters with mechanically expandable-tips such as a braid, coil, or molly-bolt construction. The expandable tip can be configured to be sufficiently soft and to provide sufficient force along a length of the microcatheter so as to reduce focal pressure against the vessel wall and minimize vessel wall injury.
Another variation of this embodiment as shown in
In another embodiment, shown in
In another embodiment, as shown in
In some instances, it may be desirable for the catheter to have an distal tip which can increase in diameter after being positioned at a target treatment site, for example to facilitate removal of an occlusion when an aspiration device is connected to the proximal portion of the catheter. In an embodiment, the catheter has an expandable tip portion. The expandable tip portion may be constructed with a mechanical structure such as a braid or stent structure, which can open or close in a repeatable manner. The mechanism for opening the tip may be a pull-wire which shortens the expandable portion, or an outer retention sleeve which maintains the distal section in a small diameter but when retracted allows the distal tip to expand. The distal section may be covered with a membrane such that when aspiration is applied, either with the tip expanded or not, a vacuum may be applied at the very tip of the catheter. The expandable tip allows the catheter to maintain a small profile during tracking of the catheter to the target anatomy, but then expands the distal luminal area for facilitated capture of occlusive material such as thrombus. The thrombus, once captured into the catheter, may be sucked all the way into the aspiration device, or alternately will be lodged in the lumen of the catheter where the catheter is no longer expanded, and at that point can be removed by retraction of the entire catheter.
In another embodiment, shown in
It may be sufficient for the contact area between the overlapping portion of the arterial access device 2820 and the catheter 2830 to provide sufficient seal such that the aspiration or pressure force is transmitted to the distal end of the catheter 2830 with no leakage at the junction between the two devices. However, if additional sealing is needed, the system may include a sealing element at the juncture between the arterial access device 2820 and the catheter 2830. This embodiment is also useful if multiple size catheters are required during a procedure to reach different target sites, without the necessity of replacing the arterial access device. The sealing element of a smaller catheter 2830 can be designed to seal the larger gap between the catheter and the access device. One embodiment of a seal element is shown in
In an embodiment, the arterial access device 2820 and catheter 2830 with features to allow the two to be telescopically coupled as in
In an embodiment, the arterial access device 2820 is a 6F sheath size with ID about 0.086″ to 0.088″, and the catheter 2830 has an outer diameter of between 0.083″ and 0.086″ and an inner diameter of between 0.068″ and 0.072″. In an alternate embodiment, the arterial access device 2820 is a 5F sheath size with ID about 0.074″ to 0.076″, and the catheter 2830 has an outer diameter of between 0.071″ and 0.073″ and an inner diameter of between 0.058″ and 0.062″. Other diameter combinations are possible as warranted by the procedure.
In another embodiment, the catheter 2830 includes a structure for morcelating the thrombotic occlusion as it is being aspirated into the catheter. In an embodiment, a separate thrombus disruption device with an expandable distal segment is inserted into the catheter and positioned inside the lumen near the distal tip, once the catheter is positioned at the target site and the inner guide wire and/or inner catheter or dilator are removed. The device is inserted with the expandable segment in the collapsed state and the expanded proximal to the distal tip of the catheter. The device is configured to be small enough in this state that it should have minimal interference with thrombus aspiration. In an exemplary method, the thrombus disruption device is connected to a rotary motor at the proximal end such that the expandable portion is rotating at the distal segment of the catheter. Aspiration is then initiated at the proximal end of the catheter. As thrombus is aspirated into the catheter, the rotating expandable section breaks up the clot which is then easily aspirated through the length of the catheter. Alternately, the thrombus disruption device is expanded but remains still and is only rotated or translated back and forth after aspiration has started and if and when the clot becomes stuck in the lumen of the catheter. In an embodiment, the device also includes a short atraumatic distal tip, such as a floppy tip on a neurovascular guide wire. This feature minimized the chance of this device causing vascular injury should it protrude from the distal end of the catheter at any time during its use.
In an embodiment, the thrombus disruption device is manufactured from a generally elongate structure, coupled with an inner member attached at the distal end to actuate the expandable segment. The construction of the expandable segment may be a braid, one or more helical wires, or a tube with a cut pattern, any of which are designed to expand when shortened by pulling the inner member. Alternately, as shown in
Many of the catheter configurations described herein provide a benefit in aspiration ability over existing methods and devices particularly when the cathereter is combined with one of the disclosed arterial access devices. This benefit translates to more rapid and more effective removal of thrombotic occlusion and reduced distal emboli in the treatment of strokes. This benefit is derived at least from from shorter and in some cases larger inner lumen diameter aspiration catheter designs. According to Poiseuille's law for laminar flow in a tube, the flow rate can be expressed as the equation Q=π×r4×(ΔP)/8×n×L, where Q=flow rate, r=radius of the tube, P=pressure, n=viscosity, and L=length. As shown by this equation, flow rate drops by increases in length and drops proportionally by decreases in radius to the fourth power. The transcarotid embodiments described herein allow aspiration rates through catheters about half the length, and therefore potentially twice the flow with respect to prior devices. In addition, the embodiments disclosed herein allow larger diameter catheters the ability to reach the same target sites more easily and more often, due to the greater proximal support from the transcarotid access site, the greater catheter pushabiltiy due to the more distal transition from flexible to stiff segments, and the tapered inner members as in
For example, one catheter currently used for clot aspiration is the Navien 058 or the Navien 072 catheters (sold by Covidien). These catheters have inner diameters of 0.058″ and 0.072″ respectively and lengths of 115 and 105 cm respectively. Although the Navien 072 catheter has been demonstrated to be a more effective catheter for removal of cerebral thrombus, it is less often able to reach the target site. In contrast, the Penumbra 5Max and 5Max ACE are frequently able to reach the face of the clot, and additionally has a stepped configuration that offers some diameter benefit. However, these catheter configurations still do not perform as well as the catheters disclosed herein. Catheters configured for transcarotid delivery, as in
When different catheter systems are tested for actual aspiration rates this benefit is diminished somewhat as compared to the theoretical aspiration rates, especially at higher flow rates. This is reflective of the fact that at the higher flow rates, the flow is less and less laminar, and thus lower than the theoretical flow as predicted by Poiseuille's law. However, the shorter and larger ID catheters do show a relative benefit. In an exemplary test method, the catheters are tested for aspiration rates with a 40% glycerin mixture to simulate the viscosity of blood using the following method: each catheter was connected to a stopcock and thence to a 30 cc locking syringe. The tip of the catheter was positioned in a container of the glycerin mixture. The catheter and syringe were purged of air, the syringe was emptied, and then the stopcock was closed. The locking syringe was then pulled back the full 30 cc volume and locked in place. A timer was started when the stopcock was opened, and the time was noted at 5 cc, 10 cc, 15 cc and 20 cc of extracted solution in the syringe. The overall average extraction rate was calculated based on the slope of the data points and was roughly linear over the 20 cc volume, indicating a constant vacuum level using this method. Results and their relative improvements over the baseline Navien Catheters are provided in the tables in
Exemplary Embodiments of Aspiration and Flow Control
As described above, it is sometime desirable to include aspiration or flow reversal devices or structures to the system. Described herein are aspiration and flow control elements configured to be used with an arterial access device, a guide catheter, and/or a catheter of the disclosed system. Examples of aspiration and flow control elements are described in U.S. Patent Publication No. 2014/0296868, filed Mar. 21, 2014, which is incorporated by reference herein in its entirety. Any or all of the arterial access device 2010 and the catheter 2030 may be connected to sources of passive or active aspiration via flow lines 2025 or 2045 (
In
In an embodiment, a flow controller may facilitate control of multiple mechanisms of aspiration through multiple devices in a single unit. This configuration may facilitate use of the system by a single operator. The flow controller may include one or more control interfaces that a user may actuate to regulate which device is being aspirated, for example the arterial access device, the catheter, both, or neither.
The active source of aspiration may be an aspiration pump, a regular or locking syringe, a hand-held aspirator, hospital suction, or the like. In one embodiment, a locking syringe (for example a VacLok Syringe) is attached to the flow controller and the plunger is pulled back into a locked position by the user while the connection to the flow line is closed prior to the thrombectomy step of the procedure. During the procedure when the tip of the aspiration device (either the arterial access device or the catheter) is near or at the face of the occlusion, the user may open the connection to the aspiration syringe. This would enable the maximum level of aspiration in a rapid fashion with one user, something that is currently not possible with existing technologies. In another embodiment, the aspiration source is a hand-held aspirator which is configured to be able to aspirate and refill without disconnecting the aspiration device. In an example of this embodiment, the hand-held aspirator contains a chamber with a plunger that is moved up and down with a single-handed actuator. The chamber includes input and output valves, such that when the plunger is moved up and down there is a continuous source of aspiration into and out of the chamber without the need to remove and empty the chamber as would be needed with a syringe. The chamber input is connected to the catheter, and the chamber output is connected to a collection receptacle such as blood-collection bag. In an embodiment, this aspiration source is configured to be used with one hand only.
One disadvantage of current sources of aspiration is that the aspirated blood is received into an external reservoir or syringe. This blood is generally discarded at the end of the procedure, and as such represents blood loss from the patient. In addition, pumps such as centrifugal or peristaltic pumps are known to cause damage to blood cells. Although it is possible to return blood from the external reservoir to the patient, the blood has been exposed to air or has been static for a period of time, and there is risk of thrombus formation or damage to the blood cells. Usually, aspirated blood is not returned to the patient to avoid risk of thromboembolism.
In operation of the pump device 3250, the vacuum source 3230 is operated to create a reduced pressure within the chamber 3220 relative to the pressure within the flow line lumen 3210. The pressure differential between the chamber 3220 and the flow line lumen 3210 causes the expandable portion 3210 of the flow line 2025 to expand to an increased volume within the chamber 3220, as shown in solid lines in
A further advantage pump system 3250 or 3305 is that it may be used in conjunction with a passive reverse flow system which is configured to return blood to the central venous system, as is disclosed elsewhere in this document. These two systems may share a venous return line, and are connected by a valve or other flow control device.
The passive source of aspiration may be a site with lower pressure, for example a sheath inserted into a central vein (for venous return) or an IV bag placed at a vertical level that would vary depending on what amount of negative pressure is desired.
In an embodiment, the arterial access device 3510 at least partially inserts into the common carotid artery CCA and the venous return device 3515 at least partially inserts into a venous return site, such as the femoral vein or internal jugular vein, as described in more detail below. The venous return device 3515 can be inserted into the femoral vein FV via a percutaneous puncture in the groin. The arterial access device 3510 and the venous return device 3515 couple to opposite ends of the flow line 3520 at connectors. The distal end of the arterial access device 3510 with the occlusion element 3529 may be positioned in the ICA. Alternately, in some circumstances where the ICA access is extremely tortuous, it may be preferable to position the occlusion element more proximally in the common carotid artery. When flow through the internal carotid artery is blocked (using the occlusion element 3529), the natural pressure gradient between the internal carotid artery and the venous system causes blood to flow in a retrograde or reverse direction from the cerebral vasculature through the internal carotid artery and through the flow line 3520 into the venous system.
In another embodiment, the arterial access device 3510 accesses the common carotid artery CCA via a transcarotid approach while the venous return device 3515 access a venous return site other than the femoral vein, such as the internal jugular vein. In another embodiment, the system provides retrograde flow from the carotid artery to an external receptacle, for example an IV bag, rather than to a venous return site. The arterial access device 3510 connects to the receptacle via the flow line 3520, which communicates with the flow control assembly 3525. The retrograde flow of blood is collected in the receptacle. If desired, the blood could be filtered and subsequently returned to the patient. The pressure of the receptacle could be set at zero pressure (atmospheric pressure) or even lower, causing the blood to flow in a reverse direction from the cerebral vasculature to the receptacle.
Exemplary Embodiments of Thrombectomy Devices
It should be appreciated that other mechanical thrombectomy catheters may be used in a similar manner with the vascular access and reverse flow system as described above. Mechanical thrombectomy devices may coil-tipped retrievers, stent retrievers, expandable cages, wire or filament loops, graspers, brushes, or the like. These clot retrievers may include aspiration lumens to lower the risk of embolic debris leading to ischemic complications. Alternately, thrombectomy devices may include clot disruption elements such as fluid vortices, ultrasound or laser energy elements, balloons, or the like, coupled with flushing and aspiration to remove the thrombus. Some exemplary devices and methods are described in the following U.S. Patents and Patent Publications, which are all incorporated by reference in their entirety: U.S. Pat. Nos. 6,663,650, 6,730,104; 6,428,531, 6,379,325, 6,481,439, 6,929,632, 5,938,645, 6,824,545, 6,679,893, 6,685,722, 6,436,087, 5,794,629, U.S. Patent Pub. No. 20080177245, U.S. Patent Pub. No. 20090299393, U.S. Patent Pub. No. 20040133232, U.S. Patent Pub. No. 20020183783, U.S. Patent Pub. No. 20070198028, U.S. Patent Pub. No. 20060058836, U.S. Patent Pub. No. 20060058837, U.S. Patent Pub. No. 20060058838, U.S. Patent Pub. No. 20060058838, U.S. Patent Pub. No. 20030212384, and U.S. Patent Pub. No. 20020133111.
A major drawback to prior thrombectomy devices is the need to re-cross the occlusion with a guidewire and microcatheter if the thrombectomy device did not remove enough of the occlusion to restore adequate flow, and additional attempts are needed to remove the occlusion. Currently, a single-lumen microcatheter is used to deliver the thrombectomy device. The microcatheter is placed over a guidewire, the guidewire is then removed and the thrombectomy device is delivered. When removing the occlusion both the microcatheter and device are pulled back and the access across the occlusion is lost. Thus if the attempt at removal was unsuccessful or incomplete and an additional attempt is required, the guidewire and microcatheter must again cross the occlusion. As mentioned above, this extra step of re-crossing the occlusion takes time and incurs risk of distal vessel injury. An embodiment of this disclosure, shown in
Exemplary Embodiments of Perfusion Devices
In an embodiment, the system may include a way to perfuse the cerebral vasculature distal to the thrombotic blockage and ischemic brain tissue via a perfusion catheter delivered, for example, through the arterial access device 2010 to a site distal to the thrombotic occlusion 10. The perfusion catheter is adapted to deliver a perfusion solution to a desired location. Perfusion solution may include, for example, autologous arterial blood, either from the flow line of a passive reverse flow circuit 3500 or from another artery, oxygenated solution, or other neuroprotective agent. In addition, the perfusion solution may be hypothermic to cool the brain tissue, another strategy which has been shown to minimize brain injury during periods of ischemia. The perfusion catheter may also be used to deliver a bolus of an intra-arterial thrombolytic agent pursuant to thrombolytic therapy. Typically, thrombolytic therapy may take up to 1-2 hours or more to clear a blockage after the bolus has been delivered. Mechanical thrombectomy may also take up to 1 to 2 hours to successfully recanalize the blocked artery. Distal perfusion of the ischemic region may minimize the level of brain injury during the stroke treatment procedure. Embodiments of distal perfusion are described below.
In an alternate embodiment, as shown in
In another embodiment, as shown in
The perfusion catheter may also provide perfusion to aid in thrombus removal.
In addition to providing pressure distal to the occlusion, the perfusion fluid from proximal perfusion catheter 3800 can supply blood to smaller vessels (perforators) originating in or just proximal to the occlusion. The shaft of the perfusion catheter 3800 may also be used as a rail or conduit for delivery of a therapeutic device such as stentriever or thrombectomy device.
In an embodiment, the perfusion lumen and the guide wire lumen are two separate lumens, configured for example as in
Perfusion catheters 3600 or 3800 may include an element for monitoring blood pressure. In an embodiment, the pressure monitoring element is a dedicated internal lumen in the perfusion catheter 3600 or 3800, wherein the lumen is fluid-filled and connected to a pressure transducer on the proximal end of the perfusion catheter. A pressure transducer on the catheter itself may also be used. Alternately, a pressure measuring guide wire may be inserted through an internal lumen of the perfusion catheter 3600 or 3800 to a location where pressure is to be monitored.
Alternatively, cerebral perfusion can include cerebral retroperfusion as described by Frazee et al. This embodiment involves selective cannulation and occlusion of the transverse sinuses via the internal jugular vein, and infusion of blood via the superior sagittal sinus to the brain tissue, during treatment of ischemic stroke. The following articles, which are incorporated herein by reference in their entirety, described cerebral retroperfusion and are incorporated by reference in their entirety: Frazee, J. G. and X. Luo (1999). “Retrograde transvenous perfusion.” Crit Care Clin 15(4): 777-88, vii.; and Frazee, J. G., X. Luo, et al. (1998). “Retrograde transvenous neuroperfusion: a back door treatment for stroke.” Stroke 29(9): 1912-6. This perfusion, in addition to providing protection to the cerebral tissue, may also cause a retrograde flow gradient in the cerebral arteries. Used in conjunction with the system 100, a retroperfusion component may provide oxygen to brain tissue, as well as aid in capture of embolic debris into the reverse flow line during recanalization of the thrombotic occlusion 10.
It should be appreciated that other perfusion catheters or systems may be used with the system 100, for example those described by U.S. Pat. Nos. 6,435,189 and 6,295,990, which are incorporated by reference in their entirety.
Exemplary Methods and Devices for Transcarotid Vessel Closure
Any type of closing element, including a self-closing element, a suture-based closing element, or a hydrostatic seal element, may be deployed on or about the penetration in the wall of the common carotid artery prior to withdrawing the arterial access device 2010 at the end of the procedure. Described herein are vessel closure methods and devices that have been specifically configured for transcarotid vessel closure. The following U.S. Patent Applications, which are incorporated herein by reference in their entirety, describe exemplary closure devices and methods: U.S. Patent Publication No. 20100042118, entitled “Suture Delivery Device”, and U.S. Patent Publication No. 20100228269, entitled “Vessel Closure Clip Device”. Additional examples of transcarotid vessel closure devices and methods are described in U.S. Provisional Application Ser. No. 61/994,623, filed May 16, 2014, which is incorporated by reference herein in its entirety. U.S. Provisional Application Ser. No. 62/074,964 entitled “Vessel Access and Closure Assist System and Method” and filed Nov. 4, 2014 and U.S. patent application Ser. No. 12/540,341 entitled “Suture Closure Device” are also incorporated herein by reference in their entirety.
The closing element may be deployed at or near the beginning of the procedure in a step termed “pre-closure”, or, the closing element could be deployed as the sheath is being withdrawn. In an embodiment, vessel closure can be accomplished by a suture-based blood vessel closure device. The suture-based vessel closure device can place one or more sutures across a vessel access site such that, when the suture ends are tied off after sheath removal, the stitch or stitches provide hemostasis to the access site. The sutures can be applied either prior to insertion of the procedural sheath through the arteriotomy or after removal of the sheath from the arteriotomy. The device can maintain temporary hemostasis of the arteriotomy after placement of sutures but before and during placement of a procedural sheath, if a pre-closure step us used, and can also maintain temporary hemostasis after withdrawal of the procedural sheath but before tying off the suture. Some exemplary suture-based blood vessel disclosure devices are described in the following U.S. Patents, which are incorporated herein by reference in their entirety: U.S. Pat. Nos. 6,562,052; 7,001,400; and 7,004,952.
In an embodiment, the system includes an ultrasound probe element, which when used with an ultrasound imaging system is configured to identify the desired site of carotid arterial access to determine that is suitable for percutaneous puncture, for example to verify that there is no vascular disease in the vessel. The probe will also visualize surrounding anatomy such as the internal jugular vein, to ensure that access can be achieved without comprising these other structures. In addition, the probe may be used to visualize the access site after vessel closure to verify that hemostasis has been achieved. If needed, the probe may be used to provide localized compression at the site of the puncture as needed to ensure hemostasis. For example, after vessel closure the probe is used to image the closure site. If blood is seen flowing from the site, the probe is pressed down to compress the site. The user periodically relaxes the pressure on the probe to assess if hemostasis has been achieved. If it has not, pressure is reapplied. If it has, the probe may be removed.
In an embodiment shown in
Exemplary Methods of Use
As illustrated in
Once the arterial access device is positioned, a diagnostic angiogram may be performed via a microcatheter which has been configured for transcarotid access and which is placed through the arterial access device. Diagnostic angiograms are performed throughout the procedure to determine the progress of the procedure.
A catheter 2030 is placed through the arterial access device 2010 or the guide catheter 2105 and positioned such that the distal tip reaches the treatment site. If desired, a coaxial system of devices comprising a guide wire, a microcatheter, and the catheter 2030 are inserted together through the arterial access device 2010 and advanced towards the treatment site. Alternately, a tapered dilator with or without a microcatheter tip may be substituted for the microcatheter. Alternately, a microcatheter and guide wire may be placed inside the tapered dilator. The removable proximal extension, if used, may be removed prior to introduction of the telescoping devices, or the devices may be inserted through the removable proximal extension. The microcatheter, or tapered dilator, and guide wire are then advanced to access and cross the cerebral occlusion. The microcatheter or dilator may be used to perform the angiogram of the cerebral circulation proximal and distal to the occlusion. The microcatheter may also used as a rail to advance the catheter.
Typically, the largest size catheter will be selected which is able to be safely navigated to the occlusion, to maximize the force and luminal area for aspiration of the occlusion. Aspiration is then initiated through the catheter. This may be done manually, with an aspiration pump, or with another aspiration source, or via the flow controller as described above. If the thrombus is too large or too strongly embedded into the vasculature such that it is not possible to remove the occlusion via aspiration alone, further steps are taken to remove the occlusion. A thrombectomy device 15 may be deployed through the arterial access device to remove the clot. During clot retrieval, passive or active aspiration may be applied via the arterial access device, or the guide catheter to minimize or eliminate the amount of distal emboli.
If the catheter is unable to reach the treatment site, or if a secondary more distal treatment site needs to be reached after removal of a first occlusion, a second, smaller diameter catheter may be inserted through the first catheter, and positioned at the distal treatment site. Alternately, the first catheter may be removed and exchanged for the second catheter. A guidewire and/or microcatheter may be placed through the first catheter to facilitate the exchange.
If there is difficulty navigating the catheter of the desired size to the treatment site, a device may be deployed distal to the site and expanded to act as an anchor to aid in advancing the catheter as shown in
At any time during the procedure, a balloon on the arterial access device 2010 may be inflated at this point to reduce forward arterial pressure on the occlusion. The inflated balloon may also increase the stability of the arterial access in the vessel to increase the support for advancement of devices through the arterial access device. Additionally, the arterial access device 2010 or guide catheter 2015 may be connected to passive or active aspiration as desired to provide embolic protection while not compromising perfusion of the brain. This may be accomplished by selective periods of reverse, stopped, and antegrade flow. At the conclusion of the procedure, the arterial access sheath may be closed by methods as described previously. Ultrasound may again be employed, in this instance to ascertain and/or ensure hemostasis. If appropriate, the ultrasound probe may be used to apply pressure at the access site until hemostasis is achieved.
In a variation of this procedure, a guide catheter 2105 is inserted through the arterial access device 2010 which has been previously inserted into the CCA, as shown in
In yet a further embodiment, the system is used to provide distal protection and/or perfusion during the procedure. In this embodiment, a perfusion catheter is inserted through the arterial access device 2010 or through the catheter 2030, and positioned across the lumen and inflated at a point distal to the occlusion. The perfusion catheter may be connected to a perfusion pump to perfuse oxygenated blood or perfusion solution to the ischemic brain via a distal opening in the perfusion catheter. In an embodiment, the perfusion catheter is a balloon-tipped catheter. The balloon is inflated at a point distal to the occlusion. This balloon acts to prevent emboli from progressing distally during removal or recanalization of the occlusion. The perfusion catheter may also be connected to a flush source to perfuse proximal to the occlusion balloon via proximal ports in the perfusion catheter. This maneuver essentially provides a back pressure on the occlusion and may aid it its removal.
In the instance where there is also a carotid artery stenosis which requires treatment either before or after treatment of the cerebral occlusion, an angioplasty balloon or stent may be deployed in the stenosis via the introducer sheath. If embolic protection is desirable during intervention of the carotid stenosis, the introducer sheath may have an occlusion balloon and a connection to a reverse flow line as shown in
In yet another method of use, a telescoping system as depicted in
This method provides speed and ease of use benefits over traditional configuration wherein the aspiration is applied via a catheter which is inserted the entire length of the arterial access device. For this traditional configuration, aspiration is applied directly to the proximal end of the catheter, and must be applied during the entire time the catheter is being removed from the access device. Likewise the catheter must be removed very slowly, otherwise there is risk that the clot is lost and either lodged back in the vasculature or in the access device. In contrast, for the telescoping method, direct aspiration to the occlusion may be applied via the arterial access device rather than the catheter, and therefore once the clot is entered into the access device the catheter may be rapidly removed. This difference may halve or even further reduce the time for each “pass” of an aspiration attempt. For many stroke procedures, more than one pass is required to completely remove the occlusion Furthermore, the fact that the back half of the aspiration lumen is the larger lumen of the access device rather than the smaller lumen of the catheter makes aspiration more effective. It will be more likely that the clot can be suctioned without “corking” at the tip or in the lumen of the catheter, and increase the rate of aspiration into the aspiration device.
In a variation of this method, a stentriever or similar device may be used as an adjunct to aspiration to remove the occlusion. It may be used initially before placement of the catheter to provide immediate perfusion through the occlusion, may be used to help provide counter-traction and rail support during positioning of the catheter, may aid in dislodging the clot into the catheter, or some or all of the above.
While this specification contains many specifics, these should not be construed as limitations on the scope of an invention that is claimed or of what may be claimed, but rather as descriptions of features specific to particular embodiments. Certain features that are described in this specification in the context of separate embodiments can also be implemented in combination in a single embodiment. Conversely, various features that are described in the context of a single embodiment can also be implemented in multiple embodiments separately or in any suitable sub-combination. Moreover, although features may be described above as acting in certain combinations and even initially claimed as such, one or more features from a claimed combination can in some cases be excised from the combination, and the claimed combination may be directed to a sub-combination or a variation of a sub-combination. Similarly, while operations are depicted in the drawings in a particular order, this should not be understood as requiring that such operations be performed in the particular order shown or in sequential order, or that all illustrated operations be performed, to achieve desirable results. Therefore the spirit and scope of the appended claims should not be limited to the description of the embodiments contained herein.
This application is a Continuation of co-pending U.S. patent application Ser. No. 15/699,401, filed Sep. 8, 2017, which is a continuation of U.S. patent application Ser. No. 15/425,460, filed on Feb. 6, 2017, now U.S. Pat. No. 10,471,233, which is a continuation of U.S. patent application Ser. No. 14/576,953 filed on Dec. 19, 2014 now U.S. Pat. No. 9,561,345, and claims priority to (1) U.S. Provisional Patent Application Ser. No. 61/919,945, filed Dec. 23, 2013, entitled “Methods and Systems for Treatment of Acute Ischemic Stroke”; (2) U.S. Provisional Patent Application Ser. No. 62/083,128, filed Nov. 21, 2014, entitled “Methods and Systems for Treatment of Acute Ischemic Stroke”; (3) U.S. Provisional Patent Application Ser. No. 62/029,799, filed Jul. 28, 2014, entitled “Intravascular Catheter with Smooth Transitions of Flexibility”; (4) U.S. Provisional Patent Application Ser. No. 62/075,101, filed Nov. 4, 2014, entitled “Transcarotid Neurovascular Catheter”; (5) U.S. Provisional Patent Application Ser. No. 62/046,112, filed Sep. 4, 2014, entitled “Methods and Devices for Transcarotid Access”; and (6) U.S. Provisional Patent Application Ser. No. 62/075,169, filed Nov. 4, 2014, entitled “Methods and Devices for Transcarotid Access.” The disclosures of the patent applications are incorporated by reference in their entirety and priority to the filing dates is claimed.
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| Number | Date | Country | |
|---|---|---|---|
| 20200345981 A1 | Nov 2020 | US |
| Number | Date | Country | |
|---|---|---|---|
| 62083128 | Nov 2014 | US | |
| 62075169 | Nov 2014 | US | |
| 62075101 | Nov 2014 | US | |
| 62046112 | Sep 2014 | US | |
| 62029799 | Jul 2014 | US | |
| 61919945 | Dec 2013 | US |
| Number | Date | Country | |
|---|---|---|---|
| Parent | 15699401 | Sep 2017 | US |
| Child | 16931234 | US | |
| Parent | 15425460 | Feb 2017 | US |
| Child | 15699401 | US | |
| Parent | 14576953 | Dec 2014 | US |
| Child | 15425460 | US |
