Patent Application
20230397988
The present invention is related to systems and methods for transcatheter valve delivery and deployment. In particular, the present invention is related to balloon catheter devices configured for prosthetic heart valve retention during delivery of prosthetic heart valves.
Transcatheter valve technology provides a minimally invasive means of implanting prosthetic heart valves. The prosthetic heart valve is loaded onto a delivery system that is able to access and navigate the vasculature to the intended implant location and implant the prosthetic heart valve. A conventional approach for a transcatheter valve system is to use a balloon catheter for the delivery system and a prosthetic heart valve incorporating a balloon expandable frame. After reaching the delivery site, the balloon is inflated to expand the prosthetic heart valve into a deployed configuration. After deployment, the balloon is deflated and the balloon catheter is removed.
In conventional balloon catheters, transcatheter balloon expandable prosthetic heart valves are crimped onto the balloon of the balloon catheter. The balloon of the balloon catheter is processed such that the balloon is pleated then folded prior to crimping the prosthetic heart valve onto the balloon. The prosthetic heart valve is delivered to the treatment site and then deployed by inflating the balloon which thereby radially expands the prosthetic heart valve. During delivery procedures, such as gaining vessel access, tracking the balloon catheter through the patient anatomy, crossing the native valve, and advancing the balloon catheter past a distal end of an introducer catheter, forces on the prosthetic heart valve may lead to migration of the prosthetic heart valve on the balloon catheter. Movement of the prosthetic heart valve may lead to an inaccurate deployment position, a prosthetic heart valve that does not fully deploy, and other complications.
Challenges impacting valve retention include the minimum crimp diameter of the prosthetic heart valve, varying contact material and shape between the crimped prosthetic heart valve and the folded balloon, and high forces exerted on the crimped prosthetic heart valve during delivery and deployment procedures. The minimum crimp diameter of the prosthetic heart valve is typically larger than the minimum diameter of the folded balloon. This size mismatch limits contact between the balloon and the prosthetic heart valve and therefore reduces friction forces between the prosthetic heart valve and the balloon. Likewise, the size mismatch limits opportunities for a mechanical lock between the prosthetic heart valve and the balloon (i.e., the prosthetic valve imprinting into the balloon during crimp). Along the length of the crimped prosthetic heart valve, the contact material can change between the metal scaffold and tissue and the balloon giving different friction coefficients and amount of compliance. Further, in the balloon catheter, the crimped prosthetic heart valve typically is the component having the largest diameter. This leads to the prosthetic heart valve being subject to the largest forces during delivery through an introducer.
Devices and methods disclosed herein address the issue of prosthetic heart valve migration during delivery.
Embodiments hereof relate generally to delivery devices for prosthetic heart valves, and, more specifically, to balloon catheters for prosthetic heart valve delivery and deployment. Balloon catheters consistent with embodiments hereof are configured to reduce or prevent valve migration during delivery and deployment procedures.
Embodiments hereof include a balloon catheter for deploying a prosthetic heart valve through balloon inflation. The balloon catheter includes an inner shaft defining a guidewire lumen; an outer shaft surrounding the inner shaft defining an inflation lumen between the outer shaft and the inner shaft; a distal portion at a distal end of the outer shaft; a balloon disposed at the distal portion such that fluid delivered to the balloon via the inflation lumen causes the balloon to inflate; a proximal multipart retention bumper having a star shape, the proximal multipart retention bumper being secured to the inner shaft inside the balloon and configurable in an interlocked configuration and a non-interlocked configuration, the proximal multipart retention bumper including a proximal inner wedge and a proximal outer bumper; and a distal multipart star shaped retention bumper having a star shape, the distal multipart retention bumper being secured to the inner shaft inside the balloon and configurable in an interlocked configuration and a non-interlocked configuration, the distal multipart retention bumper including a distal inner wedge and a distal outer bumper.
In further embodiments, a method of assembling a balloon catheter adapted for deploying a prosthetic heart valve through balloon inflation is provided. The method includes disposing a proximal outer bumper and a distal outer bumper over an inner shaft of the balloon catheter at a distal portion of the inner shaft wherein the proximal outer bumper and the distal outer bumper are star shaped; securing a proximal inner wedge and a distal inner wedge to an inner shaft of the balloon catheter at a distal portion of the inner shaft wherein the proximal inner wedge and the distal inner wedge are star shaped; positioning the balloon over the proximal outer bumper, the distal outer bumper, the proximal inner wedge, and the distal inner wedge by passing the proximal outer bumper, the distal outer bumper, the proximal inner wedge, and the distal inner wedge into the balloon via a distal opening of the balloon; interlocking the distal inner wedge and the distal outer bumper to form a distal multipart retention bumper; and interlocking the proximal inner wedge and the proximal outer bumper to form a proximal multipart retention bumper.
The accompanying figures, which are incorporated herein, form part of the specification and illustrate embodiments of a prosthesis delivery system. Together with the description, the figures further explain the principles of and enable a person skilled in the relevant art(s) to make and use the balloon catheters described herein. The drawings are provided to illustrate various features of the embodiments described herein and are not necessarily drawn to scale. In the drawings, like reference numbers indicate identical or functionally similar elements.
Specific embodiments of the present invention are now described with reference to the figures. Unless otherwise indicated, for the balloon catheters discussed herein, the terms “distal” and “proximal” are used in the following description with respect to a position or direction relative to the treating clinician or operator. “Distal” and “distally” are positions distant from or in a direction away from the clinician, and “proximal” and “proximally” are positions near or in a direction toward the clinician. As used herein, the term “proximal force” refers to a force in the proximal direction and the term “distal force” refers to a force in the distal direction.
The following detailed description is merely illustrative in nature and is not intended to limit the invention or the application and uses of the invention. Although the description of the invention is in the context of balloon catheter enabled delivery and deployment of prosthetic heart valves, aspects of the invention may also be used in any other context that is useful. As an example, the description of the invention is in the context of delivery and deployment of heart valve prostheses. As used herein, “prosthesis” or “prostheses” may include any prosthesis including a balloon expandable structure. Modifications can be made to the embodiments described herein without departing from the spirit and scope of the present invention. Therefore, the following detailed description is not meant to be limiting. Furthermore, there is no intention to be bound by any expressed or implied theory presented in the preceding technical field, background summary or the following detailed description.
The outer shaft 140 extends into the interior of the balloon 110 and terminates therein at an open distal end, while the inner shaft 130, defining the guidewire lumen 165, extends to the distal tip 160 and terminates therein. This arrangement permits the balloon inflation lumen 170 to carry fluid pumped from the handle of the balloon catheter 100 into the interior of the balloon 110. The release of fluid to the interior of the balloon 110 causes the balloon 110 to inflate, an action that is employed to expand a prosthetic heart valve frame and deploy the prosthetic heart valve 120.
The prosthetic heart valve 120 has a minimum size in a collapsed state beyond which it cannot be collapsed or compressed any further. The frame of the prosthetic heart valve 120 permits only a certain amount of compression. In a balloon catheter 100, this minimum size may not be small enough to create a large amount of contact between the balloon 110 and the prosthetic heart valve 120. In other embodiments, the frame of the prosthetic heart valve 120 may be configured for tighter crimping. Tighter crimping, however, may cause the crimped balloon 110 to interfere with fluid flowing into the balloon for inflation, leading to irregularities in deployment. These limitations on compression of the prosthetic heart valve 120 may thus prevent the prosthetic heart valve 120 from being crimped tightly onto the balloon 110. A looser crimping of the prosthetic heart valve 120 can result in a less secure fitting and a potential for migration of the prosthetic heart valve 120 when subject to proximal or distal forces during delivery.
Balloon catheters consistent with embodiments hereof are configured to deliver and deploy, through the use of an inflatable balloon, transcatheter balloon expandable prosthetic heart valves (referred to herein as “prosthetic heart valves”). Balloon catheters consistent with embodiments hereof include one or more valve retention devices configured to prevent or reduce valve migration during delivery and deployment. Balloon catheters including valve retention devices and methods of their use consistent with embodiments hereof are described below with respect to
The retention bumpers 401, 402 function to maintain an axial position of the prosthetic heart valve 120. The retention bumpers 401, 402 are positioned adjacent to the prosthetic heart valve 120 so as to maintain an axial position, i.e., prevent or reduce axial migration, through contact. In particular, as shown in
The retention bumpers 401, 402 may also function to reduce forces acting on the prosthetic heart valve 120. The retention bumpers may be sized such that they (or the balloon 410 covering them) extend further radially outward than the prosthetic heart valve 120. Thus, the features of the balloon catheter 400 having the largest diameter are the retention bumpers 401, 402 and not the prosthetic heart valve 120. When inserted into an introducer, the retention bumpers 401, 402 therefore are the portion of the balloon catheter 400 that contacts the introducer wall, thereby preventing the wall of the introducer from contacting the prosthetic heart valve 120 and thereby reducing the amount of force acting on the prosthetic heart valve 120 from the inner walls of the introducer.
The balloon opening 449 and all balloon openings referred to herein are not required to be circular. Balloon openings and/or balloon necks discussed herein may be circular, elliptical, and/or any other suitable shape. In embodiments, catheter balloons may be flexible and thus may adopt any shape which they may be formed into.
In embodiments, as described below with respect to
Retention bumpers described herein may be illustrated or described with respect to a specific profile. Unless otherwise stated, a retention bumper profile refers to the profile when viewed perpendicularly to a central axis. For example,
In embodiments, any or all of the retention bumpers described herein may include radiopaque markers to assist during prosthetic heart valve delivery. In embodiments, any or all of the retention bumpers described herein may be manufactured and assembled by any suitable manufacturing process or technique.
As used herein, the terms “radially unexpanded” and “radially expanded” refer to the expansion of the outer bumpers described herein when combined with the inner wedges described herein. In the radially expanded state, an outer bumper has an increased effective diameter relative to the radially unexpanded state, where “effective diameter” refers to the diameter required for a circle to circumscribe the outer bumper. The radially unexpanded state of the outer bumper is the initial or resting state of the outer bumper when there are no external forces placed on it. The radially unexpanded state of the outer bumper may also refer to the as-manufactured state or as-molded state.
In embodiments, each of the inner wedges 512 and outer bumpers 511 are configured with maximum diameters between approximately 0.1 inches and 0.25 inches, between 0.15 and 0.22 inches, between 0.19 and 0.21 inches, or approximately 0.2 inches. Such sizes may be suitable for entry into the opening of a balloon of a balloon catheter, as discussed in greater detail below with respect to
The outer bumper 511 is formed from any suitable flexible material, including elastic materials, such as polymers, elastomers, thermoplastic elastomers, PTFE, PS, PET, etc. and is configured to expand. In embodiments, the outer bumper 511 may be formed from a thermoplastic elastomer (TPE) such as Pebax® 55. The outer bumper 511 includes a spoked perimeter 530 surrounding a hollow core 520. The spoked perimeter 530 includes a plurality of spokes 531 that project outward from an inner perimeter 532. The spoked perimeter 530 surrounds the hollow core 520, which is an empty interior space including a central core 521 and core extensions 551. The core extensions 551 extend radially from the central core 521 towards each of the spokes 531. The hollow core 520 comprising the central core 521 and the core extensions 551 is generally star shaped. The walls of the spoked perimeter are substantially parallel to each other and are configured to mate with the cylindrical features of the seating hub 552, as discussed further below.
The inner wedge 512 includes a central hub 522 surrounding an interior cavity 523. As shown, e.g., in
The ridged tapered body 541 includes a tapered base 545, extension arms 542, an apex 543 at the end of the outer bumper 511, and a base 544 at the intersection between the ridged tapered body 541 and the seating hub 552. The star shape of the ridged tapered body 541 is defined by the tapered base 545 and the extension arms 542. The diameter of the apex 543 is smaller than the diameter of the base 544. Extension arms 542 extend radially from the tapered base 545. The extension arms 542 have a taper, such that they extend further from the tapered base 545 at the base 544 than at the apex 543. Accordingly, the extension arms 542 define a largest effective diameter of the inner wedge 512 at the base 544 of the ridged tapered body 541. The interior cavity 523 runs axially through the ridged tapered body 541. The spaces between the extension arms 542 are flow recesses 533. The flow recesses 533 extend from the tapered base 545 to a diameter defined by the extension arms 542.
The inner wedge 512 further includes a seating hub 552 adjacent to the base 544 of the ridged tapered body 541. The seating hub 552 is a hollow cylinder, with the hollow occupied by the interior cavity 523. The outer diameter of the seating hub 552 is greater than the diameter of the interior cavity 523 and less than the diameter of the base 544 of the ridged tapered body 541. Thus, the base 544 of the ridged tapered body 541 forms a flange or stop at one side of the seating hub 552.
The inner wedge 512 further includes the tapered end 562. The tapered end 562 is a tapered shape with a base 563 adjacent the seating hub 552 and an apex 564 at the end of the inner wedge 512. The base 563 of the tapered end 562 has an outer diameter greater than the outer diameter of the seating hub 552. Thus, the base 563 of the tapered end 562 forms a flange or stop at a side of the seating hub 552 opposite the ridged tapered body 541.
The inner wedge 512 is formed from a suitable rigid material, including suitable plastics or polymers, including high density polyethylene (HDPE), TPE, Pebax® and any other suitable rigid material. In embodiments, the material of the inner wedge 512 is selected so as to be substantially non-compressible during conditions expected to accompany manufacture, assembly, or use. As used herein, substantially non-compressible during conditions expected to accompany manufacture, assembly, or use means that the inner wedges 512 show less than 5%, less than 3%, and/or less than 1% strain when subject to forces or stresses common during manufacture, assembly, and/or use. For example, a suitable durometer may be in excess of 60D, in excess of 65D, in excess of 70D, or in excess of 75D.
When disposed over the seating hub 552, the spokes 531 of the outer bumper 511 have an increased effective diameter due to stretching caused by the diameter of the seating hub 552. The outer bumper 511 may be disposed on the seating hub 552 via stretching over either the tapered end 562 or over the ridged tapered body 541. Once seated, the spokes 531 of the outer bumper 511 are arranged in radial alignment with the extension arms 542 of the inner wedge 512. This arrangement allows inflation fluid to flow between the extension arms 542 (in the flow recesses 533) and between the spokes 531, without significant obstruction. Further, the extension arms 542 of the inner wedge 512 provide lateral support for the spokes 531 of the outer bumper 511. These features are discussed in greater detail below with respect to
Prior to stretching over the inner wedge 512, the outer bumper 511 has an effective diameter at the first radially unexpanded size smaller than the balloon opening. After stretching, the outer bumper 511 has an effective diameter at the second radially expanded size great enough to retain a prosthetic heart valve. Seating the outer bumper 511 on the seating hub 552 of the inner wedge 512 causes the effective diameter of the outer bumper 511 to expand from the first radially unexpanded size to the second radially expanded size.
In variations of the assembly process, various steps may take place in a different order according to different requirements. For example, in embodiments, the proximal outer bumper 511B may be loaded to the partial assembly 631 prior to insertion into the balloon 610. In another example, the outer bumpers 511 may be interlocked with the inner wedges 512 prior to bonding the balloon 610 to the distal tip 660. This may permit access to the multipart retention bumpers 501 from either end of the balloon 610. Other suitable variations may be employed without departing from the scope of this disclosure.
After completion of assembly, the balloon catheter 600 may be employed to deliver the prosthetic heart valve 120 to a treatment location. The prosthetic heart valve 120 is delivered by the balloon catheter 600 to a site of deployment. During the delivery process, the balloon catheter 600 may be guided by a guidewire passing through the guidewire lumen 665. During delivery of the prosthetic heart valve 120, the multipart retention bumpers 501 serve to maintain the axial position of the prosthetic heart valve 120 and reduce or prevent axial migration of the prosthetic heart valve 120. The multipart retention bumpers 501 combine with the wrapped balloon 610 create a stop 691 at either end of the prosthetic heart valve 120. The stop 691 applies axial force or pressure to the prosthetic heart valve 120 to maintain the position of the prosthetic heart valve 120 when it is subject to axial forces during delivery, for example, by contact with an introducer sheath. When axial force is applied to the stop 691 (and therefore to the outer bumpers 511A/511B), the extension arms 542 of the inner wedges 512 press against the spokes 531 of the outer bumpers 511A/511B and the base 544 of the ridged tapered body 541 presses against the inner perimeter 532 to maintain the axial position of the outer bumpers 511A/511B. Further, the base 563 of the tapered end 562 presses against the inner perimeter 532 of the outer bumpers 511A/511B to maintain the axial position of the outer bumper 511A/511B, in the event that the stop 691 is subject to axial force.
Once delivered, the prosthetic heart valve 120 is deployed through operation of the balloon catheter 600. Inflation fluid, e.g., saline, contrast fluid, etc., is delivered to the balloon 610 via the inflation lumen 675 disposed between the inner shaft 630 and the outer shaft 640. The inflation fluid travels through the flow recesses 533 of the proximal inner wedges 512B, and between the extension arms 542 of the proximal inner wedges 512B and spokes 531 of the proximal outer bumpers 511B. Thus, the star shape of the retention bumpers 501 provides fluid pathways to facilitate inflation of the balloon 610. The path of the inflation fluid is shown by arrows 699 in
Due to the lack of obstruction in the fluid flow pathways, inflation fluid is permitted to flow past the multipart retention bumpers 501 along substantially longitudinal streamlines. Thus, the multipart retention bumpers 501 reduce, minimize, eliminate, or otherwise limit radial flow of inflation fluid. As used herein, substantially longitudinal streamlines refer to fluid flows having streamlines approximately parallel to a designated axis. For example, a substantially longitudinal flow in a balloon catheter may have streamlines approximately parallel to a central axis of the balloon catheter. Approximately parallel may include streamlines within 10 degrees, within 5 degrees, and/or within 1 degree of parallel. Longitudinal flows represent fluid flows along the length of the balloon catheter. Radial flows refer to fluid flows having streamlines that deviate from parallelism with a designated axis, having a significant orthogonal vector component. A streamline with a significant orthogonal vector component may deviate from parallel by 10 degrees or more. Radial flows represent flows towards or away from the axial center of the balloon catheter.
The multipart retention bumper 701 includes the inner wedge 712 and the outer bumper 711. The inner wedge 712 and outer bumper 711 are configured such that, when interlocked, the maximum diameter of the outer bumper 711 (and thus the maximum diameter of the multipart retention bumpers 701) expands from a first radially unexpanded size to a second radially expanded size, wherein the first radially unexpanded size is selected to fit within the neck of a balloon during assembly of a balloon catheter and the second radially expanded size is selected to permit the interlocked multipart retention bumper 701 to maintain the axial position of a prosthetic heart valve crimped to the balloon, as discussed in greater detail below.
In profile, the outer bumper 711 is tapered from an apex surface 771 to a base surface 772. The outer bumper 711 includes a spoked perimeter 730 surrounding a hollow core 720. The spoked perimeter 730 includes a plurality of spokes 731 that project outward from an inner perimeter 732. The spoked perimeter 730 surrounds the hollow core 720, which is an empty interior space including a central core 721 and core extensions 751.
The spoked perimeter includes an outer wall 753 and an inner wall 754. The outer wall 753 is tapered and defines a profile that is narrower in effective diameter at the apex surface 771 of the outer bumper 711 and wider in effective diameter at the base surface 772 of the outer bumper, where the apex surface 771 is opposite the base surface 772. The tapered profile of the outer wall 753 is best seen in
The inner wedge 712 includes a central hub 722 surrounding an interior cavity 723.
The ridged tapered body 741 includes a tapered base 745, extension arms 742, an apex 743 at the end of the inner wedge 712, and a base 744 at the intersection between the ridged tapered body 741 and the seating hub 752. The star shape of the ridged tapered body 741 is defined by the tapered base 745 and the extension arms 742. The diameter of the apex 743 is smaller than the diameter of the base 744. Extension arms 742 extend radially from the tapered base 745. The extension arms 742 have a taper, such that they extend further from the tapered base 745 at the base 744 than at the apex 743. Accordingly, the extension arms 742 define a largest effective diameter of the inner wedge 712 at the base 744 of the ridged tapered body 741. The empty spaces between the extension arms 742 are flow recesses 733. The flow recesses 733 extend from the tapered base 745 to a diameter defined by extension arms 742.
The inner wedge 712 further includes a seating hub 752 adjacent to the base 744 of the ridged tapered body 741. The seating hub 752 is hollow, with the hollow occupied by the interior cavity 723. The seating hub 752 is a tapered base with a wider base end 755 at the intersection with the ridged tapered body 741 and a narrower apex end 756 at the intersection with the tapered end 762. At the base end 755, the seating hub 752 is greater than the diameter of the interior cavity 723 and less than the diameter of the base 744 of the ridged tapered body 741. At the apex end 756, the seating hub 752 is greater than the diameter of the interior cavity 723 and less than the diameter of the base 763 of the tapered end 762. Thus, the base 744 of the ridged tapered body 741 forms a flange or stop at one side of the seating hub 752 and the base 763 of the tapered end 762 forms a flange or stop at the other side of the seating hub 752. Further, the seating hub 752 includes stabilization fins 757. The stabilization fins 757 extend radially from the seating hub 752 with a taper having a narrow end at the apex end 756 of the seating hub 752 and a wider end at the base end 755 of the seating hub 752. Thus, the stabilization fins 757 are tapered in the same direction as the taper of the seating hub 752, extending to a larger effective diameter at the base end 755 of the seating hub 752. In embodiments, the radial arrangement of the stabilization fins 757 may correspond with the radial arrangement of the extension arms 742. For example, the number of stabilization fins 757 may be the same as the number of the extension arms 742, and the stabilization fins 757 and the extension arms 742 may be radially aligned.
The taper of the seating hub 752 and the taper of the stabilization fins 757 is selected to correspond to the taper of the inner wall 754 of the outer bumper 711 when the outer bumper 711 is elastically stretched or deformed to interlock with the inner wedge 712. When the outer bumper 711 is interlocked with the inner wedge 712, as shown in
The inner wedge 712 further includes a tapered end 762. The tapered end 762 is a tapered shape with a base 763 adjacent the seating hub 752 and an apex 764 at the end of the inner wedge 712. The base 763 of the tapered end 762 has a diameter greater than the diameter of the seating hub 752. Thus, the base 763 of the tapered end 762 forms a flange or stop at a side of the seating hub 752 opposite the ridged tapered body 741. The tapered profile of the tapered end 762, in combination with the taper of the inner wall 754 of the outer bumper 711, serves to facilitate the interlock of the outer bumper 711 and the inner wedge 712 in the multipart retention bumper 701. During an interlock procedure, the outer bumper 711 may be stretched around the inner wedge 712 as it is advanced over the tapered end 762 to rest in the seating hub 752. The combination of tapers of the inner wall 754 and the tapered end 762 provide outward radial force to the outer bumper 711 as it is advanced axially, causing the outer bumper 711 to stretch.
The inner wedge 712 is formed from a suitable rigid material, including suitable plastics or polymers, including high density polyethylene (HDPE), TPE, Pebax® and any other suitable rigid material. In embodiments, the material of the inner wedge 712 is selected so as to be substantially non-compressible compression during conditions expected to accompany manufacture, assembly, or use. As used herein, substantially non-compressible during conditions expected to accompany manufacture, assembly, or use means that the inner wedges 712 show less than 5%, less than 3%, and/or less than 1% strain when subject to forces or stresses common during manufacture, assembly, and/or use. For example, a suitable durometer may be in excess of 60D, in excess of 65D, in excess of 70D, or in excess of 75D.
The outer bumper 711 is configured to stretch, i.e., elastically deform, around the inner wedge 712 and to be disposed on the seating hub 752 of the inner wedge 712 when the outer bumper 711 and the inner wedge 712 are in an interlocked configuration. As discussed above, the seating hub 752 of the inner wedge 712 has a diameter greater than that of the inner wall 754 such that, when the outer bumper 711 is disposed on the seating hub 752, the outer bumper 711 remains in a stretched configuration. The stretched configuration of the outer bumper 711 causes an increase in its effective diameter.
When disposed over the seating hub 752, the spokes 731 of the outer bumper 711 have an increased effective diameter due to stretching caused by the diameter of the seating hub 752. The outer bumper 711 may be disposed on the seating hub 752 via stretching over either the tapered end 762 or over the ridged tapered body 741. As discussed above, stretching over the tapered end 762 is facilitated by the tapers of the tapered end 762 and the inner wall 754. Once seated, the spokes 731 of the outer bumper 711 are arranged in radial alignment with the extension arms 742 of the inner wedge 712. As discussed above, this radial alignment is maintained by the stabilization fins 757. This arrangement allows inflation fluid to flow between the extension arms 742 (in the flow recesses 733) and between the spokes 731, without significant obstruction. Further, the extension arms 742 of the inner wedge 712 provide lateral support for the spokes 731 of the outer bumper 711. These features are discussed in greater detail below with respect to
In embodiments, each of the inner wedges 712 and outer bumpers 711 are configured with maximum diameters between approximately 0.1 inches and 0.25 inches, between 0.15 and 0.22 inches, between 0.19 and 0.21 inches, or approximately 0.2 inches. Such sizes correspond to a first radially unexpanded size and may be suitable for entry into the opening of a balloon of a balloon catheter, as discussed in greater detail below with respect to
Prior to stretching over the inner wedge 712, the outer bumper 711 has an effective diameter at the first radially unexpanded size smaller than a balloon opening. After stretching, the outer bumper 711 has an effective diameter at the second radially expanded size great enough to retain a prosthetic heart valve. Seating the outer bumper 711 on the seating hub 752 of the inner wedge 712 causes the effective diameter of the outer bumper 711 to expand from a first radially unexpanded size to a second radially expanded size.
The outer bumpers 711 may be manually manipulated through the balloon 810 and/or may be manipulated via one or more tools inserted through the balloon opening 849. Such tools may include hooked or curved tubes or mandrels configured for pushing or pulling the outer bumpers 711 over the inner wedges 712. Such tools are described in greater detail below with respect to
In variations of the assembly process, various steps may take place in a different order according to different requirements. For example, the outer bumpers 711 may be interlocked with the inner wedges 712 prior to bonding the balloon 810 to the distal tip 860. This may permit access to the multipart retention bumpers 701 from either end of the balloon 810. Other suitable variations may be employed without departing from the scope of this disclosure.
After completion of assembly, the balloon catheter 800 may be employed to deliver the prosthetic heart valve 120 to a treatment location. After completion of assembly, the balloon catheter 800 may be employed to deliver the prosthetic heart valve 120 to a treatment location. The prosthetic heart valve 120 is delivered by the balloon catheter 800 to a site of deployment. During the delivery process, the balloon catheter 800 may be guided by a guidewire passing through the guidewire lumen 865. During delivery of the prosthetic heart valve 120, the multipart retention bumpers 701 serve to maintain the axial position of the prosthetic heart valve 120 and reduce or prevent axial migration of the prosthetic heart valve 120. The multipart retention bumpers 701 combine with the wrapped balloon 810 create a stop 891 at either end of the prosthetic heart valve 120. The stop 891 applies axial force or pressure to the prosthetic heart valve 120 to maintain the position of the prosthetic heart valve 120 when it is subject to axial or other forces during delivery, for example, by contact with an introducer sheath. When axial force is applied to the stop 891 (and therefore to the outer bumpers 711), the extension arms 742 of the inner wedges 712 press against the spokes 731 of the outer bumpers 711 and the base 744 of the ridged tapered body 741 presses against the inner perimeter 732 to maintain the axial position of the outer bumpers 711. Further, the base 763 of the tapered end 762 presses against the inner perimeter 732 of the outer bumpers 711 to maintain the axial position of the outer bumper 711, in the event that the stop 891 is subject to axial force.
Once delivered, the prosthetic heart valve 120 is deployed through operation of the balloon catheter 800. Inflation fluid, e.g., saline, contrast fluid, etc., is delivered to the balloon 810 via the inflation lumen 875 disposed between the inner shaft 830 and the outer shaft 840. The inflation fluid travels through the flow recesses 733 of the inner wedges 712, and between the extension arms 742 of the inner wedges 712 and spokes 731 of the outer bumpers 711. Thus, the star shape of the retention bumpers 701 provides fluid pathways to facilitate inflation of the balloon 810. The star shape of the retention bumpers 701 and the flow recesses 733 are best illustrated in
Due to the lack of obstruction in the fluid flow pathways, inflation fluid is permitted to flow past the retention bumpers 701 along substantially longitudinal streamlines. Thus, the retention bumpers 701 reduce, minimize, eliminate, or otherwise limit radial flow of inflation fluid. As used herein, substantially longitudinal streamlines refer to fluid flows having streamlines approximately parallel to a designated axis. For example, a substantially longitudinal flow in a balloon catheter may have streamlines approximately parallel to a central axis of the balloon catheter. Approximately parallel may include streamlines within 10 degrees, within 5 degrees, and/or within 1 degree of parallel. Longitudinal flows represent fluid flows along the length of the balloon catheter. Radial flows refer to fluid flows having streamlines that deviate from parallelism with a designated axis, having a significant orthogonal vector component. A streamline with a significant orthogonal vector component may deviate from parallel by 10 degrees or more. Radial flows represent flows towards or away from the axial center of the balloon catheter.
In profile, the outer bumper 911 is substantially straight-sided from the valve abutment surface 971 to a base surface 972. The outer bumper 911 includes a spoked perimeter 930 surrounding a hollow core 920. The spoked perimeter 930 includes a plurality of spokes that form valve stops 931 and perimeter extensions 942. The valve stops 931 are located on an outer wall 953 of an inner perimeter 932. The inner perimeter 932 further includes the perimeter extensions 942. The perimeter extensions 942 are loops of material that extend out from the inner perimeter 932 and include arms 945 that extend from the inner perimeter 932 and are joined at their ends by hinges 946. Between each pair of perimeter extensions 942 is one of the valve stops 931, a solid portion of material that extends outward from the inner perimeter 932. One longitudinal end or side of each valve stop 931 forms a portion of the base surface 972 of the outer bumper 911 while the opposing longitudinal end or side of each valve stop 931 forms a portion of the abutment surface 971. The valve stops 931 extend longitudinally away from the spoked perimeter 930 in a direction parallel to the central axis of the outer bumper 911 such that the abutment surfaces 971 are disposed on a plane different than a plane of the spoked perimeter. The spoked perimeter 930 expands at least partially through a hinging action of the hinges 946 at the ends of the arms 945. When the perimeter extensions 942 hinge open, arms 945 of each perimeter extension 942 spread apart, causing an expansion of the spoked perimeter 930. The spoked perimeter 930 surrounds the hollow core 920, which is an empty interior space including a central core 921 and core extensions 951. The core extensions 951 are defined by the perimeter extensions 942.
As shown in
The spoked perimeter 930 includes an outer wall 953 defining an external surface of the spoked perimeter 930 and an inner wall 954 defining an internal surface and surrounding the hollow core 920 of the spoked perimeter 930. The outer wall 953 is substantially straight-sided from the valve abutment surface 971 to the base surface 972. The inner wall 954 defines the central core 921 and the core extensions 951. The inner wall 954 is substantially straight-sided from the valve abutment surface 971 to the base surface 972. Thus, the inner wall 954 and outer wall 953 are substantially parallel to one another. As used herein, substantially parallel refers to surfaces that are parallel to within approximately 5° of one another.
The tapered body 941 has axial symmetry and includes a base 944 and an apex 943. The base 944 is at the intersection between the tapered body 941 and the seating hub 952. The apex 943 is at an end of the inner wedge 912. The base 944 and the apex 943 are each circular, with the base 944 having a larger diameter than the apex 943. The sides of the tapered body 941 are smooth and taper from the base 944 to the apex 943. The tapered body 941 surrounds a cavity forming a portion of the interior cavity 923.
The tapered profile of the tapered body 941 serves to facilitate the interlock of the outer bumper 911 and the inner wedge 912 in the multipart retention bumper 901. During an interlock procedure, the outer bumper 911 may be expanded around the inner wedge 912 as it is advanced over the tapered body 941 to rest in the seating hub 952. The taper of the tapered body 941 provides outward radial force to the outer bumper 911 as it is advanced axially, causing the outer bumper 911 to expand.
The stop portion 962 is a cylindrical shape located adjacent the seating hub 952, opposite the tapered body 941. The stop portion 962 has axial symmetry and has an outer diameter greater than the outer diameter of the seating hub 952. The stop portion 962 includes an interior cavity forming a portion of the interior cavity 923. The stop portion 962 has an interior face 963 facing the seating hub 952 and an exterior face 961 that forms the end face of the inner wedge 912.
The seating hub 952 is located between the tapered body 941 and the stop portion 962. The seating hub 952 includes a cavity which, together with the cavities of the stop portion 962 and the tapered body 941 forms the interior cavity 923. The seating hub 952 is cylindrical. The seating hub 952 has an outer diameter greater than the outer diameter of the interior cavity 923 and smaller than the outer diameter of the base 944 of the tapered body 941 and smaller than the outer diameter of the stop portion 962. Thus, the base 944 of the tapered body 941 forms a flange or stop at one longitudinal end of the seating hub 952 and the interior face 963 of the stop portion 962 forms a flange or stop at the other longitudinal end of the seating hub 952. Further, the seating hub 952 includes stabilization fins 957 extending radially from the seating hub 952. With the exception of the stabilization fins 957, the seating hub 952 has axial symmetry. The radial arrangement of the stabilization fins 957 corresponds with the radial arrangement of the core extensions 951 and perimeter extensions 942 of the outer bumper 911. For example, the number of stabilization fins 957 may be the same as the number of the perimeter extensions 942, and the stabilization fins 957 and the perimeter extensions 942 may be radially aligned when the inner wedge 912 and the outer bumper 911 are interlocked.
When the outer bumper 911 is interlocked with the inner wedge 912, as shown in
The inner wedge 912 is formed from a suitable rigid material, including suitable plastics or polymers, including high density polyethylene (HDPE), TPE, Pebax® and any other suitable rigid material. In embodiments, the material of the inner wedge 912 is selected so as to be substantially non-compressible during conditions expected to accompany manufacture, assembly, or use. As used herein, substantially non-compressible during conditions expected to accompany manufacture, assembly, or use means that the inner wedges 912 show less than 5%, less than 3%, and/or less than 1% strain when subject to forces or stresses common during manufacture, assembly, and/or use. For example, a suitable durometer may be in excess of 60D, in excess of 65D, in excess of 70D, or in excess of 75D. In embodiments, the inner wedge 912 may include a radiopaque doping agent. The inclusion of a radiopaque doping agent in the material or materials of the inner wedge 912 does not compromise the performance of the inner wedge 912. The radiopaque doping agent in the inner wedge 912 improves the visibility of the inner wedge 912 during clinical imaging operations, such as fluoroscopy. Accordingly, the radiopacity of the inner wedges 912 may be used by a doctor or other operator to assist in positioning of the prosthetic valve held in place by the retention bumpers 901.
The outer bumper 911 is configured to expand, i.e., elastically deform, around the inner wedge 912 and to be disposed on the seating hub 952 of the inner wedge 912 when the outer bumper 911 and the inner wedge 912 are in an interlocked configuration. As discussed above, the seating hub 952 of the inner wedge 912 has an outer diameter greater than that of the inner wall 954 such that, when the outer bumper 911 is disposed on the seating hub 952, the outer bumper 911 remains in an expanded configuration. The expanded configuration of the outer bumper 911 causes an increase in its effective diameter.
When disposed over the seating hub 952, the valve stops 931 of the outer bumper 911 have an increased effective diameter due to expansion caused by the outer diameter of the seating hub 952. In the interlocked configuration of the multipart retention bumper 901, the abutment surface 971 of the valve stop 931 of the outer bumper 911 may be approximately flush with the exterior face 961 of the stop portion 962 of the inner wedge 912. Approximately flush, as used herein, refers to the abutment surface 971 and the exterior face 961 being coplanar to within 2 mm, within 1 mm, within 0.5 mm, and/or within 0.1 mm. This arrangement creates an approximately continuous face (within the above tolerances) at the increased effective diameter, i.e., the second radially expanded size, for the retention bumper 901 that faces the prosthetic valve on a balloon catheter. This continuous face serves to prevent axial migration of the prosthetic valve during a valve delivery operation. The continuous face created by the exterior face 961 and the abutment surface 971 is substantially perpendicular to a central axis of the retention bumper 901.
In embodiments, each of the inner wedges 912 and outer bumpers 911 are configured with outer diameters between approximately 0.1 inches and 0.25 inches, between 0.15 and 0.22 inches, between 0.19 and 0.21 inches, or approximately 0.2 inches in their natural resting states. Such sizes correspond to a first radially unexpanded size and may be suitable for entry into the opening of a balloon of a balloon catheter. In embodiments, the multipart retention bumpers 901 may have a maximum outer diameter between 0.25 inches and 0.35 inches, between 0.27 and inches, between 0.29 and 0.31 inches, or approximately 0.3 inches after the inner wedges 912 and the outer bumpers 911 are interlocked. Such sizes correspond to a second radially expanded size and are suitable for prevention of axial migration of a prosthetic heart valve located between the retention bumpers 901 when the prosthetic heart valve is subject to force.
Prior to expansion over the inner wedge 912, the outer bumper 911 has an effective diameter at the first radially unexpanded size smaller than a balloon opening. After expansion, the outer bumper 911 has an effective diameter at the second radially expanded size great enough to retain a prosthetic heart valve. Seating the outer bumper 911 on the seating hub 952 of the inner wedge 912 causes the effective diameter of the outer bumper 911 to expand from the first radially unexpanded size to the second radially expanded size.
When the outer bumper 911 is disposed on the seating hub 952 via expanding over the tapered body 941, gaps are created between the valve stops 931 due to the expansion of the spoked perimeter 930. The gaps, or flow recesses 933, allow inflation fluid to flow between the valve stops 931 (in the flow recesses 933) without significant obstruction.
The prosthetic heart valve 120 is crimped over the pleated and folded balloon 1010, as shown in
Due to substantial perpendicularity of the continuous face created by the exterior face 961 and the abutment surface 971, the stops 1091 provide an abrupt transition at the ends of the portion of the balloon 1010 where the prosthetic heart valve 120 is crimped. This abrupt transition increases the retention force relative to a sloped or less abrupt transition by preventing the prosthetic heart valve 120 from riding up a sloped transition.
After completion of assembly, the balloon catheter 1000 may be employed to deliver the prosthetic heart valve 120 to a treatment location. The prosthetic heart valve 120 is delivered by the balloon catheter 1000 to a site of deployment. During the delivery process, the balloon catheter 1000 may be guided by a guidewire passing through a guidewire lumen 1065. During delivery of the prosthetic heart valve 120, the multipart retention bumpers 901 serve to maintain the axial position of the prosthetic heart valve 120 and reduce or prevent axial migration of the prosthetic heart valve 120. The stops 1091 provide axial force or pressure to the prosthetic heart valve 120 to maintain the position of the prosthetic heart valve 120 when it is subject to axial or other forces during delivery, for example, by contact with an introducer sheath. When axial force is applied to the stop 1091 (and therefore to the outer bumpers 911), the interior face 963 of the stop portion 962 and the base 944 of the tapered body 941 press against the inner walls 954 and the outer walls 953 of the spoked perimeter 930 to maintain the axial position of each outer bumper 911.
Once delivered, the prosthetic heart valve 120 is deployed through operation of the balloon catheter 1000. Inflation fluid, e.g., saline, contrast fluid, etc., is delivered to the balloon 1010 via the inflation lumen 1075 disposed between the inner shaft 1030 and the outer shaft 1040. The inflation fluid travels through the flow recesses 933 of the outer bumpers 911. Thus, the star shape of the retention bumpers 901 provides fluid pathways to facilitate inflation of the balloon 1010. The path of the inflation fluid is shown by arrows 1099 in
Due to the lack of obstruction in the fluid flow pathways, inflation fluid is permitted to flow past the retention bumpers 901 along substantially longitudinal streamlines. Thus, the retention bumpers 901 reduce, minimize, eliminate, or otherwise limit radial flow of inflation fluid. As used herein, substantially longitudinal streamlines refer to fluid flows having streamlines approximately parallel to a designated axis. For example, a substantially longitudinal flow in a balloon catheter may have streamlines approximately parallel to a central axis of the balloon catheter. Approximately parallel may include streamlines within 10 degrees, within 5 degrees, and/or within 1 degree of parallel. Longitudinal flows represent fluid flows along the length of the balloon catheter. Radial flows refer to fluid flows having streamlines that deviate from parallelism with a designated axis, having a significant orthogonal vector component. A streamline with a significant orthogonal vector component may deviate from parallel by 10 degrees or more. Radial flows represent flows towards or away from the axial center of the balloon catheter.
In an operation 1202 of balloon catheter assembly process 1200, at least some of the multipart retention bumpers are disposed on the inner shaft of a balloon catheter to form a partial assembly. The inner wedge portions of the multipart retention bumpers are secured to the inner shaft, e.g., via over molding. One or more outer bumper portions of the multipart retention bumpers may be disposed over the shaft. The one or more outer bumper portions are not secured and are permitted freely slide on the inner shaft. In embodiments, a distal tip may also be secured to the partial assembly at this time. In some embodiments, the distal outer bumper is disposed on the inner shaft at a location distal of the distal inner wedge and the proximal outer bumper is disposed on the inner shaft at a location proximal of the proximal inner wedge. In embodiments, the proximal inner wedge is not disposed on the inner shaft at this stage. In some embodiments, both outer bumpers are disposed on the shaft between the inner wedges.
In an operation 1204, the distal and proximal multipart retention bumpers, including the inner wedges and the outer bumpers are inserted into a balloon of the balloon catheter. Prior to insertion, the balloon is bonded to the outer shaft of the balloon catheter. During insertion, the distal and proximal multipart retention bumpers, e.g., the distal and proximal inner wedges and the distal and proximal outer bumpers, are maintained at a first radially unexpanded size. In embodiments, maintaining the retention bumpers at a first radially unexpanded size may involve maintaining the inner wedges and outer bumpers in a non-interlocked configuration. In further embodiments, maintaining the multipart retention bumpers at a first radially unexpanded size may involve maintaining the inner wedges and outer bumpers in a partially-interlocked configuration that does not result in expansion of the outer bumper. In embodiments, the balloon is bonded, e.g., via heat bonding, to the distal tip of the catheter at this stage.
In an operation 1206, the distal and proximal multipart retention bumpers are interlocked and expanded from the first radially unexpanded size to the second radially expanded size. The free moving outer bumpers are stretched over the secured inner wedges and located on the seating hubs thereof. In embodiments, the outer bumpers may be stretched over the secured inner wedges from either end of the inner wedges. The inner wedges and the outer bumpers may be secured to one another by the mating of features of the elastic outer bumper and the rigid inner wedge, as described herein. To cause interlock, a tool may be inserted into the opening of the balloon of the balloon catheter to press the outer bumper over the inner wedge. In some embodiments, the inner wedge and the outer bumper may be manually manipulated through the material of the balloon.
In some embodiments, the distal multipart retention bumper may be interlocked prior to inserting the proximal multipart retention bumper into the balloon.
In an operation 1208, assembly of the balloon catheter is completed. Completing the balloon catheter assembly includes the completion of all further required steps. For example, the outer shaft may be assembled to the catheter at this time by inserting the inner shaft into the outer shaft and bonding the outer shaft to the balloon. In some embodiments, if the balloon has not yet been bonded to the distal tip, this operation may be completed at this stage. Completing balloon catheter assembly may further involve steps such as folding the balloon, attaching the inner shaft and the outer shaft to a proximal handle, crimping a prosthetic heart valve over the balloon, and any other step required to complete assembly of the balloon catheter.
As discussed above, e.g., with respect to
The foregoing description has been presented for purposes of illustration and enablement and is not intended to be exhaustive or to limit the invention to the precise form disclosed. Other modifications and variations are possible in light of the above teachings. The embodiments and examples were chosen and described in order to best explain the principles of the invention and its practical application and to thereby enable others skilled in the art to best utilize the invention in various embodiments and various modifications as are suited to the particular use contemplated. It is intended that the appended claims be construed to include other alternative embodiments of the invention.
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/US2021/058755 | 11/10/2021 | WO |
| Number | Date | Country | |
|---|---|---|---|
| 63112807 | Nov 2020 | US | |
| 63230100 | Aug 2021 | US |
