CROSS REFERENCE TO RELATED APPLICATIONS
BACKGROUND OF THE INVENTION
This application is a continuation of U.S. application Ser. No. 10/738,666 (Attorney Docket No. 021629-000510US) filed Dec. 16, 2003, which claims the priority benefit of U.S. Provisional Patent Application No. 60/440,839 (Attorney Docket No. 21629-000500US), filed Jan. 17, 2003, the full disclosures of which are incorporated herein by reference.
1. Field of the Invention
The present invention relates generally to medical devices and methods. More particularly, the present invention relates to apparatus and methods for delivering a plurality of separate luminal prostheses within a body lumen, such as a blood vessel.
Coronary artery disease is the leading cause of death and morbidity in the United States and Western society. In particular, atherosclerosis in the coronary arteries can cause myocardial infarction, commonly referred to as a heart attack, which can be immediately fatal or, even if survived, can cause damage to the heart which can incapacitate the patient.
While coronary artery bypass surgery can be an effective treatment for stenosed arteries resulting from atherosclerosis or other causes, it is a highly invasive procedure which is also expensive and which requires substantial hospital and recovery time. Percutaneous transluminal angioplasty, commonly referred to as balloon angioplasty, is less invasive, less traumatic, and significantly less expensive than bypass surgery. Heretofore, however, balloon angioplasty has not been considered as effective a treatment as bypass surgery. The effectiveness of balloon angioplasty, however, has improved significantly with the introduction of stenting, which involves the placement of a scaffold structure within an artery that has been treated by balloon angioplasty. The stent inhibits abrupt reclosure of the artery and has some benefit in inhibiting subsequent restenosis resulting from hyperplasia.
Presently available stents may be generally categorized as either “closed cell configurations” or “open cell configurations.” Closed cell configurations are characterized by ellipses, ovals, and polygonal structures, such as closed boxes, rhomboids, diamonds, and the like, which open in the circumferential direction and shorten in the axial direction as the stent is expanded. Open cell configurations include zigzag and serpentine structures which may be formed as a plurality of discreet rings or may be formed from a single continuous wire or other element. Closed cell stents are advantageous in that they provide better coverage of the blood vessel wall when the stent is deployed. This is particularly advantageous in tightly curved segments of the vasculature where even stent coverage in both the axial and circumferential directions on the outer wall of the vessel has been shown to reduce restenosis. Such even coverage is also an advantage in achieving uniform delivery from drug eluting stents. In contrast, open cell stent configurations are generally more flexible than the closed cell configurations. Such flexibility is advantageous in the tortuous regions of the vasculature where enhanced flexibility can provide better conformance to the vessel being treated. Better conformance can reduce the stress on the vessel wall, particularly at the stent ends, and lead to reduced restenosis.
For these reasons, it would be desirable to provide improved stents and stent structures. In particular, it would be desirable to provide stents and stent structures which combine the improved wall coverage of closed cell stent structures with the increased flexibility of open cell stent structures. It would be still further desirable if such improved stent structures allowed a physician to optimize the length of vessel being treated in accordance with the nature of the disease, allowed for the delivery of both very short and very long stent structures, and optionally permited delivery of stent structures at multiple contiguous and/or non-contiguous locations within a body lumen. At least some of these objectives will be met by the inventions described hereinafter.
2. Description of the Background Art
- BRIEF SUMMARY OF THE INVENTION
U.S. Pat. Nos. 6,200,337 and 5,870,381 describe stents having closed cell rings with overlapping portions connected by axial connecting members. U.S. Pat. No. 6,375,676 describes a stent having open cell rings with overlapping portions connected by axial connecting members. U.S. Patent Application Publication Nos. 2002/0188343 and 2002/0188347 describe expandable stents having interconnecting elements which interlock circumferentially adjacent bridges between axially adjacent stent segments. U.S. Pat. No. 4,580,568 describes the sequential placement of a plurality of zigzag ring stents where the stents may optionally be overlapped (FIGS. 7 and 8). U.S. Pat. No. 6,319,277 describes a stent formed from a single element into a plurality of nested “waves.” U.S. Pat. No. 5,554,181 describes a stent formed from a single element into partially overlapping windings. Other patents of interest include U.S. Pat. Nos. 6,312,458; 5,879,370; 5,755,776; 5,507,771; and 5,104,404. U.S. Pat. No. 6,258,117 B1 describes a stent having multiple sections connected by separable or frangible connecting regions. Optionally, the connecting regions are severed after the stent structure has been implanted in the blood vessel. U.S. Pat. Nos. 5,571,086; 5,776,141, and 6,143,016 describe an expandable sleeve for placement over a balloon catheter for the delivery of one or two stent structures to the vasculature. U.S. Pat. No. 5,697,948, describes a catheter for delivering stents covered by a sheath.
The present invention provides methods and apparatus for prosthesis placement, such as stenting of body lumens, typically blood vessels, and more typically coronary arteries. The methods and systems will also find significant use in the peripheral vasculature, the cerebral vasculature, and in other ducts, such as the biliary duct, the fallopian tubes, and the like. The terms “stent” and “stenting” are defined to include any of the wide variety of expandable prostheses and scaffolds which are designed to be intraluminally introduced to a treatment site and expanded in situ to apply a radially outward force against the inner wall of the body lumen at that site. The stents and prostheses of the present invention commonly comprise a closed or, less preferably, an open lattice structure, and are typically formed from a malleable or elastic metal. When formed from a malleable metal, such as stainless steel, gold, platinum, titanium, and super alloys, the stents will typically be expanded by a balloon which causes plastic deformation of the lattice so that it remains opened after deployment. When formed from an elastic metal, including super elastic metals such as nickel-titanium alloys, the lattice structures will usually be radially constrained when delivered and deployed by releasing the structures from such radial constraint so that they “self-expand” at the target site. When the stent or lattice structures are covered with a fabric or polymeric membrane covering, they are commonly referred to as grafts. Grafts may be used for the treatment of aneurysms or other conditions which require placement of a non-permeable or semi-permeable barrier at the treatment site. The terms “stent” and “stent structures” refer broadly to all radially expansible stents, grafts, and other scaffold-like structures which are intended for deployment within body lumens.
The stents and stent structures of the present invention may have any of a variety of common constructions, including closed cell constructions such as expansible ovals, ellipses, box structures, expandable diamond structures, expandable rhomboid structures, as well as other regular and irregular polygonal structures, etc. In addition, the closed cells may have complex slotted geometries, such as H-shaped slots, I-shaped slots, J-shaped slots, etc. Suitable open cell structures include zigzag structures, serpentine structures, and the like. Such conventional stent structures are well described in the patent and medical literature. Specific examples of suitable stent structures are described in the following U.S. Patents, the full disclosures of which are incorporated herein by reference: U.S. Pat. Nos. 6,315,794; 5,980,552; 5,836,964; 5,527,354; 5,421,955; 4,886,062; and 4,776,337. Preferred structures are described herein with reference to FIGS. 4 and 5.
According to one aspect of the present invention, stents will comprise a plurality of independent expansible rings each having a length of 1 mm or greater, usually 2 mm or greater, and sometimes of 3 mm or greater, usually being in the range from 1 mm to 10 mm, typically from 2 mm to 7 mm, more typically from 2 mm to 5 mm. The use of such short ring lengths is advantageous since the overall stent length will be a multiple of the ring length.
The methods and apparatus of the present invention will provide for the deployment of a plurality of stents or other prostheses from a common stent delivery catheter. Usually, the number of delivered stents will be in the range from 2 to 50, typically from 3 to 30, and most typically from 3 to 25. As more stents are placed on the delivery catheter, the individual stent length will often be somewhat less, although this is not necessarily the case in all instances. The multiple prostheses may be deployed individually or in groups of two or more at a single location or at multiple spaced-apart locations in the body lumen or lumens.
In another aspect of the present invention, stent structures will comprise a plurality of radially expansible rings, as generally described above, arranged along an axial line. Expansible rings are arranged adjacent to each other and will include axially extending elements which interleave or nest with similarly axially extending elements on adjacent rings. By “interleaved” it is meant that the axially extending elements on adjacent rings will interpenetrate with each other in an axial direction, at least prior to stent expansion and preferably even after stent expansion. Usually, the interpenetrating elements will not overlap, i.e., be positioned one over another in the radial direction, but it is possible that in some implementations there may be some overlapping prior to or even after expansion. The axial interpenetration will be at least 0.1 mm, usually being at least 1 mm, and often being in the range from 1 mm to 5 mm, and will of course depend on the axial length(s) of the adjacent ring(s). Expressed as a percentage, the axial length of the axially extending elements will usually be at least 5% of the axial length of the ring, usually being from 5% to 50%, and preferably being from 20% to 30%.
Preferably, the axially extending elements on adjacent rings will interleave without interlocking so as to permit axial separation between the adjacent rings prior to expansion of the rings. However, axially extending elements may, in some instances, also interpenetrate in a peripheral direction prior to expansion. Such peripheral interpenetration can provide axial interlocking of the axially adjacent expansible rings prior to expansion. It will usually be desirable or even necessary that the peripheral interpenetration be relieved during radial expansion of the stent structures so that the independent rings be released from each other when deployed. In other instances, however, a tether or other types of links may be provided to interconnect or otherwise restrain the rings even after expansion and deployment.
It is not necessary that all adjacent rings be unconnected, although at least two, and preferably three, four, five, eight, ten, or more adjacent rings will be unconnected. Thus, some (but fewer than all) of the adjacent rings of the stent structures may have ties or links therebetween, including flexible or non-flexible (deflectable) ties or links. The axially adjacent rings, however, will usually not be connected, although in some cases they may have easily separable or non-permanent connections as described in more detail below. Each expansible ring will preferably comprise expansible closed cell structures, as set forth above. Less preferably, the expansible rings may comprise expansible open cell structures, as set forth above. The lengths and diameters of the individual rings have been set forth generally above. The stent structure will typically comprise from 2 to 50 individual rings, usually from 3 to 30 individual rings, and often from 3 to 25 individual rings.
The spacing between adjacent rings may be uniform or non-uniform, preferably being uniform. In some cases, it is desirable that the edges of the adjacent rings be spaced-apart by a uniform distance in the axial direction, typically at least 0.1 mm, usually being from 0.1 mm to 0.5 mm, prior to stent expansion. In other situations, it will be preferred that the adjacent rings be in contact with each other at discreet points or along continuous sections of the edges. In some cases, the stent structures will be configured to shorten upon expansion to increase the spacing between rings. It is usually preferable that the edges of the adjacent rings not overlap, at least prior to deployment. Deployment of the stents, particularly in curved and tortuous luminal regions, may sometimes result in touching and overlapping of the stent rings.
The stent structures may be modified in a variety of ways which are used with other conventional stents. For example, some or all of the radially expansible rings may releasably carry a biologically active agent, such as an agent which inhibits hyperplasia. Exemplary anti-hyperplasia agents include anti-neoplastic drugs, such as paclitaxel, methotrexate, and batimastal; antibiotics such as doxycycline, tetracycline, rapamycin, everolimus and other analogs and derivatives of rapamycin, and actinomycin; amino suppressants such as dexamethasone and methyl prednisolone; nitric oxide sources such as nitroprussides; estrogen; estradiols; and the like.
In another aspect of the present invention, a stent deployment system comprises an elongate carrier having a central axis and including a plurality of radially expansible rings arranged over a surface thereof. At least some of the radially expansible rings will have the features and characteristics just described with respect to the present invention. The elongate carriers of the stent deployment systems will typically comprise a radially expansible balloon having an outer surface where the radially expansible rings are disposed over the outer surface of the balloon. In such cases, the balloon may comprise a single inflation chamber in which case all of the rings will be expanded simultaneously. Alternatively, the balloon may comprise a plurality of independently inflatable chambers so that individual expansible rings may be deployed separately from the other rings.
The elongated carrier of the stent deployment system may alternatively comprise a carrier tube having an inner surface which carries and constrains the radially expansible rings. In such cases, the expansible rings will usually be self-expanding, i.e., held in a radially constrained configuration by the carrier tube prior to release and expansion at a luminal target site. Usually, the carrier tube structures will further comprise a pusher tube arranged to axially advance the radially expansible rings from the carrier tube. The elongated carrier may still further comprise a balloon arranged to receive and expand individual rings as they advance from the carrier tube, in which case the carrier may be used for delivering the formable (balloon-expansible) stent structures. However, such a balloon may also be used with self-expanding stent structures to control or enhance expansion, to perform predilatation of a lesion prior to stent deployment, or to further expand the stent structures and dilate the vessel lumen after the structures have self-expanded.
In a further aspect of the present invention, multiple independent stent rings are arranged on a carrier by the following methods. An elongated carrier structure is provided and a plurality of radially expansible rings comprising axially extending elements are mounted on the carrier structure such that the axially extending elements on adjacent rings interleave or nest after they are mounted. The number of rings mounted on the carrier is selected to provide a desired overall stent length, and the number of rings is typically in the ranges set forth above, providing overall stent lengths in the range from 6 mm to 120 mm, usually from 9 mm to 100 mm, and typically from 12 mm to 50 mm. Other aspects of the individual radially expansible rings have been described above.
BRIEF DESCRIPTION OF THE DRAWINGS
In yet another aspect of the present invention, methods for stenting a body lumen comprise delivering to the body lumen a stent structure having a plurality of radially expansible rings. The rings are as described above with respect to other aspects of the present invention, and at least some of the rings are expanded within the body lumen so that the axially extending elements open and axially move apart from each other as they radially expand. Preferably, the length of the axially extending elements and degree of radial expansion will be selected so that the elements remain interleaved even after being fully expanded within the body lumen. Such an interleaving structure enhances the continuity of lumenal wall coverage provided by the deployed stent structure. Target body lumens are typically blood vessels, more typically arteries, such as coronary arteries. The rings may be delivered simultaneously, typically using a single inflatable balloon, or sequentially, typically using a carrier tube, pusher tube and optionally deployment balloon. Methods may be used for delivering from 3 to 50 rings, usually from 3 to 30 rings, and typically from 3 to 25 rings, to cover a luminal length in the range from 6 mm to 120 mm, usually from 9 mm to 100 mm, and typically from 12 mm to 50 mm.
FIG. 1 is a schematic illustration of a stent structure according to the present invention comprising a plurality of closed cell ring structures.
FIG. 2 illustrates the stent structure of FIG. 1 shown in its radially expanded configuration.
FIGS. 2A and 2B illustrate the difference in deployed configuration of non-nested and nested stent structures, respectively.
FIG. 3 illustrates a stent structure constructed in accordance with the principles of the present invention comprising a plurality of open cell expansible rings.
FIG. 4 illustrates the stent structure of FIG. 3 shown in its radially expanded configuration.
FIG. 5 illustrates a first exemplary expansible ring structure in accordance with the principles of the invention.
FIG. 6 illustrates a stent structure comprising a plurality of the ring structures of FIG. 5, shown in a rolled out radially collapsed configuration.
FIGS. 6A and 6B illustrate variations on the ring structure of FIG. 6, where the variations are chosen to inhibit axial separation of the ring structures prior to deployment.
FIG. 7 illustrates the stent structure of FIG. 6 shown in its radially expanded configuration.
FIG. 8 illustrates a second exemplary expansible ring structure in accordance with the principles of the present invention.
FIG. 9 illustrates a stent structure comprising a plurality of the rings of FIG. 8.
FIG. 10 illustrates the stent structure of FIG. 8 in its radially expanded configuration.
FIGS. 11, 11A-11C and 12-14 illustrate further exemplary expansible ring structures in accordance with the principles of the present invention.
FIGS. 15A and 15B illustrate a further embodiment of a stent structure according to the present invention shown in unexpanded and expanded configurations, respectively.
FIGS. 16A and 16B illustrate a still further embodiment of a stent structure according to the present invention shown in unexpanded and expanded configurations, respectively.
FIGS. 17A-I7C illustrate deployment of a closed cell stent structure according to the present invention with both a balloon having a single chamber (FIG. 16) and a balloon having multiple chambers to permit selective delivery of portions of the stent structure.
FIGS. 18A-18D illustrate deployment of a plurality of a expansible rings which form a stent structure according to the present invention using a delivery tube and pusher tube in combination with an expansion balloon.
FIG. 19 illustrates a kit constructed in accordance with the principles of the present invention.
DETAILED DESCRIPTION OF THE INVENTION
FIGS. 20A-20B, 21A-21B, and 22A-22B illustrate further embodiments of stent structures according to the invention in unexpanded and expanded configurations.
The present invention provides apparatus, systems, and methods for preparing and delivering stent structures comprising a plurality of “separate” or “discreet” radially expansible ring segments. By “separate” or “discreet,” it is meant that the ring segments are unconnected (or easily disconnected) at the time they are delivered to a target body lumen. Usually, the ring segments will be closely packed to provide a relatively high degree of vessel wall coverage after they are expanded. By disconnecting the adjacent segments, however, such a tightly packed structure can retain a very high degree of flexibility permitting delivery and conformance in even highly torturous regions of the vasculature and other body lumens.
The ability to closely pack the expansible ring segments and achieve a high degree of vessel wall coverage is achieved at least partly because at least some of the axially adjacent rings comprise axially extending elements which interleave or nest with axially extending elements on an adjacent connected ring. Usually, the axially extending elements will be formed from a radially expansible portion of the ring, e.g., the element will be part of the closed cell structure or open cell structure as described in more detail hereinbelow. As these expansible sections will typically foreshorten as they are radially expanded, interleaving and nesting the segments on adjacent rings prior to expansion minimizes or preferably eliminates any gaps in coverage after the stent is expanded, as described in more detail below.
The stent structures of the present invention may be fabricated as either balloon-expansible or self-expanding stents according to methods well known in the art. Typical deformable materials suitable for fabricating balloon-expansible stent structures include 316L stainless steel, gold, platinum, cobalt chrome, platinum, and the like. Suitable resilient materials for self-expanding stents include nickel titanium alloys, various spring stainless steel alloys, Eligloy® alloy, and the like. It will also be possible to form the stent structures of the present invention from both natural and synthetic polymers. Natural polymers include collagen, gelatin, chitin, cellulose, and the like. Suitable synthetic polymers include polyglycolic acids (PGA), polylactic acids (PLA), poly ethylene glycols (PEG), polyamides, polyimides, polyesters, and the like. In some instances, it would be possible to form different radially expansible segments from different materials in order to achieve different properties.
The stent structures will comprise a plurality of the individual radially expansible ring segments with typical dimensions, numbers, and the like, described above in the summary. The plurality of ring segments will be arranged prior to delivery, in a manner suitable for delivery to and deployment within a target blood vessel or other body lumen. Usually, the plurality of radially expansible rings will be arranged along an axial line, typically defined by a deployment balloon, a delivery tube, or some combination thereof. The expansible ring segments will be arranged so that the axially extending elements on each of the segments is interleaved with corresponding axial extending elements on adjacent but unconnected ring segments. Referring now to FIGS. 1-4, such arrangements will be generally described for both closed cell ring structures (FIGS. 1 and 2) and open cell ring structures (FIGS. 3 and 4).
In FIG. 1, a portion of a stent structure 10 comprising a plurality of radially expansible rings 12 is illustrated. Each radially expansible ring 12 includes a plurality of closed rhomboid or diamond structures 14 circumferentially joined by connectors 16. It will appreciated that the stent structure 10 is shown in a “rolled-out” configuration, and that only a portion of the structure is depicted for simplicity. Usually, the stent structure would contain a greater number of expansible rings 12, and each ring would include a larger number of rhomboid cells.
Of particular importance to the present invention, FIG. 1 illustrates that each rhomboid cell 14 includes an axially extending element 18 which interleaves with a similar element on an adjacent ring structure. This interleaved structure permits a very close packing of the rings without the need to physically attach the rings. Moreover, when the stent structure is radially expanded, as shown in FIG. 2, the axially extending elements 18 will usually continue to axially interleave which increases the coverage of the body lumen wall being treated.
The advantages of the present invention are particularly apparent in curved blood vessels BV, as illustrated in FIGS. 2A and 2B. An expanded, non-interleaved multiple ring stent is shown in FIG. 2A. Substantial gaps G appear between the axially extending elements 18 on the large diameter side of the curved vessel segment. In contrast, the nested stent configurations of the present invention are able to maintain interleaving of the axially extending elements 18, even on the large diameter side of the curved vessel segment, as shown in FIG. 2B. While the present invention cannot assure that gaps will always be eliminated, the number and extent of the gaps will at least be reduced, thus improving wall coverage.
A similar result can be achieved with a stent structure 20 comprising a plurality of open cell zigzag ring structures 22, shown in FIGS. 3 and 4. Each zigzag ring includes axially extending elements which alternate directions, and the rings are arranged so that the elements are “nested” as shown in FIG. 3. After radial expansion of the stent structure 20, the nested axially extending elements of the rings 22 remain generally overlapping, as shown in FIG. 4, even when the stent has undergone significant radial expansion. While prior stent structures have utilized nested zigzag structures, they have generally either connected adjacent structures or utilized only a single filament for forming such structures. In neither case can the flexibility achieved by the present invention in combination with the ability to selectively deliver independent radially expansible segments be achieved.
Referring now to FIGS. 5-7, a particular stent structure 30 comprising a plurality of radially expansible rings 32 is illustrated. Each ring 32, as shown in FIG. 5, comprises a plurality of closed cell boxes 34 joined at their midpoints by circumferentially directed connectors 36. Each box 34 includes a central opening 35 which is generally an axial cut enlarged at each end and in the middle. As with prior illustrations, the ring structure 32 is shown in its rolled-out or flattened configurations. In the actual stent structure, the ring would be rolled so that the “broken” connectors 34′ are in fact connected to form a cylindrical shape. The “bow tie” shape of the central opening 35 is advantageous as it permits maximum radial compression of the stent while minimizing both the delivery profile and the stress relief of the stent during expansion in the body lumen.
FIG. 6 illustrates the very tight packing of the stent structure 30 that can be achieved. The stent structure 30 in FIG. 6 is in its pre-deployment configuration as it would be when placed over a balloon or within a delivery tube, as described in more detail hereinbelow. It can be seen that virtually all of the available area for carrying the stent is covered. Thus, when the stent is expanded as shown in FIG. 7, the area of the blood vessel or other luminal wall will be maximized. Moreover, this very close packing of the stent is achieved while concurrently providing a very high degree of flexibility while the stent is being delivered and conformability after the stent is deployed. Such flexibility results in large part from the fact that the adjacent rings are unconnected and free to move relative to each other as the stent is delivered and deployed. Coverage in curved vessels will be improved with the specific design of FIGS. 6 and 7 generally as shown in FIGS. 2A and 2B.
Axial separation of the rings 32 of stent structure 30 can be inhibited by modifying the ring geometries in a variety of ways, such as shown in FIGS. 6A and 6B. In FIG. 6A, the boxes 34 a are fabricated (or deformed after fabrication) to collapse near the centers so that they form “bow tie” structures, with enlarged ends 34 b interlocking. Alternatively, the boxes 34 c can be inclined relative to the axial direction, as shown in FIG. 6B, to also provide interlocking of adjacent rings prior to deployment. Such inclination can be used with at least most of the embodiments of the present invention to improve axial retention. In addition, other patterns, such as chevrons, interleaved sigmoidal shapes, and the like could also be used to provide the desired interlocking prior to stent expansion.
Referring now to FIGS. 8-10, a similar degree of wall coverage and flexibility can be achieved with open cell stent structures. Stent structure 40 (FIG. 9) comprises a plurality of open cell expansible rings 42 formed in a “castellated” pattern, as shown in more detail in FIG. 8. The castellations comprise narrow U-shaped loops 44 and 46 which alternatively extend in a right hand direction (loop 44) and left hand direction (loop 46) relative to a circumferential center line 48. The rings 42 are arranged so that the loops 44 and 46 overlap, as shown in FIG. 9, to form a tightly packed configuration. When expanded, as shown in FIG. 9, the loops 44 and 46 continue to overlap to provide a very high degree of vessel wall coverage, as shown in FIG. 10. The open cell configuration of FIGS. 8-10 will also improve coverage in curved vessels, minimizing gaps as discussed previously. The length of the open cells will be in the range from 0.5 to 10 mm, usually from 2 to 5 mm.
Referring now to FIGS. 11-14, additional embodiments of the radially expansible ring segments are illustrated. As with prior illustrations, the ring segments are shown in their pre-deployed configuration in a rolled-out manner. Ring structure 50 of FIG. 11 comprises a plurality of closed cell box elements 52 joined by circumferential connectors 54 and 56. Ring 50 is similar to ring 32 of FIG. 5, except that the circumferential connectors 54 are split to form H-shaped slots 55 which span pairs of adjacent box structures 52 and the intermediate connectors 54 form a single, larger cell structures. Such larger openings are advantageous when stenting in blood vessels with side branches which must be kept open. In particular, the side branches may be accessed by opening the slots 55 with a balloon structure. In contrast, the cell pattern of stent 32 (FIG. 5) provides a greater coverage that may be of particular importance with drug eluting stents.
Stent structures comprising multiple rings 50 are shown in their unexpanded and expanded configuration in FIGS. 11A and 11B, respectively. Of particular note, the open slots 55 (FIG. 11B) provide for significant additional expansion (via balloon dilation or other subsequent intervention) in order to provide access to a side branch or for any other purpose. A further expanded slot 55 is shown in FIG. 11C, as expanded by balloon B.
Ring structure 60 of FIG. 12 comprises a plurality of interconnected box structures 62, 64, and 66. Each of the box structures shares common axial struts or beams, but the axially offset nature of the three box structures permits radial expansion. Moreover, the box structures 62 and 66 provide the axially extending elements which may be interleaved in forming a stent structure from a plurality of the rings 60. Axially extending elements 62 and 66 interleave and mate so that interleaved extending elements of adjacent stents can be interference fit with each other to provide a friction fit which inhibits separation of the stents, or be kept out of contact to allow for separation. Furthermore, extending elements can deflect radially inward which will provide additional adherence to an expandable delivery balloon and increased stent retention.
Ring structure 70 in FIG. 13 comprises paired, symmetric box structures 72 and 74 joined by short circumferential connectors 76. Each of the box structures 72 and 74 define a long and a short axially extending member which can be aligned with each other when forming a stent structure from a plurality of the rings 70. This particular structure will provide good adherence to an expandable delivery balloon during deployment and have many of the same advantages as the embodiment of FIG. 12.
Ring structure 80 of FIG. 14 is similar to that of ring structure 70 of FIG. 13, except that the “longer” rings terminate in a retainer, such as T-ends 82. When deploying multiple rings 80 in a stent structure, the T-ends will interlock to help hold the ring in place on the balloon or within the delivery tube. The interlock, however, does not provide a permanent attachment and, adjacent ring segments 80 will naturally release from each other during deployment. Moreover, since the interlocking structures are not actually attached, they permit a high degree of flexibility while the stent is being deployed. While T-ends are shown in FIG. 14, the terminal retainers could be L- or J-shaped ends or have any other geometry, which also provides for interlocking. In particular, each of these geometries will include a peripherally extending segment 83 which interlocks with a peripherally extending segment 83 on an adjacent T-end 82. Upon expansion of the ring 80, the segment 83 will move apart allowing the adjacent rings to deploy separately. When deploying multiple rings 80 in a stent structure, the T-, L- or J-ends will interlock to help hold the ring in place on the balloon or within the delivery tube. The interlock, however, does not provide a permanent attachment and, adjacent ring segments 80 will naturally release from each other during deployment. Such interlocking could also incorporated in the embodiments of FIGS. 5, 8, 11 and 12.
As illustrated thus far, the stent structures have generally maximized to vessel wall coverage achieved after expansion. While this will often be desired, in some instances it may be desired to lessen the amount of wall coverage. The stent structures shown in FIGS. 15A and 15B and FIGS. 16A and 16B, achieve such reduced wall coverage by providing “spacers” between adjacent rings.
In FIG. 15A, a stent structure 90 includes independent rings 92 having boxes 93 circumferentially separated by spacers 94. The spacers 94 will either not expand or expand only after the boxes 93 have expanded, thus maintaining an axial distance D between adjacent rings after expansion, as shown in FIG. 15B. The distance D will be equal to about one-half the total axial length of the spacer 94.
Stent structure 96 (FIGS. 16A and 16B) is similar to structure 90, except that spaces 97 are axially split to define an H-shaped cell (as discussed with earlier embodiments) and certain of the rings 98 and joined by sigmoidal links 99.
Stent structures according to the present invention may be delivered in a variety of ways. As illustrated in FIGS. 17A- 17C, the stent structure 30 may be delivered on a balloon catheter 90 having a balloon 92 with a single inflation chamber. Deployment of the stent 30 is illustrated in FIG. 17B where all independent ring structures 32 are expanded simultaneously. Alternatively, as illustrated in FIG. 17C, catheter may carry a balloon 94 having a plurality of independently inflatable compartments. In that way, one or more of the independent compartments may be inflated separately from others of the compartments to selectively deploy one, two, three, or more of the independent ring structures 32. In that case, others of the ring structures 32 will remain unexpanded and available for separate expansion or may be simply removed from the patient if unused.
Referring now to FIGS. 18A-18D, an alternative stent structure delivery protocol employing a carrier tube will be described. Such delivery protocols are described in more detail in co-pending application Ser. No. 10/306,813, filed on Nov. 27, 2002 (Attorney Docket Number 021629-000320US), and in copending application Ser. No. 10/637,713, filed Aug. 8, 2003 (Attorney Docket No. 21629-000340US), the full disclosures of which are incorporated herein by reference. Catheter 160 (FIG. 18A) comprises a sheath 164, pusher tube 166, and a catheter body 168. The catheter body 168 includes an expansible balloon 170 over its distal portion. Individual expansible rings, as described above, are deployed, as illustrated in FIGS. 18B and 18C, by first advancing the distal-most ring 162 using the pusher tube 166. The catheter body 168 is also distally advanced so that a distal portion of the balloon 170 lies within the distal-most deployed ring 162, as shown in FIG. 18B. The remaining proximal portion of the balloon 170 will, of course, remain within the other rings 162 which themselves remain within the sheath 164. The balloon 170 is then inflated, but only the advanced distal portion of the balloon inflates within the advanced ring 162, as illustrated in FIG. 18C. Expansion of the remaining proximal portion of the balloon is prevented by the sheath 164. Similarly, the remaining rings 162 remain unexpanded since they remain within the sheath 164.
Referring now to FIG. 18D, additional rings 162 may be deployed, either at the same target location within the blood vessel or at a different, spaced-apart locations within the blood vessel. Deployment of two rings 162 is illustrated. The two rings 162 are axially advanced using the pusher tube 162 so that they are positioned over the uninflated balloon 170. The balloon 170 is then inflated, as illustrated in FIG. 18D, thus expanding the rings 162 within the blood vessel BV. It will be appreciated that the catheter 160 could carry many more than the four illustrated rings 162, and three, four, five, ten, and even 20 or more individual rings could be deployed at one time, with additional single prostheses or groups of prostheses being deployed at different times and/or at different locations within the blood vessel. The use of “stent valves” as described in application Ser. No. 10/306,813, previously incorporated herein by reference, may preferably be employed to facilitate controlling the number of rings deployed and the spacing between the deployed and undeployed rings.
Referring now to FIG. 19, kits 200 according to the present invention comprise a catheter 160 (or a balloon catheter) in combination with instructions for use IFU. The instructions for use set forth any of the methods of the present invention, and in particular set forth how the catheter 160 may be used to implant a stent structure comprising multiple rings within a blood vessel or other body lumen. The catheter 160 and instructions for use will typically be packaged together, for example within a conventional package 202, such as a box, tube, pouch, tray, or the like. Catheter 160 will typically be maintained in a sterile condition within the package 202. The instructions for use may be provided on a package insert, may be printed in whole or in part on the packaging, or may be provided in other ways, such as electronically over the internet, on an electronic medium, such as a CD, DVD, or the like.
A further alternative stent structure according to the invention is illustrated in FIGS. 20A-20B. FIG. 20A illustrates a portion of a stent segment 201 in an unexpanded configuration, shown in a planar shape for clarity. Stent segment 201 comprises two parallel rows 203A, 203B of I-shaped cells 205 formed around an axis A so that stent segment 201 has a cylindrical shape. The terms “I-shaped” and “H-shaped” as used herein may refer to a similar cell geometry comprising two generally parallel slots connected by an interconnecting slot. Such cells may appear H-shaped when axis A is in a vertical orientation, or I-shaped axis A is in a horizontal orientation. Each cell 205 has upper and lower axial slots 207 aligned with the axial direction and a circumferential slot 204. Upper and lower slots 207 preferably have an oval, racetrack, rectangular or other oblong shape with a long dimension L generally parallel to axis A and a short dimension W perpendicular thereto. Axial slots 207 are bounded by upper axial struts 206A and lower axial struts 206B, curved outer ends 208 and curved inner ends 210. Each circumferential slot 204 is bounded by an outer circumferential strut 209 and an inner circumferential strut 211. Each I-shaped cell 205 is connected to the adjacent I-shaped cell 205 in the same row 203A or 203B by a circumferential connecting strut 213. All or a portion of cells 205 in row 203A merge or join with cells 205 in row 203B at the inner ends 210, which are integrally formed with the inner ends 210 of the adjacent cells 205.
Stent segment 201 is configured to interleave with an adjacent stent segment of similar construction. Upper and lower axial struts 206A, 206B and outer ends 208 form axial elements E that are received in the spaces S between each element E of the adjacent stent segment 201.
In a preferred embodiment, a spacing member 212 extends outwardly in the axial direction from a selected number of outer circumferential struts 209 and/or connecting struts 213. Spacing member 212 preferably itself forms a subcell 214 in its interior, but alternatively may be solid without any cell or opening therein. For those spacing members 212 attached to outer circumferential struts 209, subcell 214 preferably communicates with I-shaped cell 205. Spacing members 212 are configured to engage the curved outer ends 208 of an adjacent stent segment 201 so as to maintain appropriate spacing between adjacent stent segments. In one embodiment, spacing members 212 have outer ends 216 with two spaced-apart protrusions 218 that provide a cradle-like structure to index and stabilize the curved outer end 208 of the adjacent stent segment. Preferably, spacing members 212 have an axial length of at least about 10%, more preferably at least about 25%, of the long dimension L of I-shaped cells 205, so that the I-shaped cells 205 of adjacent stent segments are spaced apart at least that distance. This results in elements E interleaving a distance of at least about 10%, preferably at least about 25%, and more preferably at least about 50% of their axial length as measured from the circumferential connecting struts 213. Because spacing members 212 experience little or no axial shortening during expansion of stent segments 201, this minimum spacing between stent segments is maintained both in the unexpanded and expanded configurations.
FIG. 20B shows stent segment 201 of FIG. 20A in an expanded configuration. It may be seen that cells 205 are expanded so that upper and lower slots 207 are diamond shaped with circumferential slots 204 remaining basically unchanged. This results in some axial shortening of the stent segment, thereby increasing the spacing between adjacent stent segments. The stent geometry is optimized by balancing the amount of axial shortening and associated inter-segment spacing, the desired degree of vessel wall coverage, the desired metal density, and other factors. Because the stent is comprised of multiple unconnected stent segments 201, any desired number from 2 up to 10 or more stent segments may be deployed simultaneously to treat lesions of any length from 2 mm up to 100 mm or more. Further, because such segments are unconnected to each other, the deployed stent structure is highly flexible and capable of deployment in long lesions having curves and other complex shapes.
As an additional feature, circumferential slots 204 provide a pathway through which vessel side branches can be accessed for catheter interventions. Should stent segment 201 be deployed at a location in which it covers the ostium of a side branch to which access is desired, a balloon dilatation catheter may be positioned through circumferential slot 204 and expanded. This deforms circumferential struts 209, 211 axially outward, thereby expanding circumferential slot 204 and further expanding upper and lower slots 207, as shown in phantom in FIG. 20B. This provides a relatively large opening 220 through which a catheter may be inserted through stent segment 201 and into the side branch for placing stents, performing angioplasty, or carrying out other interventions.
FIGS. 21A-21B illustrate a second embodiment of a stent segment 201′ according to the invention. In FIG. 21A, two stent segments 201′ are shown interleaved in a planar shape for clarity. Similar to the embodiment of FIG. 20A, stent segment 201′ comprises two parallel rows 222A, 222B of I-shaped cells 224 formed into a cylindrical shape around axial axis A. Cells 224 have upper and lower axial slots 226 and a connecting circumferential slot 228. Upper and lower axial slots 226 are bounded by upper axial struts 230, lower axial struts 232, curved outer ends 234, and curved inner ends 236, forming axial elements E configured to be received in spaces S between elements E in the adjacent stent segment 201′. Circumferential slots 228 are bounded by an outer circumferential strut 238 and inner circumferential strut 240. Each I-shaped cell 224 is connected to the adjacent I-shaped cell 224 in the same row 222 by a circumferential connecting strut 242. Row 222A is connected to row 222B by the merger or joining of curved inner ends 236 of at least one and preferably two of slots 226 in each row 222.
One of the differences between the embodiment of FIGS. 21A-21B and that of FIGS. 20A-20B is the way in which spacing is maintained between the adjacent interleaved stent segments. In place of the spacing members 212 of the earlier embodiment, the embodiment of FIG. 21A includes a bulge 244 in upper and lower axial struts 230, 232 extending circumferentially outwardly from axial slots 226. These give axial slots 226 an arrowhead or cross shape at their inner and outer ends. The bulge 244 in each upper axial strut 230 extends toward the bulge 244 in a lower axial strut 232 in the same cell 205 or in an adjacent cell 205, thus narrowing the space S therebetween and creating a concave abutment 246 in the space between each axial slot 226. Concave abutments 246 are configured to receive and engage curved outer ends 234 of cells 224 in the adjacent stent segment, thereby maintaining spacing between the stent segments. The axial location of bulges 244 along upper and lower axial struts 230, 232 may be selected to provide the desired degree of inter-segment spacing. Preferably, the axial depth of concave abutments 246 from curved outer ends 234 is at least about 10% of the axial length of elements E (measured from circumferential struts 242), preferably at least about 25% of the axial length of elements E, and more preferably at least about 50% of the axial length of elements E.
FIG. 21B shows two stent segments 201 of FIG. 21A in an expanded condition. It may be seen that axial slots 226 are deformed into a circumferentially-widened modified diamond shape with bulges 244 on the now diagonal upper and lower axial struts 230, 232. Circumferential slots 228 are generally the same size and shape as in the unexpanded configuration. Bulges 244 have been pulled away from each other to some extent, but still provide a concave abutment 246 to maintain a minimum degree of spacing between adjacent stent segments. As in the earlier embodiment, some axial shortening of each segment occurs upon expansion and stent geometry can be optimized to provide the ideal intersegment spacing.
In a preferred embodiment, stent segments 201′ retain some degree of interleaving in the expanded configuration, with outer ends 234 of elements E on adjacent stent segments being at least circumferentially aligned with each other, and preferably extending into spaces S of the adjacent stent segment a distance of at least about 1%, more preferably at least about 5%, and in some cases at least about 10% of the axial length of elements E as measured from circumferential connecting struts 242. In one exemplary embodiment, for a stent segment 201′ having an axial length of 4 mm and an unexpanded diameter of about 0.5-1.5 mm, elements E have an axial length of about 1 mm and are interleaved a distance Du of about 0.1-0.5 mm in the unexpanded configuration. Segments 201′ are expandable to a diameter of 2.5-3.5 mm and elements E are interleaved a distance De of about 0.01-0.1 mm in the expanded configuration.
It should also be noted that the embodiment of FIGS. 21A-21B retains the feature described above with respect to FIGS. 20A-20B to enable access to vessel side branches blocked by stent segment 201′. Should such side branch access be desired, a dilatation catheter may be inserted into circumferential slot 228 and expanded to provide an enlarged opening through which a side branch may be entered.
FIGS. 22A-22B illustrate a variant of the stent structure of FIGS. 21A-21B that has a larger expanded diameter. The primary difference in the embodiment of FIGS. 22A-22B is the geometry of the inner ends 236′ of each axial slot 226′. Rather than being curved, inner ends 236′ are generally straight and oriented in the circumferential direction. Because of the longer circumferential dimension of the inner ends 236′, an inner portion 250 of each axial strut 230′, 232′ is disposed at an angle relative to the axial direction, giving the inner half 252 of each axial slot 226′a trapezoidal shape. Again, bulges 244′ are disposed along axial struts 230′, 232′ so as to create concave abutments 246′ that engage the outer ends 234′ of axial slots 226′ and maintain inter-segment spacing.
As shown in FIG. 22B, stent segment 201′ expands to a configuration similar to that of FIG. 21B, with the exception that inner ends 236′ remain generally straight and aligned with the circumferential direction. Axial slots 226′ are again expanded into a modified diamond shape, with bulges 244′ extending into spaces S to maintain inter-segment spacing. In an exemplary embodiment, stent segment 201″ has a length of about 4 mm and diameter of about 1.0-2.0 mm when unexpanded, and is expandable to a diameter of about 3.0-4.0 mm.
The stent structures of the invention are preferably radiopaque so as to be visible by means of fluoroscopy. Radiopaque markers and/or materials may be used in or on the stent structures. Markers of radiopaque materials may be applied to the exterior of the stents, e.g, by applying a metal such as gold, platinum, a radiopaque polymer, or other suitable coating or mark on all or a portion of the stents. Alternatively, the stent structures may include a radiopaque cladding or coating or may be composed of radiopaque materials such as MP35N (ASTM 562), L-605 cobalt chromium (ASTM F90), other suitable alloys containing radiopaque elements, or multilayered materials having radiopaque layers. As a further option, the stent structures may have a geometry conducive to fluoroscopic visualization, such as having struts of greater thickness, sections of higher density, or overlapping struts. Some of the possible materials that may be used in the stent segments, either alone or in combination, include (by ASTM number):
- F67-00 Unalloyed Titanium
- F75-01 Cobalt-28 Chromium-6 Molybdenum Alloy
- F90-01 Wrought Cobalt-20 Chromium-15 Tungsten-10 Nickel Alloy
- F136-02a Wrought Titanium-6 Aluminum-4 Vanadium ELI Alloy
- F138-00, F139-00 Wrought 18 Chromium-14 Nickel-2.5 Molybdenum Stainless Steel Bar or Sheet
- F560-98 Unalloyed Tantalum
- F562-02 Wrought 35 Cobalt-35 Nickel-20 Chromium-10 Molybdenum Alloy
- F563-00 Wrought Cobalt-20 Nickel-20 Chromium 3.5 Molybdenum-3.5 Tungste-5 Iron Alloy
- F688 Wrought Cobalt-35 Nickel-20 Chromium-10 Molybdenum Alloy
- F745-00 18 Chromium-12.5 Nickel-2.5 Molybdenum Stainless Steel
- F799-02 Cobalt-28 Chromium-6 Molybdenum Alloy
- F961-96 Cobalt-35 Nickel-20 Chromium-10 Molybdenum Alloy
- F1058-02 Wrought 40 Cobalt-20 Chromium-16 Iron-15 Nickel-7 Molybdenum Alloy
- F1091-02 Wrought Cobalt-20 Chromium-15 Tungsten-10 Nickel Alloy
- F1108 Titanium-6 Aluminum-4 Vanadium Alloy
- F1295-01 Wrought Titanium-6 Aluminum-7 Niobium Alloy
- F1314-01 Wrought Nitrogen-strengthened 22 Chromium-13 Nickel-5 Manganese-2.5 Molybdenum Stainless Steel Alloy
- F1241-99 Unalloyed Titanium Wire
- F1350-02 Wrought 18 Chromium-14 Nickel-2.5 Molybdenum Stainless Steel Wire
- F1377-98a Cobalt-28 Chromium-6 Molybdenum Powder coating
- F1472-02a Wrought Titanium-6 Aluminum-4 Vanadium Alloy
- F1537-00 Wrought Cobalt-28 Chromium-6 Molybdenum Alloy
- F1580-01 Titanium and Titanium-6 Aluminum-4 Vanadium Alloy Powder coating
- F1586-02 Wrought Nitrogen Strengthened 21 Chromium-10 Nickel-3 Mnaganese-2.5 Molybdenum Stainless Steel Bar
- F1713-96 Wrought Titanium-13 Niobium-13 Zirconium Alloy
- F1813-01 Wrought Titanium-12 Molybdenum-6 Zirconium-2 Iron Alloy
- F2063-00 Wrought Nickel-Titanium Shape Memory Alloys
- F2066-01 Wrought Titanium-15 Molybdenum Alloy
- F2146-01 Wrought Titanium-3 Aluminum-2.5 Vanadium Alloy Seamless Tubing
- F2181-02a Wrought Stainless Steel Tubing
The preferred embodiments of the invention are described above in detail for the purpose of setting forth a complete disclosure and for the sake of explanation and clarity. Those skilled in the art will envision other modifications within the scope and sprit of the present disclosure.