Source: https://patents.google.com/patent/EP1799145B1/en
Timestamp: 2019-04-22 10:57:21+00:00

Document:
2010-06-01 First worldwide family litigation filed litigation Critical https://patents.darts-ip.com/?family=35610001&utm_source=google_patent&utm_medium=platform_link&utm_campaign=public_patent_search&patent=EP1799145(B1) "Global patent litigation dataset” by Darts-ip is licensed under a Creative Commons Attribution 4.0 International License.
Anchors are used in the treatment of patients to secure devices at a desired location within a natural bodily lumen. For example, anchors can be used to secure tubes within the digestive tract, such as intestinal sleeves. For example intestinal sleeves anchored within the gastrointestinal tract are described in U.S. application No. 10/339,786 filed on January 9, 2003 , claiming priority to U.S. Provisional Application No. 60/430,321 filed on December 2, 2002 ; 10/858,852 filed on June. 16, 2004 , claiming priority to U.S. Provisional Application Nos. 60/528,084 filed on December 9, 2003 and 60/544,527 filed on December 14, 2004 . US2004/0093065 discloses a lining for insertion into a body lumen.
This invention is generally related to articles for anchoring within a natural bodily lumen.
The present invention provides an intraluminal anchor, as defined in claim 1.
The elongated anchor, when implanted, provides at least two different radial forces at respective positions along its length. These different radial forces act differently upon respective portions of the lumen when the device is implanted therein. Namely, at least one of the radial forces is primarily a securing force adapted to anchor within the lumen. The other radial force is a transitional force adapted to mitigate damage to the lumen. Further, when implanted, the intraluminal implant defines an interior lumen allowing for continued functioning of the natural bodily lumen.
The elongated anchor can include plural anchoring elements each providing a respective radial force, at least one of the elements providing a different radial force from the others. By positioning each of the plural anchoring elements at a respective position along the length of the intraluminal anchor, the respective radial forces, including the different radial force, are disposed at different lengths along the lumen.
To further enhance its anchoring performance, the intraluminal anchor includes at least one external barb adapted to penetrate tissue of the natural bodily lumen. The external barb is located at a predetermined position along the length of the intraluminal anchor, the corresponding radial force acting to press the barb into the tissue. For example, in a multi-anchoring element embodiment, the at least one external barb is coupled to one of the anchoring elements. The force of the coupled anchoring element then acts to hold the barb within the tissue.
In some embodiments, the external barb can be a bi-directional barb. Bi-directional barbs are particularly well suited for applications in which the intraluminal anchor is subjected to external forces acting in either direction along the lumen. Generally, the bi-directional barb includes a first barb segment adapted to oppose proximal movement and a second barb segment adapted to oppose distal movement. Such barbs are well suited to gastrointestinal applications in which the device is subjected to the substantial axial forces of peristalsis.
Preferably, the anchor is radially collapsible for endoscopic insertion. The intraluminal anchor can also include a drawstring to facilitate repositioning and/or removal. The drawstring, for example, can be provided at a proximal end of the device and be adapted for engagement by a removal device, such as a hook. The drawstring, when engaged, can be pushed or pulled by the removal device, in opposition to the stationary intraluminal anchor, to at least partially collapse at least part of the intraluminal anchor. With a reduced diameter, the device can be removed through, or repositioned within, the lumen. In some embodiments, at least a portion of the device is drawn into a retrieval hood, sheath, or overtube prior to removal.
The intraluminal anchor is coupled to an elongated tube at a proximal end of the tube, the tube being adapted to extend distally within the intestinal lumen. The elongated anchor can be coupled to the elongated tube in any of a number of different ways. For example, the anchor can be mechanically fastened using sutures, staples, or the like. Alternatively or in addition, the anchor can be bonded to the tube, using a chemical adhesive and/or heat welding. In some embodiments the tube is thin walled and flexible. For example, the tube can be formed as a sleeve having extremely thin and floppy walls, the sleeve tending to collapse upon itself. The anchor can be secured between at least two overlapping layers of the sleeve. The overlapping layers can then be attached to each other using any available fastening technique including bonding together at least a portion of the overlapping layers of the sleeve.
In other embodiments, the elongated anchor can be formed from a homogeneous hollow tube. The thickness of the tube can be altered (i.e., tapered) along the length of the tube, such that different portions of the tube provide different spring forces. When implanted within a naturally bodily lumen, the tapered tube provides different forces along its length and therefore different forces along the bodily lumen according to the thickness of the tube. In some embodiments, the tapered tube can be further modified using known techniques (e.g., laser cutting) to promote radial expansion and contraction of the device.
Figures 2 to 6 and 9 do not show embodiments of the invention.
FIG. 1B is a schematic diagram illustrating an example of an intraluminal anchor according to the principles of the invention implanted within a natural bodily lumen.
FIG. 2 is a schematic diagram illustrating an example of an intraluminal anchor.
FIG. 3 is a schematic diagram illustrating an example of a bendable, intraluminal anchor.
FIG. 4A is a schematic diagram illustrating an alternative example of the intraluminal anchor shown in FIG. 1.
FIGS. 5A and 5B are schematic diagrams illustrating alternative example of the intraluminal anchor shown in FIG. 2 having cross-linking members.
FIG. 6 is a schematic diagram illustrating an alternative example of the intraluminal anchor shown in FIG. 4A having multiple coupled wave elements.
Fig. 9A is a schematic diagram illustrating an example of a shaped tube.
Fig. 9B is a schematic diagram illustrating an example of an intraluminal anchor formed from the shaped tube shown in Fig. 9A.
A cross-section of a natural bodily lumen 20 including an anchor 10b' is illustrated in Fig. 1A. Generally, the lumen defines a natural diameter, D1, that may vary over time. The anchor provides a radially-outward securing force directed against the luminal walls. Depending upon the structure of the anchor 10b' and the compliance of the luminal walls, the anchor 10b' when implanted can increase the intraluminal diameter (i.e., D2) as shown. The sharp transition from the anchored region to the unsupported adjacent region applies a strain to the tissue, particularly at the ends of the anchor 25. As shown, tissue stretching can occur over a first distance Δ1. Such a strain can lead to irritation of the tissue or even damage over time.
To offset the possibility of damage due to the securing force, the anchor also provides a transitional force that is different from the securing force and acts upon an adjacent region of the surrounding anatomy. As shown in FIG. 1B, an anchor 10b" providing a securing force is surrounded on either side by another anchoring element 10a", 10c" providing a lesser, transitional force. The transitional force allows for a more gradual decrease in anchoring force from a central region along the length of the anchor and thus less trauma. Thus, the transition from an expanded diameter D2 to the natural luminal diameter D1 occurs over a second distance [Delta]2, that is greater than first distance [Delta] 1. By transitioning from unsupported tissue to anchored tissue using a softer anchoring element, the strain to the tissue is reduced, thereby reducing the likelihood of tissue irrigation and damage.
By applying different forces at different lengths along the natural bodily lumen, the securing force can be applied, or focused where needed, while the transitional force can distribute the pressure loading to the surrounding anatomy. In particular, the transitional force is a lesser force than the securing force, providing a gradual transition from the luminal region subjected to the securing force, to adjacent, unsupported luminal regions. The anchor is used in combination with a tube, such as a gastrointestinal sleeve, to secure the tube at a predetermined location within the bodily lumen.
FIG. 2 schematically illustrates an exemplary example of an intraluminal anchor 100. The anchor 100 has an overall axial-length 'L' measured length-wise with respect to the lumen and defines an interior channel 115 configured to allow continued operation of the lumen when implanted therein. For example, the anchor 100 can have a generally cylindrical shape, having a length 'L', a diameter 'D', and defining an interior channel 115. When implanted, the anchor provides a radially-outward spring force directed against the adjacent walls of the natural bodily lumen (i.e., the anchor includes an annular, radial spring providing a force corresponding to a displacement of the spring along its radius). The radial force includes a securing force, sufficient to secure the anchor 100 in place under anticipated bodily forces. In particular, the outward radial force is varied along the length of the anchor to provide a transitional force, reducing the likelihood of damage to surrounding tissue. When implanted within a natural bodily lumen, the anchor provides a transition along the lumen from soft tissue, to a low compliance region (i.e., transitional force), to a higher compliance region (i.e., securing force), again to a low compliance region, and ultimately back to unsupported, soft tissue.
Generally, the anchor includes a spring providing the desired securing force. The force produced by the spring is defined by an associated spring rate relating to its compliance or stiffness. The spring rate can be determined by one or more anchor features including its type of material, material thickness, dimensions, and shape. As a radial spring, a greater force results from a greater radial displacement. For intraluminal applications, such a radial spring preferably has a relaxed diameter (i.e., no load diameter) that is greater than the largest anticipated intraluminal diameter. Thus, the implanted anchor is always subjected to a compressive force causing radial compression and leading to an opposing securing force. Compliant anchors are described in U.S. application No. 11/147,992 filed on June 8, 2005 .
The anchor remains sufficiently compliant, when implanted, to conform to the walls of the lumen over a full range of motion. For example, an anchor implanted within the proximal duodenum of an adult human may experience intraluminal diameter variations from about 25-millimeters or less, to greater than 50-millimeters.
As suggested by FIG. 2, the anchor 100 can provide a varied force by using plural anchoring elements. For example, the anchor 100 can include three or more different anchoring elements 110a, 110b and 110c (generally 110), as shown. Each of the anchoring elements 110a, 110b and 110c can be annular, as shown, and occupy a respective axial sub-length '11,' '12,' and '13.' Further, each of the anchoring elements 110 can be separated from its neighboring anchoring element by a respective distance 's1,' 's2.' In some embodiments, the one or more of the distances can be negative, suggesting that the elements overlap. The overall length of the anchor 100 is determined as the sum of the sub-lengths of the anchoring elements and any distances provided therebetween. Each of the annular anchoring elements 110 can be sized and shaped to conform to the walls of the surrounding lumen with its opening collinearly aligned with a luminal axis.
In some examples, the anchoring elements 110 are coupled together using a respective cross-linking, or joining member 120a, 120b (generally 120), as shown. The joining member 120 can be a rigid member or strut, such as a wire or rod. Use of rigid struts can reduce or substantially eliminate axial compression of the device. Alternatively or in addition, the joining member 120 can be flexible, such as a wire, tape, or thread (e.g., a suture). Such flexible members can permit axial compression but not expansion, so the length can be less than or equal to a maximum length. If axial compression and expansion is desired, the joining members 120 can include elastic elements. Such flexibility can be beneficial to both patient comfort and anchoring effectiveness. In some embodiments, the joining members 120 are formed integrally to the anchoring elements 110 themselves.
An example of a flexible elongated anchor 200 is illustrated in Fig. 3. The elongated anchor 200 can include more than one anchoring element 210a, 210b, 210c, each capable of independent movement with respect to the other elements. The anchor 200 may include joining members 220a, 220b, but they are selected and positioned to allow a desired flexibility. For example, rigid joining members can be aligned along one side of the anchor 200, allowing the anchor to bend towards that side.
An alternative example of an intraluminal anchor 300 is illustrated in Fig. 4A. The anchor 300 includes multiple anchoring elements 310a, 310b, 310c in a collinear arrangement with adjacent elements 310 abutting. A corresponding force-versus-distance graph for the anchor 300 is illustrated in Fig. 4B. In particular, the graph illustrates the different radially-outward forces provided by each of the anchoring elements 310 (Fig. 4A) versus its respective distance as measured along a central axis of the anchor 300. As shown for the exemplary embodiment of Fig. 4A, the greater radial force is provided by the central element 310b, having a representative force of F2. The corresponding force can be substantially constant across the axial length subtended by the second anchoring element 310b (i.e., from L/3 to 2L/3, assuming all three elements are of equal length L/3). Similarly, forces F1 and F3 provided by the adjacent first and third anchoring elements 310a, 310c are lesser forces, as shown in the graph (e.g., at region 320). The greater force F2 corresponds to a securing force to hold the anchor in place when implanted; whereas, the lesser forces F1 and F3 correspond to transitional forces lessening the likelihood of damage to surrounding tissue.
In some example, however, the structure of the anchoring elements 310 allows the elements to provide different forces along their respective sub-lengths. As the anchoring elements 310 are radial springs, they have an associated spring constant. The radial force provided by the anchoring element 310 is thus a result of the spring constant and the amount of radial compression. Anchoring element configurations that allow for varied compression along the anchor sub-length will lead to a corresponding varied radial force. For example, if the outer anchoring elements 310a, 310c are each coupled at one end to the central anchoring element 310b, they may have a different diameter on each end. As the central anchoring element 310b is stiffer, it may have a greater diameter than a less stiff element. In general, there is no limit to the number of anchoring elements that can be provided or to the particular stiffness profile desired.
The securing force produced by the anchor can include a radial component directed outward and pressing against the walls of the surrounding lumen. The securing force also includes an axial component provided by a barb (not shown in all Figs.). The magnitude of the securing force preferably depends on the intended application being selected to sufficiently secure the anchor without being excessive. Limiting the maximum force is important as substantial forces acting against the luminal walls are more apt to traumatize the surrounding tissue.
In some example, the radially-outward force of an anchor is varied by varying the stiffness (or compliance) of the anchor along its length. Such a feature provides for greater flexibility in tailoring the anchor to its intended delivery location. For example, the thickness of the anchor member can be varied to control the desired stiffness, such that a portion of the anchor is relatively stiff, whereas another portion of the anchor is relatively soft. In this manner, the stiffer portion of the anchor can be used to distend that portion of the bodily lumen within which it is implanted. To reduce irritation, the stiffness is then reduced towards the proximal and distal ends of the anchor to reduce any trauma to the tissue of the bodily lumen.
For example, a side view of a flexible intraluminal anchor 400' is illustrated in FIG. 5A. By using different anchoring elements 410a', 410b', 410c', interconnected by joining members 420a', 420b'(generally 420') as shown, the anchor 400' is allowed to flex and bend. The joining members 420' are not necessary for embodiments in which the elements 410 are each coupled to the same tube or sleeve. The anchoring elements 410' are each formed from a respective continuous wire fashioned into the oscillating, wave-shaped pattern shown. Viewed along an axis (not shown), the anchor 400' would appear as an open circle or hoop. Wave-shaped anchors and related matters are described in U.S. application No. 10/858,852 filed on June 1, 2004 and claiming priority to U.S. Provisional Application Nos. 60/528,084 filed on December 9, 2003 and 60/544,527 filed on December 13, 2004 .
In one example the central anchoring element 410b' is formed from a relatively thick wire, such as a 0.58mm (0.023 inch) diameter Nitinol wire. The additional anchoring elements 410a', 410c' are formed from a thinner wire, such as a 0.36mm (0.014 inch) diameter Nitinol wire. Using wires formed from the same material, the thicker wire results in a greater stiffness than the thinner wire. Thus, the central anchoring 410b' element provides a greater radially-outward force when compressed than either of the two surrounding anchoring elements 410a', 410c'. The spring rate can also be varied by altering the axial length of a wave-shaped anchoring element, shorter elements being stiffer than longer ones. Also, the spring rate can be varied by altering the number of oscillations for a give anchoring element, elements with more oscillations being stiffer.
The wires can be formed from any suitable material, such as metals, metal alloys (e.g., stainless steel and Nitinol), and/or synthetic materials (e.g., plastic). Preferably, the material is bio-compatible, although it is possible to use non bio-compatible material that is coated or encapsulated in a bio-compatible material. Anchoring can be accomplished using an interference fit between the intraluminal anchor and the inner walls of the lumen. In addition, anchoring is accomplished using at least one barb. In the exemplary embodiment, at least one external barb 425' is attached to the central anchoring element 410b'. When implanted, the barb 425' is held in place within muscular tissue by the stiffness and corresponding radially-outward force of the 0.58mm (0.023 inch) diameter wire. The central anchor element 410b provides a substantial force to keep the barb 425' inserted into the surrounding tissue. Without the first and third anchoring elements 410a', 410c', the securing force provided by the middle anchoring element 410b' could lead to tissue irritation or even damage at the ends of the element 410b'.
The anchoring elements described above can be formed into any number of different shapes. In some example, each of the anchoring elements is formed in a wave shape. Thus, a linear element (i.e., a wire) is contoured into an oscillating manner along a cylindrical surface at a distance (i.e., a radius) from a central axis. Such a wire form can be shaped on a cylindrical mandrel. The two ends of the wire are joined together (e.g., crimped, soldered, or chemically or thermally bonded) forming a continuous structure. An anchoring element thus formed provides a relatively small surface area in contact with the natural bodily lumen, while allowing the anchor to provide a relatively large diameter (e.g., 25 to 50 or more millimeters for gastrointestinal applications). The oscillations result in relatively straight segments 412a, 412b (generally 412) interconnected at nodes 414a, 414b (generally 414). When compressed in a radial direction, the nodes 414 flex allowing the relatively straight segments 412 to become more aligned with respect to each other. Thus, the diameter of the anchor 400' can be reduced substantially to allow for its insertion and/or removal through a relatively small diameter. For example, in some intestinal applications, a 50-millimeter diameter device is adapted to be inserted through a 12-millimeter diameter catheter. When released, the anchor 400' expands with spring force against the walls of the bodily lumen.
The anchoring elements 410a', 410b', 410c' may be separated by respective distances S1, S2 as shown, or one or more of the elements may be adjacent or even overlapping. An alternative example of a wave-shaped wire anchor 400" is illustrated in Fig. 5B. The anchoring 400" also includes multiple anchoring elements 410a", 410b", 410c" that may or may not be interconnected by joining members 420a", 420b". As shown, one or more of the anchoring elements 410a", 410b", 410c" can overlap another anchor element to varying degrees. At least one advantage of such an overlap is a reduction in the overall length of the anchor 400". Such an overlap can also be used to achieve a desired force-versus-distance profile of the anchor 400", leading to a more gradual transition of the forces distributed along the axis.
A side view of an alternative example of an intraluminal anchor 500 is illustrated in FIG. 6. The anchor 500 includes multiple anchoring elements 510a, 510b, 510c, again shown as wave-shaped elements for illustrative purposes, that are interconnected to each other. The anchoring elements 510a, 510b, 510c can be interconnected by mechanical fasteners, chemical adhesives, thermal bonding, welding, soldering, and/or weaving. The interconnection may be fixed, or in the case of a weave, capable of longitudinal compression.
As described above, the intraluminal anchor can be used to anchor an elongated tube within a natural bodily lumen. An exemplary device 600 including an intraluminal anchor, similar to the one described above in reference to FIG. 5A, and coupled to the proximal end of an elongated tube 615 is illustrated in FIG. 7. The tube 615 may be rigid, semi-rigid or flexible. Gastrointestinal sleeves and related matters are described in U.S. application No. 10/339,786, filed January 9, 2003 , which claims the benefit of U.S. Provisional Application No. 60/430,321, filed December 2, 2002 ; and U.S. application No. 10/726,011, filed on December 2, 2003 , which claims the benefit of U.S. Provisional Application No. 60/512,145 filed October 17, 2003 .
The anchoring elements 610a, 610b, 610c (generally 610) can be bonded to the tube (e.g., chemically bonded using an adhesive, or thermally bonded). The anchoring elements 610 can also be mechanically coupled to the elongated tube 615. For example, the anchoring elements 610 can be coupled using a suture, a surgical staple, and/or by threading the anchoring element itself through perforations in the elongated tube.
In some embodiments, the anchoring elements 610 are encapsulated within the elongated tube 615. For example, the elongated tube 615 can be formed as a sleeve. A portion the sleeve can then be used to encapsulate the anchoring elements by folding one end of the sleeve back upon itself to cover both the interior and exterior of the anchoring elements 610. The portions of the elongated tube forming the overlapping portion 617 can then be coupled together, thereby capturing the anchoring elements 610 and securing them in place with respect to each other and with respect to the elongated tube 615. For example, the overlapping portions 617 of the tube 615 can be bonded together (e.g., chemically bonded using an adhesive, or thermally bonded). Alternatively or in addition, the overlapping portions 617 of the tube 615 can be mechanically fastened together. For example, the overlapping portions 617 of the elongated tube 615 can be coupled together using sutures, staples, clasps, or any other suitable mechanical fastener.
As shown, the anchor 600 includes barbs 620 that protrude externally from the anchor 600 to penetrate the surrounding tissue. For illustrative purposes, the device 600 as implanted within a portion of an animal's intestine 630 illustrated in cross section. Shown are the intestinal wall 630 including an inner mucosal layer 632 in communication with the anchor 600 and a surrounding layer of muscular tissue 634. The barbs 620 are adapted to penetrate the mucosal layer 632 and into the muscular tissue 634 of the intestine 630. In some embodiments, the barbs 620 actually penetrate the outer walls of the intestine 630. Thus, the barbs 620 provide an axial securing force component, with the anchoring element 610b providing a securing force adapted to maintain the barbs into engagement with the muscular tissue 634.
To ensure that the barbs 620 remain secured to the muscular tissue during implantation, the anchoring element to which the barbs 620 are coupled should be relatively stiff. Thus, the stiffness of the supporting anchoring element 610b maintains a radial force ensuring that the barbs 620 are driven into the tissue. In some embodiments, the stiffness is sufficient to force the supporting anchoring element 610b through the mucosal layer 632, abutting it to the layer of muscular tissue 634.
In some applications, however, the stiffness of the anchoring element 610b can lead to irritation and possibly damage to the surrounding tissue. To reduce the possibility of such irritation or damage, additional anchoring elements 610a, 610c are provided on either side of the anchoring element 610b. Preferably, the additional anchoring elements 610a, 610c are less stiff (i.e., softer) than the central anchoring element 610b. In this manner, the transition between unanchored portions of the lumen and the stiff anchoring element 610b is spread over a larger surface area to achieve the desired anchoring force at the barbs 620 in a gradual manner. Thus, the additional anchoring elements 610a, 610c provide a strain relief on both sides of the stiff anchoring element 610b to minimize trauma to the tissue, as shown in Fig. 1B.
As described above in reference to wire anchoring elements, the radial force, or stiffness can be controlled by varying a physical property of the anchoring element. This approach can also be extended beyond wire examples. For example, the elongated anchoring element can be formed from a tapered tube. To vary the radial force, or stiffness, the tube can be shaped to vary its wall thickness. The axial taper can be accomplished by injection moulding to a desired shape and/or by removing material from a solid elongated tube. The result in either case is an anchoring element having differing thicknesses along its central axis. Figure 9A illustrates a cross-sectional view of an exemplary tube 800 after having both ends tapered from a thicker middle section. Thus, the thinner ends 810 are achieved by removing extra material 820. For example, a stainless steel or alloy (e.g., Nitinol) tube 800 can be shaped by grinding it and/or turning it on a lathe to selectably remove material along its length. As shown, the tube 800 can be tapered from a relatively thick portion along the tube middle, to a relatively thin portion at the tube's ends (with this approach, any conceivable profile is possible).
While this invention has been particularly shown and described with references to preferred embodiments thereof, it will be understood by those skilled in the art that various changes in form and details may be made therein without departing from the scope of the invention encompassed by the appended claim.
wherein the elongated anchor remains sufficiently compliant, when implanted, to conform to the walls of the intestinal lumen over a full range of motion, and is adapted to experience intraluminal diameter variations from 25 millimeters or less to greater than 50 millimeters.
The intraluminal anchor (610) of claim 1 wherein the elongated anchor comprises a plurality of anchoring elements (610), at least one (610b) of the anchoring elements (610) relating to the primary anchoring region and at least two other (610a,610c) of the anchoring elements (610) relating to the secondary anchoring regions.
The intraluminal anchor (610) of claim 2, wherein the anchoring element (610b) relating to the primary anchoring region and the at least two other (610a,610c) of the anchoring elements (610) relating to the secondary anchoring regions comprise different materials.
The intraluminal anchor (610) of claim 2, wherein the anchoring element (610b) relating to the primary anchoring region and the at least two other (610a,610c) of the anchoring elements (610) relating to the secondary anchoring regions comprise substantially the same material having a different thickness.
The intraluminal anchor (610) of claim 2, wherein the at least one of the plurality of anchoring elements (610) is formed from an elongated wire.
The intraluminal anchor (610) of claim 2, wherein at least one of the plurality of anchoring elements (610) is a wave-shaped element.
The intraluminal anchor (610) of claim 2, wherein the at least one (610b) of the plurality of anchoring elements (610) comprises the at least one external barb (620) in the primary anchoring region adapted to penetrate muscular tissue of the intestinal lumen, the respective anchoring element (610b) expanding against the lumen and adapted to hold the barb (620) within the muscular tissue.
The intraluminal anchor (610) of claim 7, wherein the external barb (620) is a bi-directional barb, comprising a first barb segment adapted to oppose proximal movement and a second barb segment adapted to oppose distal movement.
The intraluminal anchor (610) of claim 2, further comprising at least one joining member coupled between at least two of the plurality of anchoring elements (610).
The intraluminal anchor (610) of claim 1, wherein the elongated anchor is adapted to be anchored in the proximal duodenum, the tube (615) extending distally within the intestine.
The intraluminal anchor (610) of claim 10, wherein the elongated tube (615) is thin-walled, collapsing upon itself.
The intraluminal anchor (610) of claim 1, wherein the external barb (620) is a bi-directional barb, comprising a first barb segment adapted to oppose proximal movement and a second barb segment adapted to oppose distal movement.
The intraluminal anchor (610) of claim 1, wherein the elongated tube (615) is thin-walled, collapsing upon itself.
The intraluminal anchor (610) of claim 1, wherein the elongated anchoring element is coupled to the tube (615) between overlapping layers (617) of the tube (615).
The intraluminal anchor (610) of claim 1, wherein the anchor is radially collapsible for endoscopic insertion.
The intraluminal anchor (610) of claim 1, wherein the elongated anchor is formed from a homogeneous hollow tube having a tube wall of differing thickness along its length, the tube wall defining apertures adapted to allow radial variation of the tube.
The intraluminal anchor (610) of claim 1, wherein the primary and secondary anchoring regions comprise different spring rates.
The intraluminal anchor (610) of claim 1, wherein the primary anchoring region is central.
ES2293653T3 (en) 2008-03-16 Graft stent kink resistant.
Owner name: GI DYNAMICS, INC.

References: application No. 10
 Application No. 60
 application No. 11
 application No. 10
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 Application No. 60
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 Application No. 60