This application is a division of U.S. application Ser. No. 11/274,889, filed Nov. 14, 2005.
BACKGROUND OF THE INVENTION
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The present invention relates principally to a system for the delivery and deployment of a replacement heart valve. Heart valve surgery is used to repair or replace diseased heart valves. Valve surgery is an open-heart procedure conducted under general anesthesia. An incision is made through the patient's sternum (sternotomy), and the patient's heart is stopped while blood flow is rerouted through a heart-lung bypass machine.
Valve replacement may be indicated when there is a narrowing of the native heart valve, commonly referred to as stenosis, or when the native valve leaks or regurgitates. When replacing the valve, the native valve is excised and replaced with either a biologic or a mechanical valve. Mechanical valves require lifelong anticoagulant medication on to prevent blood clot formation, and clicking of the valve often may be heard through the chest. Biologic tissue valves typically do not require such medication. Tissue valves may be obtained from cadavers or may be porcine, equine, bovine, or other suitable material, and are commonly attached to synthetic rings that are secured to the patient's heart.
Valve replacement surgery is a highly invasive operation with significant concomitant risk. Risks include bleeding, infection, stroke, heart attack, arrhythmia, renal failure, adverse reactions to the anesthesia medications, as well as sudden death. Two to five percent of patients die during surgery.
Post-surgery, patients temporarily may be confused due to emboli and other factors associated with the heart-lung machine. The first 2-3 days following surgery are spent in an intensive care unit where heart functions can be closely monitored. The average hospital stay is between 1 to 2 weeks, with several more weeks to months required for complete recovery.
In recent years, advancements in minimally invasive surgery and interventional cardiology have encouraged some investigators to pursue percutaneous replacement of the aortic heart valve. Percutaneous Valve Technologies (“PVT”) Inc., has developed a balloon-expandable stent integrated with a bioprosthetic valve. The stent/valve device is deployed across the native diseased valve to permanently hold the valve open, thereby alleviating a need to excise the native valve and to position the bioprosthetic valve in place of the native valve. PVT's device is designed for delivery in a cardiac catheterization laboratory under local anesthesia using fluorscopic guidance, thereby avoiding general anesthesia and open-heart surgery. The device was first implanted in a patient in April of 2002.
PVT's device suffers from several drawbacks. Deployment of PVT's stent is not reversible, and the stent is not retrievable. This is a critical drawback because improper positioning too far up towards the aorta risks blocking the coronary ostia of the patient. Furthermore, a misplaced stent/valve in the other direction (away from the aorta, closer to the ventricle) will impinge on the mitral apparatus and eventually wear through the leaflet as the leaflet continously rubs against the edge of the stent/valve.
Another drawback of the PVT device is its relatively large cross-sectional delivery profile. The PVT system's stent/valve combination is mounted onto a delivery balloon, making retrograde delivery through the aorta challenging. An antegrade transseptal approach may therefore be needed, requiring puncture of the septum and routing through the mitral valve, which significantly increases complexity and risk of the procedure. Very few cardiologists are currently trained in performing a transseptal puncture, which is a challenging procedure by itself
Other prior art replacement heart valves use self-expanding stents as anchors. In the endovascular aortic valve replacement procedure, accurate placement of aortic valves relative to coronary ostia and the mitral valve is critical. Standard self-expanding systems have very poor accuracy in deployment, however. Often the proximal end of the stent is not released from the delivery system until accurate placement is verified by fluoroscopy, and the stent typically jumps once released. It is therefore often impossible to know where the ends of the stent will be with respect to the native valve, the coronary ostia and the mitral valve.
Also, visualization of the way the new valve is functioning prior to final deployment is very desirable. Visulization prior to final and irreversible deployment cannot be done with standard self-expanding systems, however, and the replacement valve is often not fully functional before final deployment.
Another drawback of prior art self-expanding replacement heart valve systems is their lack of radial strength. In order for self-expanding systems to be easily delivered through a delivery sheath, the metal needs to flex and bend inside the delivery catheter without being plastically deformed. In arterial stents, this is not a challenge, and there are many commercial arterial stent systems that apply adequate radial force against the vessel wall and yet can collapse to a small enough diameter to fit inside a delivery catheter without plastically deforming.
However when the stent has a valve fastened inside it, as is the case in aortic valve replacement, the anchoring of the stent to vessel walls is significantly challenged during diastole. The force to hold back arterial pressure and prevent blood from going back inside the ventricle during diastole will be directly transferred to the stent/vessel wall interface. Therefore the amount of radial force required to keep the self expanding stent/valve in contact with the vessel wall and not sliding will be much higher than in stents that do not have valves inside of them. Moreover, a self-expanding stent without sufficient radial force will end up dilating and contracting with each heartbeat, thereby distorting the valve, affecting its function and possibly migrating and dislodging completely. Simply increasing strut thickness of the self-expanding stent is not a practical solution as it runs the risk of larger profile and/or plastic deformation of the self-expanding stent.
U.S. patent application Ser. No. 2002/0151970 to Garrison et al. describes a two-piece device for replacement of the aortic valve that is adapted for delivery through a patient's aorta. A stent is percutaneously placed cross the native valve, then a replacement valve is positioned within the lumen of the stent. By separating the stent and the valve during delivery, a profile of the device's delivery system may be sufficiently reduced to allow aortic delivery without requiring a transseptal approach. Both the stent and a frame of the replacement valve may be balloon-expandable or self-expanding.
While providing for an aortic approach, devices described in the Garrison patent application suffer from several drawbacks. First, the stent portion of the device is delivered across the native valve as a single piece in a single step, which precludes dynamic repositioning of the stent during delivery. Stent foreshortening or migration during expansion may lead to improper alignment.
Additionally, Garrison's stent simply crushes the native valve leaflets against the heart wall and does not engage the leaflets in a manner that would provide positive registration of the device relative to the native position of the valve. This increases an immediate risk of blocking the coronary ostia, as well as a longer-term risk of migration of the device post-implantation. Further still, the stent comprises openings or gaps in which the replacement valve is seated post-delivery. Tissue may protrude through these gaps, thereby increasing a risk of improper seating of the valve within the stent.
One potential solution to these issues is the development and use of a repositionable heart valve, as has been described in U.S. patent application Ser. No. 10/746,280 filed on Dec. 23, 2003 entitled “Repositionable Heart Valve and Method.” The contents of that application are herein incorporated by reference. The repositionable heart valve resolves numerous issues presented by Garrison's stent. However deploying and redeploying the heart valve is not without its own set of technical challenges.
One challenge with using mechanical elements to connect the user control with an implantable device and/or its delivery system is assuring that the user controls properly actuate the mechanical components of the system, particularly when the deployment tool or catheter navigates the tortuous path from its insertion point to the deployment location, such as the heart. For example, some deployment systems use multiple actuators elements extending along at least part of the path from insertion point to deployment location to perform the deployment function. Bends, twists, and rotations in the catheter can cause internal physical path lengths to vary widely.
If differences in actuator path lengths are not properly compensated for, the operation of the deployment tool may not be predictable. For instance, some actuators may have a shorter path length to the implant and its deployment mechanism than others. If all the actuators are used simultaneously, the operator would expect an even distribution of the deployment operation. Instead those paths that are shorter might function sooner, while those that are longer might operate later. The reverse is also true if the shorter lengths are overly relaxed due to slack in the actuation elements, while the longer path ways are taut because the actuation elements are strained because of the longer path length. In either scenario, the operation and deployment become unpredictable and unreliable. If stresses on the actuation elements are too great, they may cause deformation or distortion of the implant before any of the actuation elements are even used. This could result in serious complications that may require invasive procedures to intervene.
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OF THE INVENTION
Thus it is an objective of the present invention to provide for a system capable of deploying a replacement heart valve where the system has a compensation mechanism for correcting path length differences among the mechanical actuation elements.
It is another objective of the present invention to provide a system able to exert the needed actuation forces for both deployment, and redeployment of the replacement heart valve.
Yet another objective is to provide for a deployment system having a reliable actuator system for safely delivering the proper level of forces to the implant and the deployment mechanism that the implant requires.
There is still another need for a method of operating such a system to provide safe and effective steps to handle the deployment of a replacement heart valve or other vascular implant.
One or more of the objectives above are met using an implant system comprising an implant, and a deployment tool adapted to deploy the implant. The deployment tool comprises an actuation controller and a plurality of elements adapted to apply forces to one or more implant deployment mechanism(s). Each actuation element is adapted to extend along an actuation element path within a patient's vasculature. There is also an actuation element compensation mechanism adapted to compensate for differences in length between the actuation element paths.
There is also a method for deploying an implant using the system of the present invention. The method comprises the steps of first endovascularly delivering an implant and implant deployment mechanism to an implant site. Second applying an actuation force to the implant deployment mechanism through actuation elements extending through the patient's vasculature while compensating for differences in length between actuation element path lengths to deploy the implant.
INCORPORATION BY REFERENCE
All publications and patent applications mentioned in this specification are herein incorporated by reference to the same extent as if each individual publication or patent application was specifically and individually indicated to be incorporated by reference.
BRIEF DESCRIPTION OF THE DRAWINGS
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The novel features of the invention are set forth with particularity in the appended claims. A better understanding of the features and advantages of the present invention will be obtained by reference to the following detailed description that sets forth illustrative embodiments, in which the principles of the invention are utilized, and the accompanying drawings of which:
FIG. 1A shows an implant to be used with the present invention.
FIG. 1B-C illustrate two cut away views of the implant.
FIG. 2 provides an illustration of the system.
FIG. 3A shows one embodiment of an actuation element path length compensation
FIG. 3B illustrates a cross section of the deployment tool.
FIG. 3C illustrates a mold used in manufacturing the actuation element path length compensation section.
FIG. 4 illustrates a multiple actuation element compensation mechanism.
FIG. 5 shows a pulley style compensation mechanism.
FIGS. 6A-B show an actuation element path length compensation mechanism using a common path for multiple actuation elements.
FIG. 7 shows a length style compensation mechanism.
FIGS. 8A-J illustrate additional compensation mechanisms.
FIG. 9 illustrates a hydraulic compensation mechanism.
FIGS. 10A-E illustrates an implant deployment.
FIGS. 11A-B provide an illustration of implant and actuation element details according to alternative embodiments of the invention.
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OF THE INVENTION
The invention is drawn to methods, mechanisms and tools for the endovascular deployment of medical implants, such as replacement heart valves. According to some embodiments of the invention, the deployment process includes actuating one or more actuation elements to control and/or perform actions of the implant deployment mechanism, or mechanical elements of the implant itself. The operation of the implant deployment mechanism or the mechanical elements of the implant are often fully reversible, allowing a physician to partially deploy and then reverse the deployment operation of (“undeploy”) the implant. This provides the ability to reposition and redeploy the implant. As a general reference, the orientation of the system is referred to as is traditional for a medical device catheter. The proximal end is nearest the physician or operator when the system is being used. The distal end is furthest away from the operator and is in the patient's vasculature. To facilitate imaging of the implant during a procedure, the deployment tool may have a lumen for providing a contrast agent to the site where the implant is being positioned within the patient's body.
One embodiment of the invention provides an implant system having an implant adapted for endovascular delivery and deployment and a deployment tool adapted to deploy the implant. The implant of the present invention can be any suitable for deployment into the human body. Possible implants envisioned for deployment with the present system are those previously described in co-pending U.S. patent application Ser. No. 10/746,280 entitled “REPOSITIONABLE HEART VALVE,” filed on Dec. 23, 2003; Ser. No. 10/893,131 entitled “METHODS AND APPARATUS FOR ENDOVASCULARLY REPLACING A PATIENT′S HEART VALVE” field on Jul. 15, 2004; Ser. No. 10/893,151 entitled “METHODS AND APPARATUS FOR ENDOVASCULARLY REPLACING A PATIENT′S HEART VALVE” filed on Jul. 15, 2004; Ser. No. 10/746,120 entitled “EXTERNALLY EXPANDABLE HEART VALVE ANCHOR AND METHOD” filed on Dec. 23, 2003; Ser. No. 10/746,285 entitled “RETRIEVABLE HEART VALVE ANCHOR AND METHOD” filed Dec. 23, 2003; Ser. No. 10/982,692 entitled “RETRIEVABLE HEART VALVE ANCHOR AND METHOD” filed on Nov. 5, 2004; Ser. No. 10/746,872 entitled “LOCKING HEART VALVE ANCHOR” filed on Dec. 23, 2003; and Ser. No. 10/870,340 entitled “EVERTING HEART VALVE” filed on Jun. 16, 2004. Additional forms of a replacement heart valve implant will be illustrated herein.
The deployment tool is designed to deliver the implant to an implant site and to deploy the implant, such as described in the above referenced patent application(s). In some embodiments, the deployment is controlled through actuation elements which are connected to actuators (such as knobs, levers, etc.) in an actuation controller (such as a handle). When a user exerts force on an actuator, by either pushing or pulling the actuator, the actuation element conveys a force to whatever the actuation element is connected to, such as an implant deployment mechanism or the implant. For minimally invasive implant procedures (percutaneous, endovascular, laparoscopic, etc.), the actuator controller and actuators are often remote from the actuated implant. In addition, the path from actuator to implant—the path along which the actuation elements extend—may be other than a straight line. For example, the delivery tool for a percutaneous endovascular delivery of a replacement heart valve may extend through the arterial vasculature from an opening in the patient's femoral artery at the thigh to the patient's aorta, a route that has multiple bends and turns. Because some of the deployment tool's actuation elements extend through a bent or turned section of the deployment tool, the path lengths through which various actuation elements need to operate may differ. It may therefore be desirable to compensate for these differences in path length, or to otherwise equate displacements and force of the actuation element paths.
In some embodiments, deployment is achieved when an operator uses the actuation controller to apply proximally or distally directed forces on the implant deployment mechanism. These forces are translated into displacements. Force is conveyed from the actuation controller through the actuation elements to an implant deployment mechanism. The actuation elements extend along actuation element paths. This invention provides an actuation compensation mechanism incorporated into the deployment tool that compensates for variations in length between actuation element paths.
The actuation controller is located on the proximal end of the deployment tool. The actuation controller may be a handle or gripping device having one or more actuators incorporated into it. The actuators may be, e.g., mechanical, fluid or electrical actuators.
The actuation elements may be, e.g., a material or substance used to convey force from the actuation controller to the implant deployment mechanism. Wires, threads (such as polymer threads) or sutures are examples of actuation elements used to provide direct mechanical linkage between the actuation controller and the implant. In other embodiments, the actuation elements may have a fluid component. Other possible applications for the actuation element include the use of electromechanical or electromotive components. Another alternative is the use of shape memory alloys that can be electrically or thermally actuated.
The actuation element paths may be along individual lumens (one for each actuation element), or there may be a lesser number of lumens than actuation element paths (e.g., where multiple actuation elements share a lumen). All actuation elements may share a single path, in which case there is a single actuation element path extending from the actuation controller to the either the implant or the implant deployment mechanism. The actuation element paths may be sealed against the environment so that blood and other bodily fluids do not escape from the patient and to minimize contamination by outside environmental factors. The introduction of the deployment tool and the actuation paths may be similar to those techniques used to introduce catheters, laparoscopes, endoscopes, etc., into the body.
In some embodiments, the implant deployment system comprises a catheter, and the actuation elements are disposed within the catheter. It will be appreciated that there is no need for path length compensation where there is no differences in path length between two points. Thus the actuation element compensation mechanism does not have to adapt the path lengths for the entire length of the deployment tool or catheter. In some embodiments, path length compensation is therefore provided only in the sections of the deployment tool that actually experience actuation element path length differences.
For instance, if the deployment tool were to experience a substantial bend (such as when navigating the aortic arch), the path length differences between actuation elements on the outer curve of the deployment tool will be greater than those on the inside of the curve of the deployment tool in that section of the deployment tool and will be compensated for by this invention. In one embodiment, the actuation element paths extend in a spiral fashion about the long axis of the deployment tool. By rotating the actuation element paths about this axis so that each path completes at least a 360 degree rotation about the central axis over the bend area of the deployment tool, the effect of the bend is minimized since all actuation elements will experience the same path length over this region. It is not important for each actuation element path to have a uniform pitch across any length of the deployment tool or bend, only for each lumen to make an equal number of turns about the central axis over a given distance. If there are multiple regions along the length of the deployment tool where compensation will be needed, the deployment tool can be designed to provide the compensation necessary. For instance, there may be multiple sections of the deployment tool that have spiral actuation paths, as well as intermediate sections where the actuation element paths are substantially straight.
The correspondence of the actuation elements to the actuation element paths is such that the system may be designed so that the actuation element compensation mechanism comprises a catheter with a number of distinct actuation element lumens. In one embodiment, the actuation elements are disposed in a 1:1 ratio with the actuation element paths.
In yet another embodiment, the actuation controller incorporates the actuation element compensation mechanism. The actuation element compensation mechanism may be built into the actuation controller, the actuators or be a part adapted to be fitted onto the actuation controller during use.
One example of an actuation compensation mechanism incorporated into the actuation controller is the use of a fluid compensation device. Here the actuation element compensation mechanism is a manifold fluid reservoir combined with a number of pistons. Each piston is operatively connected to an actuation element, and each has a surface exposed to fluid from the reservoir. There may also be a source for pressurized fluid communicating with the reservoir. A movable wall or diaphragm can be adapted to be a movable wall to change the volume of the reservoir.
In still another embodiment, the actuation element compensation mechanism may comprise a movable mechanical linkage connected to the actuation elements. The mechanical linkage may be a single pivoting element, or a group of pivoting elements, a spring at the proximal end of each actuation element, or one or more pulleys. To facilitate the operation and movement of each actuation element, the system may incorporate an actuation element operation mechanism to permit each actuation element to be moved separately, in groups or in unison.
The actuation element compensation mechanism may be incorporated into the body of a catheter comprising at least two actuation element lumens. A first actuation element is disposed in a first lumen and a second actuation element is disposed in a second lumen.
In yet another alternative embodiment, the implant system is provided with a catheter type body with a prefabricated shape bent to approximate the expected bends in the anatomy through which it will be delivered. The actuation elements are set to different lengths at manufacture to accommodate the known different path lengths associated with the bend. The catheter would be sufficiently flexible to be deployed in a straightened configuration similar to other catheters for minimally invasive procedures; however the catheter would assume the prefabricated bent shape either through a controlled operation or through a natural tendency to assume the bent shape. Once the catheter is in the bent shape, the pre-set actuation element lengths offset the differing lengths of the actuation element paths through the catheter body. Thus if the first actuation element path is shorter than the second (or N value of actuation element paths) then the first actuation element is correspondingly shorter than the second actuation element (and so forth to the N value of actuation elements and paths).
In some embodiments, the deployment device may need very few actuation elements, or the actuation elements can be grouped while they traverse the actuation element paths. In this manner a plurality of actuation elements may be placed into a single lumen. The actuation element path will run substantially parallel to and offset from a central axis of the catheter.
The use of the system described above also entails a novel method for placing an implant where an actuation compensation mechanism must be used. The method of deploying an implant using the present system comprises the steps of first endovascularly delivering an implant and implant deployment mechanisms to an implant site, and second applying an actuation force to the implant deployment mechanisms through actuation elements extending through the patient\'s vasculature while compensating for differences in length between actuation element path lengths to deploy the implant.
The compensating step may involve moving a proximal end of one actuation element proximal to a proximal end of another actuation element. The moving step may involve applying fluid pressure to a piston surface operatively connected to each actuation element. The compensating step may also involve locking relative positions of the proximal ends of the actuation elements prior to the applying step.
Alternatively, the compensating step may involve moving a proximal end of one actuation element distal to a proximal end of another actuation element. Here the moving step may involve applying fluid pressure to a piston surface operatively connected to each actuation element. Once again, this may entail locking relative positions of the proximal ends of the actuation elements prior to the applying step.
In another alternative embodiment, the applying step may involve moving a hinged mechanical linkage to with proximal ends of the actuation elements are operatively connected. Instead of a hinged mechanical linkage, the step may be moving a mechanical linkage operatively connected to proximal ends of the actuation elements through a pulley.
In still another embodiment, the applying step may involve moving a mechanical linkage operatively connected to proximal ends of the actuation elements through springs.
The system and methods may be used to deploy any suitable implant into a patient; however the systems as described below are discussed primarily in association with the preferred embodiment, in which the implant is a replacement heart valve.
In referring to the accompanying drawings, a variety of conventions are used in the labeling of the many parts. Among the many parts of the present system some are labeled using alphabet scripts in addition to numerical labels. The convention of “number+letter” denotes there are multiple numbers of this part. For instance, actuation elements are labeled as 308a-n. A reference to the collective whole of actuation elements is referred to simply as 308. Where there are multiple discrete actuation elements shown in the drawings, these appear as 308a, 308b, 308c, etc. . . . The letter variables a-n denote a first part beginning with the letter “a” and going to an indefinite number of parts “n”. The letter “n” here does not denote the 14th letter of the alphabet and thus limit the part sequence to a maximum of 14 duplications of the part. “n” is used in the sense of a mathematical variable for as many multiples of a part as are needed. Furthermore, the drawings as presented are not to scale, either to each other or internally, but instead are offered in a manner to provide clearer illustration of the various embodiments and elements discussed herein.
The system of the present invention is designed to deliver and deploy an implantable device. Specifically the system is adapted to deliver and deploy an implantable device using a plurality of mechanical actuation elements in mechanical communication with the implant itself, as well as any number of additional deployment elements. By way of example, and for illustration purposes only, the present invention may be adapted and used with a radially expandable and foreshortening anchoring mechanism to help secure the placement of a replacement heart valve. An example of such a replacement is herein provided in FIG. 1A. Viewed here is an implantable device 600 being connected to the deployment tool through a set of radially disposed interface elements or fingers. Additionally actuation elements extend from the body of the deployment tool and connect to various actuatable portions of the implant 600. The implant may also have a prosthesis, such as a valve, disposed within it.
The detailed assembly of the implant may follow a number of design parameters and uses. One embodiment of an implant that may be used with the system of the present invention is described in U.S. patent application Ser. No. 10/746,280, entitled REPOSITIONABLE HEART VALVE AND METHOD and filed on Dec. 23, 2003. The implant has been reproduced herein in FIGS. 1A-C. The implant 600 has two major components, an anchor 602 and a replacement heart valve 606. Optionally, radiopaque bands 616 may be added to the implant to enhance viewing of the implant under fluoroscopy. The implant 600 can be deployed using a distal mechanical deployment device 402 located substantially on the end of the deployment tool. The anchor has a relatively long and narrow length 600i (FIG. 10A) in its pre-deployment state compared to its fully deployed state 600f (FIG. 10E).
The actuation elements described herein are illustrated with various interface points in the implant. FIG. 1B shows the implant cut open and laid flat; actuation elements 308 can be seen connecting to the lattice network of the anchor 602. Additional actuation elements 308a, 308b, 308c are shown interfacing with paired posts 608a, 608b, 608c and buckles 610a, 610b, 610c. The actuation elements 308, 308a-c can be surgical threads, wires, rods, tubes or other mechanical elements allowing for the mechanical linking of the actuators in the handle or actuation controller and the various components of implant 600 and/or its delivery system, such as posts 608, buckles 610. In operation, some of the actuation elements shown 308a, 308b, 308c may be drawn up so the posts attached to the actuation elements are drawn into and through the buckles 610a, 610b and 610c. The actuation elements 308 interface with the implant or deployment mechanism at various actuation element interface sites 604. While the posts are being drawn through the buckles, the anchor 602 goes through a foreshortening process to expand the radius of the anchor. When the anchor 602 is foreshortened to a deployed configuration, the posts are drawn up to lock in place with the buckles.
The deployment of the anchor is a fully reversible process until the lock has been locked via, e.g., mating a male interlocking element with a female interlocking element. After locking, deployment is completed by decoupling the actuation elements from the anchor.
FIGS. 2 and 3A show an implant system 10 designed to deploy an implant 600, such as a replacement heart valve 606 and anchor 604. Actuators 204a, 204b are movable in corresponding sliders 206a, 206b in the proximal handle 200 of a deployment tool 100 and provide an appropriate amount of force and/or displacement to the implant 600, to an implant deployment mechanism (that is, e.g., part of the deployment tool itself), and/or to release mechanisms at the actuator element/implant interfaces or at the actuator element/deployment mechanism interfaces regardless of path length differences taken by the actuation elements of the deployment tool 100 during a medical procedure. The deployment tool 100 has a deployment tool body 300 and an outer sheath 18. In one example, when deploying a replacement heart valve from the femoral artery through the aorta and across the aortic arch, a length of the deployment tool must bend nearly 180 degrees to make the placement possible as shown in FIG. 3A. This bend region 520 of the deployment tool 100 is where the actuation element path lengths begin to vary, with the effect realized at the distal end 400. The actuation element compensation mechanism 500 compensates for path length differences that result from this bend. As shown, the system 10 also has a guide wire lumen 114 (FIG. 3B) for slidably receiving a guide wire 14, a nose cone 406 for facilitating advancement of the system 10 through the vasculature, an outer sheath 18, and an outer sheath advancement actuator 20.
The actuation element compensation mechanism may be a mechanical arrangement of the actuation element paths over the length of a bend region, or it may be a mechanism designed to compensate through a flexible and adaptable adjustment system regardless of changes in path length during usage. The compensation mechanism may be positioned in the bend, proximally or distally. Though some embodiments are more advantageous than others depending on circumstances and environment, all are contemplated as alternative embodiments of the present invention.
FIG. 4 is an expanded view of the region 520 from FIG. 3A. Here the actuation element compensation mechanism 500 takes the form of winding the actuation element paths 306a, 306b, 306n in a spiral fashion about the central guide wire lumen 114. The number of actuation element paths that may be wound about the center is limited only by the physical size of the deployment tool 100.
The construction of the deployment tool uses technologies and materials as are appropriate for medical device catheters. The positioning of the various actuation element paths within the deployment tool may be fixed or variable. In one embodiment, the position of the various actuation element paths 308a, 308b, 308n are fixed and shown in cross section (FIG. 3B). This is accomplished by an extrusion process for making the core of the deployment tool body. A polymer material, such as PEBAX™, may be used to make the core. The core is extruded having the desired number of lumens. Beside the lumens that serve as the actuation element pathways 308, there may be additional lumens as are needed for placement and use of the deployment tool.
Once the core has been extruded, a fixed length is cut and prepared for shape setting. The shape setting involves threading each lumen with a PTFE coated, stainless steel mandrel. Then the core along with the mandrels are twisted so the lumens rotate about the central axis a desired number of rotations. The preferred rotations for the actuation element paths is 360-540 degrees (one to one-and-a-half twists). The twisted core is fed into a shaped metal mold M and baked in an oven to heat set the desired bend and twists into the core (FIG. 3C). Once this process is complete, the core is removed from the oven and allowed to cool. The twisted core is mated to a straight core section and welded together so the lumens match from the twisted heat set section, to the normal extruded section. The normal extruded section has a higher durometer value than the twisted section, to provide enhanced pushability during use.
Once the twisted section and the straight section are mated together properly, the core containing the actuation element pathways is combined with a braided wire heat set outer sheath. The sheath can be used to provide added guidance and movement control of the deployment tool during deployment, as well as radial compression force on the implant deployment mechanism and/or the implant. Overall the diameter of the deployment tool that is inserted into the body is 24 French or less. Preferably the diameter is 21 French or less.
Although the above description calls for an extruded core, it is also practical to make the core using a variety of other catheter building techniques. For instance, individual lumens may be designed and arranged in cable-like manner so the twisting of the actuation element paths occurs by winding individual lumens together. Alternatively the actuation element paths may be formed from a series of gap spaces in an axial layering arrangement. Additional methods may be readily apparent to those skilled in the art of catheter manufacturing.
In another embodiment, the actuation element compensation mechanism 500 uses a pulley and tackles 508 arrangement (FIG. 5). The pulley 522 can be controlled through an actuator 204. As the pulley line 526 is stretched tight through the actuator, the tackles 524a-c move in corresponding fashion to take up the slack in the pulley compensation device 508 and the actuation elements 308 extending through the deployment tool body 300. Once the slack in the actuation elements is taken up, the actuator 204 can exert force on the connectors 408a, 408b, 408c to pull the buckles 610a, 610b, 610c of the implant proximally.
In another embodiment there are numerous actuation element interface sites 408a-c to the deployment mechanism or the implant (FIG. 6A-B). There is at least one actuation element 308a-c linked to each actuation element interface site 408a-c. To at least partially compensate for differences in path length from the interface sites to the actuator, the actuation elements are disposed along a single actuation element path, such as by placing all actuation elements within a single lumen 506. The actuation elements may also be bundled together, either into a single line 310 such as a cable, or bundled to move together as a single unit in a harness so that the actuation elements reduce to a single primary actuation element extending to the proximal end to be linked to a single actuator 204. It is possible when using low friction materials, such as a Teflon™ coated polymer thread, or other suitable material, that the individual actuation elements may be harnessed into a single unit 310. Instead of being intertwined, the individual elements are laid side by side with a minimal amount of twining or braiding. Then at the actuation controller, each actuation element 308a-n is separated out and linked to an individual actuator 204a-n. In this manner it is possible to construct the same relationship of actuators 204 and actuation elements 308 and actuation element interface sites 408 without having to construct numerous actuation element paths.
In still another embodiment, if the deployment tool is configured for a particular application in the body where the bend is of a known length and angle, the individual actuation elements 308 can be preformed to correspond to the path lengths associated with the bend (FIG. 7). Here there are two actuation elements 308a, 308b traversing two actuation element paths 306a, 306b respectively. So long as the bend 520 of the deployment tool remains substantially the same during deployment in the human body as the manufactured shape, this embodiment will operate reliably. If there are variations that may be involved, a secondary actuation element compensation as described herein may be combined with the preformed path length embodiment. In this embodiment, the path length compensation mechanism takes the form of preformed actuation element lengths when the system is manufactured.
Many variations are possible. If the system is in a neutral position, the path lengths extending from the actuation controller to the implant are the same length. No compensation is needed until the deployment tool and its accompanying actuation elements are bent to conform to a body lumen. In one alternative embodiment shown in FIG. 8B, the illustrative actuation elements 308a-c are shown with three different arc lengths. When the curvature of the deployment tool in the human body is known or can be estimated with sufficient accuracy, the actuation elements 308a-c can be prefabricated so the actuation element paths are of the appropriate length between the distal end 400 and the actuation controller 200 as well as any associated mechanical device 600 located distally. The actuators 204a, 204b, 204c can be pre-positioned in a manner to allow for proper engagement of the actuation elements once the deployment tool is properly positioned, or the actuators may be movable so their positions adjust during deployment.
In this manner the actuators 204 are able to automatically adjust to the changes in path length with the actuation elements during the deployment of the deployment tool. The actuation elements in this embodiment may be set into the actuation element pathways in order to prevent any kinking or bunching up of the actuation element length while the deployment tool is stored in a neutral state, or is flexed into a neutral state (such as when the tool is first deployed into the human body).
It is also possible for each actuation element to have a separate actuation element compensation mechanism directly linked to the actuation elements so that a different compensation mechanism can be used for different parts of the deployment system. For example, one actuation element compensation may work well for the release of the actuation elements that interface with the deployment mechanism while a different compensation mechanism will interface well with the actuation elements associated with actuation of the implant. Another actuation element compensation mechanism may be used with the actuation elements used to disengage the operable actuation elements from the implant in order to make the final deployment of the implant. In this embodiment, the various actuation elements have two or more compensation mechanism types. The actuation element compensation mechanisms are identified as generic box components 500a-c shown in FIG. 8C allow for the incorporation of any of the compensation mechanisms described herein to be adapted to the actuation element as provided in the drawing.
In another embodiment (FIG. 8D), a pulley system 508 can be used as the actuation element compensation mechanism 500. In this embodiment the operation of the actuator 204 causes the withdrawing of a first pulley 522a. The first pulley 522a has a first actuation element 308a engaged about its surface. As the actuator is moved, the pulley is drawn back and forth in the actuation controller 200. The proximal end of the actuation element 308a is engaged to a second pulley 522b. When the first pulley 522a is moved via the actuator 204, the first pulley will be drawn up until the tension in the line is equal throughout its length. When the first pulley has used up the slack in the first actuation element, the proximal end of the actuation element begins to operate on a second pulley. The second pulley 522b now moves in response the force requirements of the first actuation element to ensure all the actuation elements are taut before the deployment of the implant begins. A variety of combinations are possible allowing for one actuator to control one or more set of pulleys while having multiple actuators to control multiple actuation elements. The actuators may cooperate to control multiple actuation elements for one distal component of the system, or to control more than one distal component using one or more actuator for each distal component to be controlled.
In still another embodiment, the actuation element compensation mechanism may be a set of springs 508a-n. (FIG. 8E). The springs 518 are used as an interface between the actuators 204 and the actuation elements 308. As the system is deployed through a patient vasculature, the springs extend from a resting position to provide additional path length to the actuation elements that require additional length to handle the bend in the deployment tool. The springs 508 are connected on their distal ends to the actuation elements while the proximal ends are connected to one or more actuators 204. Once the deployment tool 100 is properly placed in a patient\'s vasculature, the actuators can be engaged to operate the various components on the distal end. If the springs have additional slack that needs to be taken up before the individual actuation elements are taut, then the actuators may be moved so as to exhaust the slack in each spring line, or the actuator may possess an additional feature to absorb slack. For instance, the actuator may rotate like a spool to take up slack in the actuation element and spring connection. Alternatively, the spring may have a spring tension low enough to allow it to yield during deployment, but high enough to operate as a continuation of the actuation element itself when the actuator is engaged. In a third embodiment the actuator may engage the spring element and the actuation element. In this manner the actuator can withdraw the spring, or exhaust the slack in the spring before engaging the actuation element. The spring may be attached to a movable piece that the operator may withdraw from the system while manually affixing the actuator to the actuation element for operation.
In another embodiment, the actuators 204 may be positioned between the actuation elements 308 and the springs 518 (FIG. 8A). In this embodiment, the actuators are not constrained during the placement of the deployment tool into a patient\'s vasculature. In this manner the springs 518 may compensate for path length differences by extending in axial length and providing additional length as needed. Once the implant is properly positioned, the actuators are already located on the distal end of the taut actuation elements 508. The actuators 204 may now be engaged without any further operations or manipulations to ensure the actuation elements are taut and the actuation element pathways have been properly compensated for.
In another embodiment, the actuation element compensation mechanism 500 may be a mechanical linkage (FIG. 8F-H). In one embodiment there is a two bar linkage system used in the actuation controller 200. The two bar linkage 516 has at least one proximal interface for being controlled by an actuator. The two bar linkage may have spring resistance or tension incorporated into its pivot joints 517. The pivot joints 517 serve to provide path length compensation for the actuation elements 308a-n as the handle 200 is being used. Each of the bars in the two bar configuration will pivot such that the ends which experience the least force will pivot in a proximal direction. The end experiencing the least force will be that connected to the actuation element providing the least resistance or having the most slack, as associated with a shorter path length. When the resistance of the actuation elements is substantially equal, any further movement of the actuator will cause all the actuation elements to pull equally on the distal end. Once again, actuation elements may be connected to one or more sets of linkages like a additional two bar linkage.