|Publication number||US20060247750 A1|
|Application number||US 11/116,540|
|Publication date||Nov 2, 2006|
|Filing date||Apr 28, 2005|
|Priority date||Apr 28, 2005|
|Also published as||CA2605813A1, EP1901795A1, US8403866, US20090198252, WO2006116595A1|
|Publication number||11116540, 116540, US 2006/0247750 A1, US 2006/247750 A1, US 20060247750 A1, US 20060247750A1, US 2006247750 A1, US 2006247750A1, US-A1-20060247750, US-A1-2006247750, US2006/0247750A1, US2006/247750A1, US20060247750 A1, US20060247750A1, US2006247750 A1, US2006247750A1|
|Inventors||Kevin Seifert, Raymond Yee|
|Original Assignee||Seifert Kevin R, Raymond Yee|
|Export Citation||BiBTeX, EndNote, RefMan|
|Patent Citations (7), Referenced by (24), Classifications (7), Legal Events (1)|
|External Links: USPTO, USPTO Assignment, Espacenet|
The present invention relates to bilumen guide catheters for introduction and implantation of cardiac leads for applying electrical stimulation to and/or sensing electrical activity of the heart or the introduction of other medical instruments and materials into cardiac vessels.
Implantable permanent and temporary medical electrical stimulation and/or sensing leads are well known in the fields of cardiac stimulation and monitoring, including cardiac pacing and cardioversion/defibrillation, and in other fields of electrical stimulation or monitoring of electrical signals or other physiologic parameters. In the field of cardiac stimulation and monitoring, the electrodes of epicardial or endocardial cardiac leads are affixed against the epicardium or endocardium, respectively, or inserted therethrough into the underlying myocardium of the heart wall.
It has become possible to reduce endocardial lead body diameters from 10 to 12 French (3.3 to 4.0 mm) down to 2 French (0.66 mm) presently through a variety of improvements in conductor and insulator materials and manufacturing techniques. The lead bodies of such small diameter, 2 French, endocardial leads are formed without a lumen that accommodates use of a stiffening stylet to assist in implantation.
These small diameter endocardial pacing and cardioversion/defibrillation leads are advantageously sized to be advanced into the coronary sinus to locate the distal electrode(s) adjacent to the left atrium or into coronary veins branching from the coronary sinus to locate the distal electrode(s) adjacent to the left ventricle. The distal end of such a coronary sinus lead is advanced through the superior vena cava, the right atrium, the valve of the coronary sinus, the coronary sinus, and, if employed to pace or sense the left ventricle, into a cardiac vein branching from the coronary sinus.
Typically, such small diameter endocardial leads are formed with an active fixation helix that extends distally and axially in alignment with the lead body to a sharpened distal tip and that has a helix diameter substantially equal to the lead body diameter. The fixation helix does not necessarily increase the overall diameter of the endocardial lead and is relatively robust, once the helix is screwed into the myocardium. Typically, but not necessarily, the fixation helix is electrically connected to a lead conductor and functions as a pace/sense electrode. In some cases, the lead body encloses one or more helical coiled or stranded wire conductor and lacks a lumen.
The lead bodies of such small diameter endocardial screw-in leads can be so supple and flexible that it is difficult to rotate the lead distal end by application of rotary torque to the lead proximal end unless the lead body remains relatively straight and not confined by contact with vessel walls. This diminished “torqueability” prevents the rotation of the fixation helix at the lead distal end or renders the rotation difficult once the lead body is advanced through a tortuous pathway and confined by contact against the vessel walls. In addition, such lead bodies may also possess little if any column strength and lack “pushability”, that is the ability to advance the lead distal end axially when the lead proximal end is pushed axially, particularly when the lead body extends through the tortuous transvenous pathway. Thus, it has been found necessary to use implantation instruments or tools that compensate for the lack of pushability and torqueability of the lead body.
Once the implantation site is reached in coronary vasculature, it is difficult to aim the distal fixation mechanism toward myocardial tissue, and the fixation mechanism may inadvertently be aimed at and deployed away from the myocardium. The pace/sense electrodes may not be sufficiently in contact with excitable cardiac tissue, resulting in unduly high stimulation thresholds and diminished sensing.
Aspects and features of the present invention will be readily appreciated as the present invention becomes better understood by reference to the following detailed description when considered in connection with the accompanying drawings, in which like reference numerals designate like parts throughout the figures thereof and wherein:
In the following detailed description, references are made to illustrative embodiments for carrying out the invention. It is understood that the drawing figures are not necessarily to scale and that other embodiments may be utilized without departing from the scope of the invention. The invention and its preferred embodiments may be employed in implantation of unipolar, bipolar or multi-polar, endocardial, cardiac pacing leads, cardioversion/defibrillation leads or monitoring leads having one or more pace/sense electrode(s) or sense electrode(s), respectively, at or adjacent the distal lead end and an active fixation mechanism that is to be affixed into the myocardium. Moreover, other sensors for sensing a physiologic parameter may be incorporated into the lead body. An insulated electrical conductor extending proximally through the lead body to connector element of a lead proximal end connector assembly is coupled to each such pace/sense electrode, sense electrode, cardioversion/defibrillation electrode and sensor. The proximal connector assembly is adapted to be coupled to the connector assembly of an external medical device, including an external pacemaker or monitor, or an implantable medical device, including an IPG for pacing, cardioversion/defibrillation (or both) or an implantable monitor. Therefore, it will be understood that the arrangement for introduction of a cardiac lead of the present invention can be employed to introduce permanently implantable and temporary cardiac leads of any of these types, particularly within the coronary vasculature.
The multi-lumen guide catheters and methods of the present invention are particularly useful in introducing such small diameter cardiac leads that are devoid of a stylet lumen and are so flexible and possess such low column strength, rigidity, pushability and torqueability that the lead distal end cannot be advanced transvenously and positioned at the desired implantation site without assistance. Moreover, one particular use of the arrangement of the present invention is to introduce such cardiac leads that are formed using stranded wire conductor(s) within a lead body diameter of about 0.010-0.026 inches of the type described in the above-incorporated, commonly assigned, '014 patent. The lead body outer diameter is minimized by use of such conductors and by eliminating the lumen for receiving a stiffening stylet. However, the arrangement of the present invention can also be employed to introduce cardiac leads that employ coiled wire conductors with or without a lumen for receiving a stiffening stylet. In the latter case, the stiffening stylet need not be used to achieve the introduction.
As illustrated in
In patients suffering from heart failure, a CS lead of the types described above is advanced through the pathway “A” extending through the SVC 1 and RA 2 into the CS 4 to dispose one or a pair of distal pace/sense electrodes at an LV site(s) within one of the vessels branching from the CS 4. An RV lead is advanced through the SVC 1, the RA 2, the tricuspid valve, and the distal pace/sense electrode(s) is affixed at an RV pace/sense site(s) of the RV 8, e.g., in the RV apex or along the septum separating the RV and LV chambers. The RV lead can take any of the functions known in the art preferably having an active or passive fixation mechanism.
The proximal connectors of the CS lead and the RV lead are coupled to a connector header of a pacing IPG or an ICD IPG (not shown) implanted subcutaneously. The IPG is capable of sensing and processing cardiac signals detected at the pace/sense site(s) to provide synchronized RV and LV pacing at the pace/sense sites as needed. The pacing and sensing functions of such an IPG that provides synchronous activation of the RV 8 and LV 7 in order to improve the hemodynamic output of the heart 6 are disclosed in commonly assigned U.S. Pat. No. 5,902,324, for example, and are embodied in the MEDTRONIC® InSync Marquis™ ICD IPG, for example.
Hemodynamic output is enhanced when the CS pace/sense electrode(s) site is selected within a late activated region of LV 7. Late activated regions of the LV 7 are found within the myocardium underlying the PLV 11, the LCV 10, the GCV 9, or the CS 4 near a junction with the GCV 9. Moreover, pacing and sensing functions are optimized when the pace/sense electrode(s) are disposed in intimate contact with excitable myocardial tissue.
The lead body of a permanent or temporary cardiac lead typically includes one or more insulated conductive wire surrounded by an insulating outer sheath. Each conductive wire couples a proximal lead connector element with a distal stimulation and/or sensing electrode. Temporary and permanent cardiac leads having a single stimulation and/or sensing electrode at the lead distal end, a single conductor, and a single connector element are referred to as unipolar cardiac leads. Temporary and permanent cardiac leads having two or more stimulation and/or sensing electrodes at the lead distal end, two or more respective conductors, and two or more respective connector elements are referred to as bipolar lead or multi-polar leads, respectively.
A typical example of an active fixation cardiac lead 20 that can be introduced through a bilumen guide catheter of the present invention advanced through pathway “A” and employed as a CS lead is schematically illustrated in
Lead body 21 is constructed of a stranded conductive or non-conductive filament cable 28 disposed within an inner sheath lumen of an inner sheath 29, which in turn extends through the coil lumen of a coil 27. The assembly of the coil 27, inner sheath 29, and cable 28 is fitted through an outer sheath lumen of an outer sheath 26.
Coil 27 is formed of any bio-stable and biocompatible material that is sufficiently stiff to provide adequate torque transfer from proximal connector assembly 22 to fixation element 25 at distal end 24 of cardiac lead 20. When coil 27 functions as a lead conductor, coil 27 is preferably formed of single or multiple wire filars made of MP35-N alloy, well known in the art, or any other bio-stable and biocompatible material that is capable of reliably conducting electrical current after having been subjected to numerous, repeated bending and torsional stresses.
Inner cable 28 is formed from synthetic filaments or conductive metallic wires, when inner cable functions as a lead conductor. The proximal and distal ends of inner cable 28 are coupled to connector pin 23 or within connector assembly 22 and fixation helix 25, respectively, to provide tensile strength to lead body 21.
Outer sheath 26 is formed of either a silicone rubber or polyurethane, well known in the art, or any other flexible, bio-stable and biocompatible, electrically insulating, polymer material. Inner sheath 29 is similarly formed of a bio-stable and biocompatible flexible polymer coating or tube that protects inner cable 28 from mechanical stresses or degradation and electrically insulates inner cable 28 from contact with wire coil 27. Inner sheath 29 can be formed of flexible, bio-stable and biocompatible electrically insulating materials known in the art, including silicone rubber compounds, polyurethanes, and fluoropolymers.
In both unipolar and bipolar cardiac lead embodiments, the proximal connector assembly 22 includes a connector pin 23 that is typically electrically connected with the distal fixation helix 25 when the distal fixation helix 25 functions as a pace/sense electrode. In a bipolar cardiac lead embodiment, the proximal connector assembly 22 includes a connector ring 32 (shown with dashed lines) that is electrically coupled to a ring-shaped pace/sense electrode 30 (shown with dashed lines) supported by outer sheath 26 proximal to fixation helix 25. The connector assembly 22 is shaped to be inserted into a bore of a connector block of the connector header of an IPG as described above to make an electrical connection between the distal pace/sense electrode(s) and IPG sensing and/or pacing pulse generating circuitry. Ring-shaped pace/sense electrode 30 is preferably formed of a platinum alloy but other materials may also be used, including but not limited to such materials as palladium, titanium, tantalum, rhodium, iridium, carbon, vitreous carbon and alloys, oxides and nitrides of such metals or other conductive or even semi-conductive materials. Of course, some materials are incompatible with others and may not be effectively used together. The limitations of specific materials for use with others are well known in the art.
The fixation helix 25 is adapted to be screwed into the myocardium, as described below, by rotation of lead body 21 from the proximal connector assembly 22 when piercing tip 251 is advanced to and oriented toward a fixation site. When fixation helix 25 functions as a pace/sense electrode, as in alternate embodiments described above, fixation helix 25 is preferably formed of a platinum iridium alloy, although it is understood that other biocompatible and bio-stable materials may also be used, including but not limited to such materials as palladium, titanium, tantalum, rhodium, carbon, vitreous carbon and alloys, oxides and nitrides of such metals or other conductive or even semi-conductive materials well known in the art.
In a unipolar embodiment of cardiac lead 20, the inner cable 28 is nonconductive, a proximal end of coil 27 is coupled to connector pin 23, and a distal end of coil 27 is coupled to the proximal end of fixation helix 25. The proximal and distal ends of coil 27 are welded or crimped to the connector pin 23 and fixation helix 25, respectively, using common welding or crimping techniques known in the art. The proximal and distal ends of inner cable 28 are crimped to the connector pin 23 or connector assembly 22 and fixation helix 25, respectively, using common welding or crimping techniques known in the art.
In an alternate unipolar embodiment wherein the inner cable is nonconductive, helix fixation element 25 simply provides fixation and does not function as a pace/sense electrode. The proximal end of coil 27 is coupled to connector pin 23, and the distal end of coil 27 is coupled to the ring-shaped pace/sense electrode 30 incorporated coaxially about a distal portion of lead body 21. The spacing 31 between ring-shaped pace/sense electrode 30 and fixation helix 25 is less than approximately 0.02 inches, in order to locate ring-shaped pace/sense electrode 30 close enough to a fixation site for tissue contact when fixation helix 25 is fixed into the myocardium.
In a further alternate unipolar embodiment of cardiac lead 20, inner cable 28 is electrically conductive, and the proximal and distal cable ends are electrically coupled by crimping or welding or other known techniques to connector pin 23 and helix fixation element 25, respectively. Inner sheath 29 electrically insulates inner cable 28 from coil 27, which acts only as a structural element to provide torsional stiffness to lead body 21. Alternatively, the proximal and distal ends of the conductive inner cable 28 and the wire coil 27 can be electrically connected together to provide a redundant unipolar lead conductors. Conductive inner cable 28 is preferably formed from wire strands or filaments made of MP35-N alloy, well known in the art, or any other bio-stable and biocompatible material that is capable of reliably conducting electrical current after having been subjected to numerous, repeated bending and torsional stresses.
In a bipolar embodiment of cardiac lead 20, both coil 27 and inner cable 28 are lead conductors as described above, that are electrically insulated from one another by inner sheath 29. In this embodiment, the proximal and distal ends of coil 27 are electrically and mechanically coupled by crimping or welding to the connector ring 32 and the ring-shaped pace/sense electrode 30, respectively. The proximal and distal ends of the inner cable 28 are electrically and mechanically coupled by crimping or welding to connector pin 23 and distal fixation helix 25, respectively. The spacing 31 between ring-shaped pace/sense electrode 30 and fixation helix 25 is between approximately 0.2 inches and 0.4 inches, a range well known in the pacing art for inter-electrode bipolar pace/sense electrode spacing.
The exemplary active fixation cardiac lead 20 can also be formed having an elongated cardioversion/defibrillation (C/D) electrode extending proximally a predetermined distance along the outer sheath 21 from a C/D electrode distal end located proximal to distal lead end 24. The proximal and distal ends of the wire coil 27 would be electrically and mechanically coupled to the connector ring 32 and the elongated C/D electrode, respectively. The proximal and distal ends of the inner cable 28 would be electrically and mechanically coupled by crimping or welding to connector pin 23 and distal fixation helix 25, respectively.
A means for steroid elution may be incorporated into any of the aforementioned embodiments of the exemplary active fixation cardiac lead 20 near distal end 24. Such steroid elution means may take the form of a monolithic controlled release device (MCRD), constructed, for example, from silicone rubber and loaded with a derivative of dexamethasone, such as the water-soluble steroid dexamethasone sodium phosphate. MCRD construction and methods of fabrication are found in commonly assigned U.S. Pat. Nos. 4,506,680, 4,577,642, 4,606,118, and 4,711,251. Alternatively a steroid coating containing a no more than sparingly water-soluble steroid such as beclomethasone diproprionate or dexamethasone acetate may be applied to surfaces of ring-shaped pace/sense electrode 30 and/or fixation helix 25. A steroid coating composition and method of application is found in commonly assigned U.S. Pat. No. 5,987,746. The steroid coating may be applied directly to surfaces or portions of surfaces preserving structural integrity of ring-shaped pace/sense electrode 30 and/or fixation helix 25 and taking up less space than an MCRD.
Such an exemplary active fixation cardiac lead 20 can be employed advantageously as a CS lead through the use of the bitumen guide catheters of the present invention advanced through the pathway “A” of
The guide catheters of the present invention enable the implantation of a small diameter lead body 21 in the range of 1 French (0.33 mm) to 3 French (1.00 mm), but it will be understood that the over-the-wire guide catheters can be sized to facilitate implantation of larger diameter lead bodies exceeding 3 French in diameter. It will be understood that the guide catheters and methods of use disclosed herein can be employed to introduce and secure any form of distal fixation hooks or fixation helices either extending distally like distal fixation helix 70 or laterally from the lead body in the manner of those distal fixation helices disclosed in U.S. Pat. Nos. 3,835,864 and 4,233,992, for example. It will be understood that other active fixation cardiac leads having differing shaped fixation mechanisms, e.g., barbs or prongs or pins, can also be advantageously employed with the bilumen guide catheters of the present invention. For example, the guide catheters of the present invention can be employed to locate the fixation mechanism at a fixation site in the coronary vasculature and to aim a fixation mechanism toward the heart before the proximal connector assembly or a further device is activated or manipulated to advance and drive the fixation mechanism through the vessel wall and into the myocardium.
The bitumen guide catheter 100 receives a small diameter cardiac lead, e.g., cardiac lead 20, during the advancement of the catheter body 102 through the tortuous pathway “A” and facilitates fixation of the distal helix 25 at the selected implantation site as shown in
The catheter body 102 therefore encloses a delivery lumen 114 extending between a guide lumen entry port at the catheter body proximal end 112 within the hub 110 and the catheter body distal end 118. The delivery lumen diameter is sized to receive the guidewire 80 inserted therein to aid in steering the guide catheter body 102 through the tortuous pathway “A”. The proximal portion of the catheter body 102 encloses delivery lumen 114 extending between a delivery lumen entry port at catheter body proximal end 112 within hub 110 and a delivery lumen exit port 134 disposed along the catheter body proximal to the catheter body distal end 118.
To some degree, the disposition of the delivery lumen 114 and a guide lumen 116 extending side-by-side through a circular catheter body 108 will cause the catheter body 102 to preferentially bend in a direction that is transverse to a geometric axis plane AP (shown in
The proximal portion 108 is extruded into the shape depicted in
The catheter body 102 is reduced in cross-section area diameter in the distal leader 120 extending between the delivery lumen exit port 134 and the guide lumen exit port 136. The distal leader 120 can be tubular in cross-section and tapered distally to facilitate advancement over the guidewire 80 extending through the guide lumen 116. Consequently, the small diameter leader 120 can be advanced readily over guidewire 80 through twists and turns of the tortuous pathway and thereby guides the advance of the larger cross-section proximal segment 108 of the catheter body 102. The small diameter leader 120 can also be advanced deeply into narrow pathways or passages to dispose the more proximal delivery lumen exit port 134 at a desired implantation site. The flattened surface 104 encourages bending of the proximal portion 108 to track the contours of the heart and dispose the delivery lumen exit port 134 aimed toward the heart. The leader 120 can be straight or have one or more preformed bend along the length thereof.
Then, as shown in
The hub 110 (
The hemostasis valve 140 includes a proximal rotating closure knob 142, an intermediate side port (extension hose and stopcock not shown) 144 and a distal rotating locking collar (for securing valve to luer hub fitting) 146 that is press fit onto the hub 110. The knob 142 and side port 144 and collar 146 are used in the fashion of a standard hemostasis valve manufactured by numerous suppliers to shut off the flow and to lock the lead or other catheter in relation to the catheter body. The valve 140 provides a lead insertion lumen axially aligned with the hub delivery lumen 148 so that a cardiac lead 20 of the types described above can be inserted therethrough and into the catheter body delivery lumen 114.
The hub guide tube 122 extends in an arcuate path through window 150 and the side extension 132 that can also be coupled with a Luer type hemostasis valve to seal around the guidewire 80 in a manner well known in the art. The hub 110 and the catheter body 102, particularly the proximal portion 108, are formed to be slittable along the lengths thereof to exposed the aligned hub and catheter body delivery lumens and release the lead body of the cardiac lead 20 in a manner described in the above-referenced '346 and '433 patents. An enlarged, relatively flat pad or paddle 130 is formed extending away from the hemostasis valve 140 and the hub guide tube 122 that can be gripped on either side by the fingers to assist in holding and manipulating the hub 110 during adjustment of the hemostasis valve 140 and advancement of the catheter body assembly of the cardiac lead 20 and catheter body 102 through the tortuous pathway over the guidewire 80.
The guidewire 80 may have an outer diameter in the range of 0.014 to 0.016 inches. The guidewire 80 can be a guidewire that is either introduced by itself or is introduced through a separate, small diameter introducer, e.g., a COOK® RoadRunner® Extra Support guidewire having an outer diameter of 0.018 inches (0.49 mm). The guidewire 80 can also be a deflectable or steerable guidewire of the type disclosed in commonly assigned U.S. Pat. No. 4,815,478, for example.
The bilumen guide catheter 100 depicted in
A typical stylet includes a stainless steel wire extending between a proximal stylet wire handle and stylet wire distal end. The stylet wire is adapted to be advanced through the hub guide lumen 125 and the catheter guide lumen 116 from outside the patient's body to abut the stylet distal end against the blockage 138 at the catheter body distal end 118. The stylet wire may have a stylet diameter of about 0.012 to 0.016 inches. The stylet may be a steerable stylet, e.g., the MEDTRONIC® Model 9210 steerable stylet or a steerable stylet of the types disclosed in commonly assigned U.S. Pat. Nos. 5,873,842 and 6,146,338.
Certain embodiments of the bitumen catheter body 102 can advantageously be formed by extrusion of a single polymeric material without the necessity of reinforcement or changing material characteristics along its length. The bitumen catheter body 102 can be extruded from medical grade thermoplastic resins of 35D Shore durometer, for example, to form the delivery tube 104 joined to a guide tube 106 at the elongated junction 108. A radiopaque marker band can be incorporated at the catheter body distal end 118 at the distal tip of the distal leader 120.
The proximal portion 108 can be extruded from medical grade thermoplastic resins of 70D-75D Shore durometer, for example, and the distal leader 120 can be extruded from medical grade thermoplastic resins of 75A-35D Shore durometer, for example. The durometer of the proximal portion 108 is therefore lower than the durometer of the distal leader 120. The higher durometer of the distal leader 120 enables it to be formed having a thin sidewall so that the distal leader 120 can be made smaller in diameter while providing a suitable guide lumen diameter to track a guidewire or receive a stylet or to be directed into smaller diameter blood vessels or other body tracts. The harder surface of the higher durometer material tends to have lower contact stress and, thus, presents lower friction to the guidewire. Moreover, the higher durometer distal leader 120 can be shaped to have a pre-formed bend or curvature that is assumed upon retraction of the guidewire and assists in urging the delivery lumen exit port 134 toward the heart. The medical grade thermoplastics can be selected from polyether block amide (PEBA), polyamide (PA), polyurethane (PU), polyester (PET), polybutylene terephthalate (PBT), or polyvinyl chloride (PVC). Optimally, the proximal portion 120 can be extruded from one of the group consisting of PEBA, PU, PET or PVC having a relatively low durometer, whereas the smaller diameter distal leader 120 can be extruded from the group consisting of PEBA, PU, PA, PET, PBT or PVC having a relatively higher durometer.
In addition to the radiopaque marker band, an atraumatic soft tip can be applied at the catheter body distal end 118. The soft tip can be formed of a polyurethane, e.g., TECOFLEX® TT-1074A polyurethane sold by Thermedics Polymer Products, Inc., Woburn, Mass. The polyurethane material can be loaded with a radiopaque material, e.g. barium sulfate or tungsten powder, to make the resulting molded soft tip radiopaque.
The surfaces of delivery lumen 114 and guide lumen 116 may be coated with a lubricant to facilitate advancement of a cardiac lead 20 or other instrument through the delivery lumen 114 and the guidewire 80 or stylet wire or other instrument through the guide lumen 116. The exterior surface of a distal portion of the catheter body 102 including the distal leader 120 can also be coated with the lubricant to facilitate advancement of the distal leader 120 through the tortuous pathway. Suitable biocompatible lubricating coatings include a silicone-based lubricant, e.g., a silicone oil, or a reactive silicone lubricant, e.g., MDX4-4159 silicone lubricant available from Dow Chemical Co., Midland, Mich. Other suitable biocompatible lubricating coatings include hydrophilic slip coating materials, e.g., polyacrylamide, polyvinylpyrrolidone, hyaluronic acid, or polyethylene oxide.
As shown in
The delivery lumen 214 and the guide lumen 216 can constitute co-extruded tubes of the materials described above. The connection between the co-extruded tubes can be severed along the length of the distal segment of the delivery lumen 214. The distal ends of the co-extruded tubes can be cut to length to form the distal leader 220 and to dispose a short segment of the tube surrounding the delivery lumen 214 over a proximal segment of the tube surrounding the guide lumen 216. Or, a distal segment of the proximal portion 208 and the distal leader 220 can be molded as a separate assembly that is adhered to a distal end of the substantially rectangular cross-section extrusion to form the catheter body 202.
A jacket 240 of flat metal or plastic filaments may be braided over the outer surface of the proximal portion 208 of the catheter body 202 that further assists in causing the catheter body to preferentially bend to bias the delivery lumen exit port 234 toward the heart. A thin coating of elastomeric material can be fitted over the jacket 240 to make its exterior surface smooth.
A jacket 440 of flat metal or plastic filaments may be braided over the outer surface of the tube 438 in proximal portion 208 of the catheter body 202 that further assists in causing the catheter body 202 to preferentially bend to bias the delivery lumen exit port 234 toward the heart. In this embodiment, the generally cylindrical outer sheath 442 is formed over the jacket 440 to make the proximal portion 408 of catheter body 402 generally cylindrical.
A short distal segment of the delivery lumen 414 is shifted out of side-by-side alignment with a corresponding segment of the guide lumen 416 to dispose the delivery lumen exit port 434 above or alongside the flat side 404 in the manner described above with respect to the embodiment of
In this way, the shape of the jacket 440 tends to cause the catheter body 402 to advance through the coronary vasculature over the guide tool, e.g., the guidewire 80, within the guide lumen 416 with the delivery lumen exit port 434 disposed or biased toward the heart. A curve 421 is preferably pre-formed in the distal segment 420 extending away from the flat side 405 that tends to offset the shift of the delivery lumen exit port 434 into alignment with the flat side 404 and to dispose the delivery lumen exit port 434 toward the heart, particularly the myocardium of the LV 7 as also shown in
According to an embodiment of the present invention, the leader 520 has a length extending from the proximal end 511 to the distal end 518 and the proximal portion 508 has a length extending from the hemostasis valve 140 and hub 110 to the distal end 509 that is dependent upon the selected pathway through the patient to the implantation site.
The proximal portion 508 of the guide catheter 500 includes an outer wall 504 that forms a lumen 506 that extends within the proximal portion 508 of the catheter body 502 from the proximal end 112 of the catheter body 502 to the distal end 509 of proximal portion 508, forming an opening 522 at the distal end 509. Similarly, the leader 520 includes an outer wall 522 that forms a lumen 528 in the catheter body 502 that extends from the proximal end 511 of the leader 520 to the distal end 518, and forms an opening 530 at the distal end 518 of the catheter body 502. The outer wall 504 of the proximal portion 508 includes a tapered portion 530 that extends from a tapered portion proximal end 532 to the distal end 509 of the proximal portion 508 of the catheter body 502 so that the opening 522 at the distal end 509 of the proximal portion 508 is axially aligned at the junction 524 with and in fluid communication with the lumen 528 and the opening 522 has a diameter approximately equal to the diameter of the lumen 528 extending within the leader 520.
An inner wall 540 is positioned within the lumen 506 of the proximal portion 508 of the catheter body 502 spaced from an inner surface of the outer wall 504 to form an inner lumen 542 that extends from the proximal end 112 of the catheter body 502 to a distal end 544 of the inner wall 540 and forms an opening 546 at or proximal to the tapered portion 530 of the outer wall 504. Similarly, the inner wall 540 is spaced from an opposing inner surface of the outer wall 504 to form a second inner lumen 548 that extends from the proximal end 112 of the catheter body 502 to the distal end 544 of the inner wall 540 and forms a second opening 550 at or proximal to the tapered portion 530 of the outer wall 504.
According to an embodiment of the present invention, a stylet or guide wire 552 is advanced though inner lumen 542 to extend outward from opening 546 along the inner surface of the outer wall 504 at the tapered portion 530 and outward from the distal end 518 of the catheter 500 during navigation of the catheter 500 to a desired site in the patient. Once the catheter 500 has been positioned at the desire site, the guidewire 552 is retracted by being advanced inward within the catheter body until a distal tip is proximal to the tapered portion 530 within the lumen 506. A lead 554 is then advanced through the second inner lumen 548 to extend outward from the second opening 550 along the inner surface of the outer wall 504 at the tapered portion 530 and outward from the distal end 518 of the catheter 500 to the desired site in the patient. The catheter 500 and guidewire 552 are then removed from the patient, leaving the lead in place at the desired site.
According to the present invention, a tube member could be utilized to form the second lumen 648 that is utilized for receiving the cardiac lead, rather than the inner lumen 642 that is utilized for receiving the guide tool shown in
The two lumens of the present invention provide the ability to more easily switch between advancing the guide tool outward from the distal end of the catheter and advancing the lead outward from the distal end of the lead, reducing the likelihood that the catheter position will be corrupted when the guide tool is retracted or the lead is advanced. In addition, the tapered portion of the catheter serves to improve access to cardiac veins. It is understood that while the present invention is described above in terms of placing the lead within the coronary veins, the present invention is not intended to be limited to left heart lead placement but rather may also be utilized for placing leads to other locations in the patient, including, for example, the right ventricle or the right atrium of the heart.
These embodiments of bilumen and multi-lumen guide catheters 100 can be employed in a variety of procedures for introducing cardiac leads into coronary veins of the heart, e.g., deep in the cardiac veins descending from the coronary sinus accessed transvenously and through the coronary sinus as illustrated in
Further instruments or diagnostic fluids can be selectively advanced through the delivery lumen and/or the guide lumen to facilitate identification or advancement of the catheter body distal end to the implantation site preceding the advancement of the cardiac lead through the delivery lumen.
The guide catheter having an open guide lumen exit port can advantageously be used to perform other functions, e.g., to facilitate blocking of a cardiac vessel employing a balloon catheter so that radiopaque diagnostic fluid can be introduced into the cardiac vessel to visualize the cardiac vessel in an angiographic procedure in order to identify a suitable implantation site.
All patents and publications identified herein are incorporated herein by reference in their entireties.
While particular embodiments of the invention have been disclosed herein in detail, this has been done for the purposes of illustration only, and is not intended to limit the scope of the invention as defined in the claims that follow. It is to be understood that various substitutions, alterations, or modifications can be made to the disclosed embodiments without departing from the spirit and scope of the claims. The above described implementations are simply those presently preferred or contemplated by the inventor, and are not to be taken as limiting the present invention to the disclosed embodiments. It is therefore to be understood, that within the scope of the appended claims, the invention may be practiced otherwise than as specifically described without actually departing from the spirit and scope of the present invention.
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|Cooperative Classification||A61M2025/0037, A61N2001/0585, A61N2001/0578, A61N1/056|
|Apr 17, 2006||AS||Assignment|
Owner name: MEDTRONIC, INC., MINNESOTA
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:SEIFERT, MR. KEVIN R.;YEE, DR. RAYMOND;REEL/FRAME:017478/0521;SIGNING DATES FROM 20050719 TO 20050912