Source: https://patents.google.com/patent/ES2586111T3/en
Timestamp: 2020-01-20 18:07:07
Document Index: 314240690

Matched Legal Cases: ['art 90', 'art 80', 'art 90', 'art 80', 'art 90', 'art 90', 'art 40', 'art 90', 'art 80', 'art 90', 'art 40', 'art 80', 'art 90', 'art 40', 'art 90', 'art 90', 'art 90', 'art 90', 'arts 255', 'art 261', 'art 261', 'art 270', 'art 402']

ES2586111T3 - Collapsible and re-expandable prosthetic heart valve sleeve designs and complementary technological applications - Google Patents
Collapsible and re-expandable prosthetic heart valve sleeve designs and complementary technological applications Download PDF
ES2586111T3
ES2586111T3 ES14180622.4T ES14180622T ES2586111T3 ES 2586111 T3 ES2586111 T3 ES 2586111T3 ES 14180622 T ES14180622 T ES 14180622T ES 2586111 T3 ES2586111 T3 ES 2586111T3
ES14180622.4T
Paul E. Ashworth
Julia A. Neumann
2008-07-15 Priority to US13499508P priority Critical
2008-07-15 Priority to US134995P priority
2009-07-15 Application filed by St Jude Medical AB, St Jude Medical LLC filed Critical St Jude Medical AB
2016-10-11 Publication of ES2586111T3 publication Critical patent/ES2586111T3/en
2017-01-04 First worldwide family litigation filed litigation Critical https://patents.darts-ip.com/?family=41259553&utm_source=google_patent&utm_medium=platform_link&utm_campaign=public_patent_search&patent=ES2586111(T3) "Global patent litigation dataset” by Darts-ip is licensed under a Creative Commons Attribution 4.0 International License.
A prosthetic heart valve (100), comprising: (a) a collapsible stent (10) for mounting on an administration and expandable device when implanted, which includes a generally tubular ring region (30) having a proximal axis. distal (14) when implanted; (b) a valve element (70) mounted inside the stent and operative when implanted, to allow flow in anterograde direction (D) through the ring region from a proximal end to a distal end; characterized by (c) a sleeve (200) mounted on the stent, the sleeve including an inner wall, an outer wall outside the inner wall and outside the stent, and at least one pocket, the outer wall being arranged around the periphery of the ring region and having an edge oriented in the anterograde direction, where each pocket of the at least one pocket has an opening oriented in the anterograde direction when implanted cooperatively, defined by the inner wall and the edge of the outer wall, and the at least one pocket has a size and shape to fill with blood with blood flow around the outside of the stent in retrograde direction to predispose the outer wall to the coupling with a native valve ring to prevent perivalvular leakage.
Collapsible and re-expandable cuff designs of prosthetic heart valve and complementary technological applications
Cross reference with related requests Field of the invention
The invention is related to a device as described in claims 1 to 7. To the extent that the terms "invention" and / or "embodiment" are then used, and / or features are presented as optional, this should be construed as such that the only protection sought is that of the invention as claimed. Methods for treating patients are simply described as examples to understand the invention.
Certain prosthetic heart valves incorporate an expandable stent body and valve elements such as prosthetic valve leaflets mounted on the stent body. The prosthetic valve may also include a sleeve that includes one or more layers of materials such as fabric or animal tissue. Valves of this type can be implanted in the heart by advancing the valve within the patient's body with the stent body and the cuff in a collapsed state in which the stent body and the cuff have a relatively small diameter. Once the valve is placed at the desired implantation site, the stent body is brought to an expanded state in which a part of the stent body has a generally tubular shape. This part is coupled to the surrounding native tissue and holds the valve in place. The sleeve forms a lining that covers all or part of the tubular stent body. The valve acts as a functional substitution for the diseased native valve. Thus, the valve elements within the body of the stent allow the blood flow in the anterograde direction but substantially block the flow in the opposite retrograde direction. For example, a prosthetic valve can be advanced to a place within a native aortic valve percutaneously ill through the arterial system and into the aorta to the native aortic valve. In a transapical placement, a prosthetic valve can be advanced through an incision in the vertex of the heart and through the left vent to the native aortic valve. Other approaches can be used through other places of access. Once the prosthetic valve is in place, it allows flow from the left ventricle to the aorta when the left vent contracts during the sfstole, but substantially blocks the retrograde flow from the aorta to the left vent during diastole.
There are significant challenges in the design of an expandable valve. For example, the valve may desirably collapse to a relatively small diameter to facilitate advancement within the body. This imposes significant limitations on the sleeve design, such as the thickness of the material that can be incorporated into the sleeve. However, the stent body must be able to expand to an expanded operational state in which the stent body is securely coupled to surrounding native tissues to hold the valve in place. The stent body and the sleeve carried on the stent body should form a good seal with the surrounding native tissues to prevent leaks around the outside of the prosthetic valve, commonly referred to as perivalvular leakage. However, the stent body and sleeve should not apply excessive forces to the ring of the native valve. Excessive forces in the ring of the native aortic valve can disturb the heart's electrical conduction system and also impair the functioning of the mitral valve. These issues are complicated by the fact that native valve leaflets and other diseased tissues may present an implantation site that is irregular. For example, patients with stenotic or calcified aortic valves cannot be treated well with current collapsible valve designs, and may encounter problems such as (1) perivalvular leak (PV leak), (2) valve migration, (3) compression mitral valve, (4) conduction system disturbance, etc., all of which can lead to adverse weather outcomes. To reduce these adverse events, the optimal valve must be properly sealed and anchored without the need for excessive radial force that could damage the nearby anatoirna and physiology.
Numerous designs of prosthetic valve and stent body have been proposed. However, despite all the attention devoted to such designs, further improvements are still desirable.
US2005 / 0283231 describes methods and apparatus for endovascularly replacing a patient's heart valves. The apparatus includes a replacement valve and an expandable hook configured for endovascular administration in the immediate vicinity of the patient's heart valve.
Brief compendium of the invention
One aspect of the present invention provides a prosthetic heart valve according to claim 1 and a set according to claim 7.
The present invention can be more fully appreciated with reference to the following detailed description, which in turn refers to the drawings, wherein:
Figure 1 is a schematic section representation of an aortic root anatoirna;
Figure 2 is a perspective view of a part of a stent body used in an embodiment of the present invention;
Figure 3 is a partial elevational view of a valve according to an embodiment of the present invention;
Figure 4 is an end view of the valve shown in Figure 3;
Figure 5 is a fragmentary schematic sectional view depicting parts of the valve of Figures 3 and 4
in an implanted state, along with parts of the native tissue;
Figure 6 is a view similar to Figure 5 depicting the valve of Figures 3 and 4 in a different implanted state;
Figure 7 is a fragmentary schematic elevational view of a part of a valve according to a further embodiment of the invention;
Figure 8 is a fragmentary schematic perspective view depicting parts of a valve according to even another embodiment of the present invention;
Figure 9 is a schematic perspective view of a valve according to another embodiment of the invention;
Figure 10 is a schematic perspective view of a valve according to a further embodiment of the invention;
Figure 11 is a schematic sectional view depicting parts of a valve according to even another embodiment of the invention;
Figure 12 is a fragmentary perspective view showing elements of the valve represented in Figure 11;
Figure 13 is a schematic perspective view of an element for use in a further embodiment of the present invention;
Figure 14 is a schematic end view of a structure used in even another embodiment of the present invention;
Figure 15 is a partially sectioned view of a valve according to even another embodiment of the present invention;
Figure 16 is a view similar to Figure 15 but depicting a valve according to a still further embodiment of the present invention;
Figure 17 is a perspective view of a sleeve for use in a valve according to a further embodiment of the present invention;
Figure 18 is a perspective view of a valve incorporating the sleeve of Figure 17;
Figure 19 is a perspective view of another sleeve for use in a valve according to even another embodiment of the present invention;
Figure 20 is a perspective view of a valve invention using the sleeve of Figure 19;
Figure 21 is a schematic and fragmentary elevation view of a collapsed configuration of a valve according to a further embodiment of the present invention;
Figure 22 is a schematic view of the valve of Figure 21 in a different operating state;
Figure 23 is a schematic view partially in section of a valve according to another embodiment of the present invention;
Figure 24 is a fragmentary schematic view of a valve according to another embodiment of the present invention;
Figure 25 is a schematic elevational and partial view of a valve according to a still further embodiment of the present invention;
Figure 26 is a schematic view of a valve according to an embodiment of the present invention in an implanted state, together with native tissues;
Figure 27 is a schematic schematic and fragmentary elevation view of a valve according to even another embodiment of the present invention;
Figure 28 is a schematic view of a valve of Figure 27 in an implanted state, together with native tissue;
Fig. 29 is a schematic and fragmentary elevation view of a valve according to a still further embodiment of the present invention;
Figure 30 is a fragmentary schematic view of a part of the valve of Figure 30 in a different operating state;
Figure 31 is a schematic view of the valve of Figures 29 and 30 in an implanted state, together with native tissue;
Figure 32 is a view similar to Figure 31 but depicting a valve according to a further embodiment of the present invention;
Figure 33 is a schematic and fragmentary sectional view showing a valve according to even another embodiment of the present invention; Y
Figure 34 is a partial side elevation view of a valve according to a further embodiment of the present invention.
Figure 1 is a simplified view of the geometna or anatoirna of the aortic root tissue in a typical human heart. The outflow tract of the left ventnulum (LVOT) 1 communicates with the ascending aorta 5 through the ring 2 of the native aortic valve and the sinus of Valsalva 3. The sinus meets the aorta in the sinotubular junction (STJ) 4. The native aortic valve typically includes three leaflets 6 of the native valve, of which only two are visible in Figure 1. When the left ventricle contracts during sfstole, blood is forced from the LVOT 1 through the native valve and the sinus and inside of the aorta 5, moving generally in the direction of flow downstream or anterograde indicated by the arrow D. Each native valve valve has an inner surface 7 generally oriented proximally and generally inward, towards the other valves of a native valve, and has an opposite surface oriented opposite 8. In a healthy individual, the valves 6 of the native valve open away from each other and move to the position shown schematically in the line s discontinuous at 6 'to allow flow in this direction. During diastole, when the vent is not contracting, the valves 6 of the native valve return to the position indicated in continuous lines in Figure 1, where they bump between sf or "coaptan" to substantially block the flow in retrograde or upstream direction , opposite arrow D. The "distal" sense as used herein with reference to a characteristic of the native circulatory system refers to the direction of anterograde flow, that is, the predominant sense of blood flow through said characteristic , as indicated by arrow D. The "proximal" sense as used herein with reference to a characteristic of the native circulatory system is the opposite direction.
The parameters identified in Figure 1 are as follows: OD = orifice diameter, that is, the inner diameter of the native ring 2; DA = the diameter of the aorta just distal to the sinus; DB = maximum projected sinus diameter (this breast is sometimes known as the Valsalva sine); LA = sinus length, that is, the dimension distally from ring 2 to the sinotubular junction 4; and LB = distal distance between OD and DB.
The leaflets 6 have distal ridges 9 at a distance from the ring 2. Each native leaflet 6 has a surface 7, referred to herein as the "inner" surface of the leaflet, generally oriented towards the other leaflets. Each native leaflet 6 also has a surface 8, referred to herein as the "outer" surface of the leaflet, oriented outward, away from the other leaflets and towards the sinus wall 3. The cross-sectional shape of a native valve something of this type varies from one individual to another, and this variation can be increased by various types of disease. For example, a disease can reform the cross-section of a patient's valve to a circular, triangular or elliptical shape, depending on the disease state.
An expandable stent body 10 (Figure 2) for a prosthetic heart valve according to an embodiment of the present invention is formed as a unitary structure, for example, by laser cutting or chemical attack of a tube of a superelastic metal alloy such as nickel-titanium alloy of the type sold under the designation NITINOL. A unitary structure of this type can also be referred to as a "nonwoven" structure, because it is not formed by interlacing or winding one or more filaments. In the fully expanded unstretched configuration shown in Figure 2, the stent body 10 includes a ring section 30, an aorta section 20 and support struts 60 that extend between the ring section and the aorta section. The ring section 30 in the expanded configuration is generally in the form of a cylindrical tube having a central axis 14, while the aorta section 20 is generally in the form of a coaxial ring with the ring section. In the expanded configuration, the ring section has a substantially constant diameter except that the ring section has a flared region 40 at one end. The tubular ring section 30 has a wall formed by numerous interconnected cell struts to form a plurality of cells. The aorta section 20 is defined by a similar wall formed of multiple cells, each of which includes a plurality of interconnected cell struts.
The stent body is adapted for installation in the body of a patient with the ring section adjacent to ring 2 (Figure 1) and with the aorta section 20 adjacent to the sinotubular junction 4 and aorta 5. Thus, when the valve that incorporating the stent body is placed in the patient, the aorta section 20 will be disposed distal to the ring section 30 in the reference frame of the patient's circulatory system. Therefore, as used with reference to features of the stent body and the valve, the direction D (Figure 2) along the axis 14 from the flared region 40 of the ring section 30 through the ring section and from the ring section to the aorta section 20 it is referred to as the distal direction, and the opposite direction is taken as the proximal direction. In other words, the distal direction along the body of the stent is the direction from the end of the stent that is intended for disposition in a proximal location in the reference frame of the circulatory system to the end of the stent that is intended for disposition in a more distal location in the reference frame of the circulatory system. The "axial" senses as they are referred to herein are the proximal and distal senses. In addition, the outward direction as used with reference to the valve is the sense moving away from the proximal-to-distal axis 14. As used with reference to valve features, the "circumferential" senses are the senses around the axis 14.
The stent body 10 includes features that facilitate the connection of valve leaflets as discussed further below. In this particular stent body, the valve connection features include three commissure posts 50 formed integrally with the rest of the stent and extending axially in the ring section 30. The commissure posts are connected to the struts of the ring section and are spaced equidistant around the ring section 30.
The particular construction of the stent body 10 shown in Figure 2 (and later figures) is only an example.
Numerous other collapsible and expandable stent bodies can be used. By way of example only, the ring region may include multiple rows of cells; valve connection features other than axially extended posts can be used; and the aorta section 20 and the struts 60 can be omitted. As an example, Figure 33 shows a variation of stent with multiple rows of circumferentially collapsible / expandable cells in the annular valve section 30 of the stent body 10. Referring to Figure 34, a few representative cells in the most distal or downstream row are numbered 32a, while a few representative cells in the most proximal or upstream row are numbered 32b. The locations of some of the cells, which are otherwise hidden by sleeve material in Figure 34, are improved by the addition of dotted lines.
A valve 100 (Figure 3) incorporating a stent body 10 similar to the one discussed above with reference to Figure 2 includes three flexible prosthetic leaflets 70 formed of a biocompatible material such as an animal tissue such as, for example, pericardial tissue or a material synthetic polymer, such as a silicone-polyurethane polymer. The leaflets are mounted on the body of the stent, such as by suturing the leaflets to the posts 50, so that when the valve and the body of the stent are in an expanded state as shown in Figure 3, the leaflets they are arranged totally or partially within the ring section 30 of the stent body.
The valve also includes a sleeve 85. The sleeve includes a first sleeve portion 80, also referred to herein as a supraanular sleeve portion, which extends over a region of the tubular wall of the ring section 30 at a distance from the end proximal of the ring section and distal to the flare region 40 of the ring section. The sleeve also includes a second part, also referred to herein as the subannular part 90 of the sleeve, proximal to the first part 80. A line 110 is shown in Figure 3 as a boundary between these two parts of the sleeve for clarity of the illustration. . In actual practice, there may or may not be a visible demarcation between these parts. Line 110 is approximately at the bottom of the commissure posts 50. In other words, in this embodiment, the second sleeve part 90 is disposed proximal to the commissure posts and proximal to the prosthetic leaflets 70. In the embodiment shown in FIG. 3, both the first sleeve part 80 and the second sleeve part 90 extend over the outer surface of the stent body, that is, the outwardly oriented surface away from the axis 14. The second or sub-annular part 90 of Sleeve also includes a layer of material 120 (Figure 4) on the inner surface of the flared part 40 of the stent. Thus, the second or sub-annular part 90 of the sleeve is thicker than the first or supra-annular part 80. In Fig. 4 a dashed line 105 is shown for clarity of the illustration at the junction of the inner layer 120 and the layer in the outer surface, that is, on the proximal edge of the stent body. In actual practice there may be no visible border in this location. In the particular embodiment shown in Figure 4, the entire sleeve 85 is formed of a sheet of unit material. Layer 120 is integral with the sleeve material outside the stent, and is formed by folding the unit sheet around the proximal edge of the stent. The material inside and outside the stent can be sutured together
This particular embodiment is illustrative only; In other arrangements, sleeve portions 80 and 90 may be formed as separate pieces of the same or different materials. One or both sleeve portions may include one or more layers inside the stent body, one or more layers outside the stent body, or both. The layers inside and outside the sleeve can be formed separately from each other or integrally with each other. The sleeve desirably connects to the stent, for example, by suturing the cell struts, the joints between the cell struts, or both. The sleeve can be formed of materials such as
animal tissues such as, for example, porcine, sheep and bovine pericardium, porcine submucosa and synthetic fabrics such as knitted or woven polyester, and nonwoven fabrics. Collagen impregnated fabrics can be used. In addition, bioabsorbable materials such as polyglactin, lactide and caprolactone copolymers, and polylactides can be used.
Figure 4 shows the valve 100 (Figure 3) as seen in an axial view, looking distally from the proximal end of the valve. The three flexible leaflets 70 can be seen in Figure 4 in its almost closed state (ie, "free" upper edges of the leaflets approaching approximately in a Y-pattern). The valve is preferably designed to close with fully redundant coaptation under the diastolic return pressure.
In operation, the valve is brought to a collapsed state and mounted on an administration device (not shown) such as an elongated probe having a cover adapted to retain the stent body in the collapsed state. The administration device may include a mechanical or other arrangement to release the stent body from the sheath once the valve has advanced to the desired location within the body. For example, the administration device may be arranged to move the sheath with respect to the stent body in response to manipulation by the operator. In the collapsed state, the stent body, including ring section 30 and aorta section 20, is radially compressed. The prosthetic valve leaflets 70 are folded into the body of the stent. Since the second or thick subannular part 90 of the sleeve is disposed proximal to the valve leaflets, it does not prevent the valve from collapsing to a relatively small diameter.
The administration device is advanced to the patient's body until the valve is aligned with the native aortic valve, with the ring section 30 adjacent to the aortic ring. The valve is released from the sheath and the body of stent 10 expands under its own resilience. Resilient expansion can take place only as a result of the release of the mechanical constriction of the stent body, or it can include the expansion resulting from the effects of the temperature change on the material of the stent body. In this embodiment, the entire expansion of the stent body from its collapsed state to its expanded operating state is caused by the stent body itself. In other words, the stent body desirably is fully self-expanding and does not require a balloon or mechanical movement device to cause any part of the expansion. As best seen in Figure 5, the ring section 30 takes the first or supraannular section 80 of the sleeve to the coupling that engages the ring 2 of the native aortic valve, and to the coupling with the inner surfaces 7 of the leaflets. native valve The expansion of the ring section 30 and, particularly, the expansion of the flared part 40 lead the second or sub-annular section 90 of the sleeve to the coupling with the LVOT proximal to the ring 2. The sleeve forms a seal with the native anatoirna. Depending on the anatoirna of the particular patient, the seal can be formed with one or more of the inner surfaces 7 of the native valve leaflets, the ring and the LVOT. The aorta section 20 (Figure 1) is coupled to the native anatoirna at or near the sinotubular junction 4.
Although the stent reaches an expanded configuration, it typically does not reach its configuration without fully expanded constriction. Thus, the resilience of the stent body typically causes the aortic section 20 to rest on the sinotubular junction and also causes the ring section 30 to rest on the ring and on the inner surfaces of the leaflets, which helps maintain the Coupling sealing sleeve with native anatoirna. The prosthetic valve leaflets 70 open to allow distal or anterograde blood flow during sfstole, and close to block proximal or retrograde flow during diastole. The sealing coupling of the sleeve with the native anatoirna helps block retrograde flow around the outside of the stent body, commonly referred to as perivalvular leakage. The valve does not block the flow to the coronary arteries. For example, support struts 60 can extend through the sinus of Valsalva, so that blood can flow to the coronary arteries through spaces between the support struts.
Figure 6 is similar to Figure 5, but shows the valve used in an alternative implantation procedure. In this procedure, the patient's native aortic valve leaflets have undergone resection (removed), typically before implanting the prosthetic valve 100 in the patient as shown. In this embodiment, the first or supraannular part 80 of the sleeve is coupled with the native valve ring 2, while the second part 90 of the sleeve is in contact with the native anatoirna proximal to the ring 2, that is, with the distal end of the outflow tract of the left vent (LVOT).
The embodiment discussed above can be varied in many ways. For example, Figures 5 and 6 represent the sleeve disposed only outside the ring region 30 and the flared part 40 of the stent body. However, the sleeve can be arranged inside only or inside and outside at the same time. In addition, the stent body may not be entirely or even partially self-expanding. The stent body can be brought from its collapsed state to an expanded operating state by means of one or more inflatable balloons or mechanical elements incorporated in the administration device.
A valve according to a further embodiment includes a sleeve 200 (Figure 7) formed extending around the outside of the ring section 202 of the stent. In the radially expanded state of the stent body, the sleeve material is folded. In this embodiment in addition, the stent is a radially collapsible structure, and may be similar to the stent body discussed above. For example, the ring section may include numerous cells that cooperatively define a tubular wall, each of said cells being formed of interconnected cell struts 204. In the radially collapsed state (not shown), the cell struts are oriented
more almost parallel to the proximal-distal axis 214 of the stent body. Thus, as the stent is transformed from the radially expanded state shown in Figure 7 to the radially collapsed state, the ring section tends to lengthen in the axial direction. In the reverse transition, from the radially collapsed state to the radially expanded state, the ring region decreases in axial length as it increases in diameter. The folds in the sleeve define a plurality of valley regions 203 and crest regions 205 which generally extend in the circumferential direction. As the stent decreases in axial length during the transition to the radially expanded state, adjacent valley regions approximate each other. This facilitates the radial expansion of the crest regions. Optionally, the sleeve can be connected to the stent body only in the valley regions. The folds may or may not be present in the radially collapsed state of the stent body. In other words, the axial extension of the stent body during radial collapse can collapse crest regions 205 inward to the same diameter as valley regions 203. In the radially expanded state of the stent body, the folds help to form An effective seal with native tissue. Sleeves with folds according to this embodiment can be formed from sleeve materials discussed above. It is not necessary that the folds be exactly circumferential. For example, they can be one or more helical valley regions and one or more helical crest regions, so that the valley and crest regions cooperatively define a shape generally similar to a screw thread.
The valve of Figure 7 also includes predisposition elements in the form of bands 210 of sponge-like hygroscopic material that easily collapses and fills a larger volume when the stent expands after implantation. By way of example only, the hygroscopic material may be a collagen sponge or foam similar to the commercially available material with the Angioseal trademark used to plug arteries, and the similar material currently used for embolic protection. The predisposition bands or elements 210 are formed separately from the sleeve and are coupled between the crest regions 205 of the sleeve and the outer surface of the ring portion 203 of the stent. Thus, the predisposition elements are mechanically coupled with the sleeve and the stent body. When the valve is implanted and the material of the bands 210 swells, the predisposing elements force the crest regions of the sleeve outward with respect to the ring region 202 of the stent body. In the embodiment of Figure 7, the bands of hygroscopic material are arranged proximal to the leaflets 271 of the prosthetic valve, and therefore are axially offset from the leaflets. This facilitates the collapse of the valve to a small diameter. In a valve according to even another embodiment (Figure 8), the predisposing element includes a helical band 211 of hygroscopic material disposed within the sleeve 201.
Pre-disposition elements, such as hygroscopic material, can be used with sleeves other than the folded sleeves shown in Figures 7 and 8. Bands of hygroscopic material can be integrated into the valve to take advantage of the specific geometry in order to increase the capacity of sealing them, while not compromising (that is, improperly increasing) the diameter of the collapsed valve. For example, in a valve that includes a sleeve having a sub-annular part as discussed above with reference to Figures 3 and 4, the predisposition element can be located to expand the sub-annular sleeve part (i.e., on the side upstream of the patient's native valve ring). Again, as the predisposition element is axially offset from the prosthetic valve elements, it is not added to the cross section of the prosthetic valve where the valves are when the valve is collapsed. In the collapsed state, the volume of the predisposition element does not overlap the volume of the leaflets. This helps to make the valve collapse possible to a circumferential size smaller than what is possible if both the leaflets and the predisposition element were in the same cross-sectional area of the valve.
In a further variant, a predisposition element, such as a water absorbing polymer, can be placed between layers of sleeve material, so that the predisposition element forces the outer layer away from the stent body. In a further embodiment, the sleeve material can be impregnated with such a polymer. When it is allowed to expand as a result of implantation in a patient and the subsequent absorption of water from the tissue and / or blood of the patient, these materials can fill any gaps in the sleeve material and can also fill gaps between the sleeve material and native tissue to reduce PV leakage.
Staples and / or sutures may be used to secure the valve to the patient's native valve ring using elongated instruments transapical or percutaneously inserted. The valve shown in Figure 9 has a stent body having a ring section 30 similar to the ring section of the valve discussed above with reference to Figures 2-4. This particular valve body does not have an aortic section as used in the valve body of Figures 2-4. The ring section 30 has a flared part (not shown) at its proximal end, that is, at the bottom of the drawing as seen in Figure 9. In this embodiment, in addition, the sleeve includes a second or sub-annular part 90 cuff The cuff part 90 may be sutured or stapled to the patient's native tissue because the bases or proximal edges of the prosthetic valve leaflets 70 are downstream of the cuff part 90. Point lines 72 in Figure 9 indicate the approximate locations of the valve bases. The zones 92 of the second sleeve part 90 are thus available for stapling or suturing through the sleeve 90 in the patient's native tissue without interfering with the prosthetic leaflets 70.
The valve of Figure 10 includes a sleeve 285 defining multiple pockets 220. Each sleeve has an open side 221 oriented distally. The other sides of each sleeve are substantially closed. When
The valve is implanted, these pockets will prevent perivalvular leakage or retrograde blood flow around the outside of the stent body. The retrograde flow will tend to fill each pocket with blood and thus predispose the outer surface of the pocket outward, until the coupling with the native tissue, for example, until the coupling with the ring or valves of the native valve. In other words, the pockets act as miniature parachutes around the periphery of the valve. It is expected that pockets 220 will finally have incoming tissue growth to eliminate the long-term need for their PV leak prevention function. In figure 10 the mini-pockets 220 of the sleeve are constructed to prevent retrograde flow. It will be appreciated, however, that the pockets can be oriented in the opposite direction (ie, to prevent the bloody flow forward), with their open sides generally oriented proximally. Pockets can be provided in any number, size and / or shape to minimize leakage. The pockets 220 can be made of the same sleeve materials as discussed above.
A valve according to a further embodiment of the invention (Figure 11) incorporates predisposition elements in the form of springs 230 formed integrally with the stent body. In the expanded state of the stent body, parts of the springs protrude outwardly from the tubular wall of the ring section 30. The sleeve, or the outermost layer of the sleeve, is disposed out of the tubular wall and out of the springs, so that the springs tend to predispose the sleeve 85 outwardly relative to the wall of the ring section. Predisposition elements of this type can be provided at any location along the sleeve. The springs 230 may be axially extended fingers as shown in Figure 12, or they may have other configurations. For example, finger-shaped springs can be directed generally circumferentially. The fingers may have blunt ends for coupling with the sleeve, as shown in 230c and 230d in Figure 12. Alternatively, the fingers may have sharp ends as shown in Figure 12 in 230a and 230b. Fingers with sharp ends can pierce the cuff and can also pierce the native tissue.
The predisposition elements may also include helical springs. As shown in Figure 13, a conical helical spring 250 has a spring shaft 251 and a spring member disposed in a helix around the spring shaft so that the spring member defines a plurality of progressively increasing diameter turns. The largest turn 253 defines a base surface of the spring. A plurality of said springs can be mounted between the stent body and the sleeve, with the base surface facing inwards towards the stent body, and with the spring axis generally extending in a radial or outward direction. Here again, the spring will tend to predispose the sleeve out with respect to the stent body. When the stent includes cells formed from cell struts, the base surface of each spring can be supported in a joint between the struts. Also, when the stent includes commissure posts such as posts 50 shown in Figure 2, the springs can be supported on the commissure posts. In a further arrangement, the springs can be provided between layers of a multilayer sleeve. Each spring 250 can be cut from a flat sheet of a coil pattern (spiral) and shaped into a cone. The material can be a superelastic / shape memory material such as Nitinol. Depending on the size of the spring base, each turn of the spiral can even be in the form of a seat to allow the spring to conform to the curvature of the part of the stent on which the spring sits (Figure 14).
In a further embodiment (Figure 14), the turns 251 are generally elliptical as seen in the end view, looking along the spring axis 250. Also, in this embodiment, the base surface defined by the largest turn 253 is curved about an axis 257 transverse to the spring axis 250. Thus, parts 255 of lap 253 at a distance from axis 257 protrude in directions parallel to the spring axis 250, out of the plane of the drawing, towards the observer as seen in Figure 13. The other turns desirably have a similar curvature. Thus, when the spring is fully collapsed, it has the shape of a part of a cylinder, the axis 257 being the axis of the cylinder. A spring according to this embodiment can be mounted on the stent body, with the transverse axis 257 oriented generally parallel to the axis of the cylindrical surface, and desirably coaxial with said cylindrical surface. In other words, the spring in its collapsed or compressed state may coincide with the curvature of the stent body in its radially collapsed state. This design has the ability to be low profile, with minimal radial extension when it collapses and the ability to push radially outward when deployed.
Helical springs as shown in Figures 13 and 14 can be cut from a flat sheet, and then heat hardened or formed into mandrels to make them obtain the characteristics of a spring. They can be connected by means of sutures, welds, locking mechanisms, etc. to the stent body or placed inside the appropriate sleeve part. Helical springs can also be formed integrally with the stent body.
A valve according to even another embodiment of the invention includes a sleeve 85 similar to the sleeves discussed above. However, in this embodiment, the sleeve is provided with a thin ring 260 formed of a resilient material such as silicone rubber. The ring 260 extends circumferentially around the rest of the sleeve and around the ring section 30 of the stent body. The ring has a main part 261 that rests on the stent body through the other layers of the sleeve, and has a free edge 262 axially offset from the main part. When the stent body is in its radially collapsed state, the free edge of the ring is flat against the other structures of the stent. When the inner diameter of the ring expands
forcedly by the transition of the ring section 30 of the stent body from the free edge 262 of the ring tends to turn and thus tends to protrude outwardly with respect to the main part 261 and with respect to the stent body. This causes the free edge 261 of the ring to seal against the surrounding native tissue, even when the native tissue is irregular. The ring has a low enough profile to collapse during the administration of the prosthetic valve in the patient. The ring can be placed anywhere along the axial extension of the ring section. If it is axially offset from the prosthetic valve leaflets 70, as when placed in the area of the second subannular sleeve portion 90, this will minimize the material of the valve in the cross-section of the leaflets.
A ring such as the one discussed above with reference to Figure 15 can also be used as a predisposition element, to predispose another part of the sleeve outwardly with respect to the stent body. For example, in the embodiment of Figure 16, a ring 260 similar to the one discussed above is disposed between the stent body and an overlapping portion 270 of the sleeve material. The free edge of the ring rests on this part 270 and the force out with respect to the stent body. The sleeve package shown in Figure 16 is thus caused by the free edge of the silicone ring that is turned over.
Since the features, as discussed above with reference to Figures 7-16, provide a predisposition outwardly to the parts of the sleeve, they tend to promote effective sealing between the sleeve and the surrounding native tissue even when the native tissue is irregular . While these features have been previously discussed in connection with an expandable stent body, they can be used with other types of stents. For example, a valve designed for implantation in an open surgery technique may include a substantially non-expandable stent. The predisposition characteristics can also be used with stents of this type.
Calcified patterns of aortic stenosis can take place in a variety of distribution patterns, which can have a direct effect on PV leakage between the stenotic leaflets and an implanted collapsible valve. In many cases, PV leakage is more likely to occur at the commissure location between native stenotic leaflets (R. Zegdi et al., "Is It Reasonable to Treat All Calcified Stenotic Aortic Valves With a Valved estent?", Valvular Heart Disease, Vol. 51, No. 5, pages 579-84, February 5, 2008). In other words, the native valve ring, and the space defined by the inner surfaces of the native valve leaflets, have no circular cross-sectional shape. A valve according to a further embodiment includes a sleeve 285 (Figure 17) that includes a plurality of regions 280 distributed around the circumference of the sleeve. In the operative implanted configuration shown, some of these regions 280a, 280b and 280c, referred to herein as "bulk regions, have radial thickness R greater than the radial thickness of other regions, such as regions 280d, 280e and 280f, referred to herein as "intermediate regions." In the particular example of Figures 17 and 18, there are three bulk regions circumferentially spaced between sf and intermediate regions between the bulk regions. In another example, there are two bulk regions 280a and 280b spaced between sf and intermediate regions such as 280e and 280d between the bulge regions.The number and location of the bulge regions are desirably selected to match the configuration of the native tissue of the particular patient.Therefore, in order to making the valve sleeve specifically for a particular patient, each region 280 incorporates a separate chamber 287, (figure 18). Each chamber can be inflated to pro Portion a region of bulk or be left deflated to provide an intermediate region. This arrangement can provide sufficient sealing against PV leakage without adding additional unnecessary sleeve material. The configuration of Figures 17 and 18 can be used, for example, in a patient having a typical tricuspid native aortic valve with stenotic native valves. The configuration of Figures 19 and 20 can be used in a patient who has a native bicuspid stenotic aortic valve.
The chambers can be inflated either before implantation or after the valve has expanded into the native stenotic valve. Inflation can be achieved intraprocedurally with material such as liquid collagen or RTV silicone, or before the procedure with similar or other materials. This sleeve construction offers the potential of a single collapsible valve design for use in a variety of sizes of aortic valve and calcified distribution patterns, while some of the previously known designs can only be used with uniform calcified distribution patterns. This sleeve design can also be used in insufficient aortic valves (leaking) due to its ability to fill PV leaks and clearances. Other possible uses of this sleeve design are in other valve positions. For example, a configuration such as that shown in Figures 19 and 20 can be particularly well suited for the mitral valve, which is naturally elliptical and often insufficient (leaking).
As discussed further below, certain techniques that can be employed in prosthetic heart valve procedures may be better applied while the regions treated by these techniques are temporarily isolated from direct blood flow. A device that insulates a work camera can be beneficial. Such a device is described in the document by R. Quaden et al .: "Percutaneous Aortic Valve Replacement: Resection Before Implantation," European Journal of Cardio-thoracic Surgery, Vol. 27, 2005, pags. 836-40, the description of which is hereby incorporated by reference herein. As described in the article by Quaden et al., An aortic valve resection chamber is sealed by polyethylene balloons. Surgical instruments are inserted through an instrument channel. Two catheters with small sealing balloons provide coronary heart cardioplegia and prevent coronary embolization during the resection process. A
This type of work camera can also be beneficial (although not necessarily in all cases) for the application of some techniques such as those described later in this specification.
Many lasers have been used to coagulate tissue in the medical sector. An example of the laseroscope system used to cauterize tissue (available from Laseroscope, 3052 Orchard Drive, San Jose, CA 95134-2011). A low power laser that can minimize tissue vaporization, even adhere tissue, is optimal. As alternatives, other energy sources such as ultrasound, cryogenics, an electrical resistance or other heating element can be used. The sleeve of a prosthetic valve can be made to adhere to the native tissue such as, for example, the stenotic leaflets (or the native valve ring if the leaflets undergo resection) during or after implantation. For example, a swine pericardial strip can be used on the outside of the sleeve to adhere a tissue-to-tissue junction. Probes in various ways (toroid, pointed, etc.) can be used to directionally apply energy to the desired locations.
In certain medical applications biocompatible adhesives, such as epoxyamines, have been applied. See, for example, US patents. UU. 6,780,510 and 6,468,660). Such adhesives can be applied around the cuff penimeter of a prosthetic valve to adhere to stenotic leaflets (or to the ring if the leaflets have undergone resection) during or after implantation. In certain situations, other silicone materials such as "caulking" may be used. The adhesive can be injected internally or externally through holes in the valve sleeve itself and / or the sleeve may have pockets to allow injection (see Figures 10, 12 and 16).
A valve according to a further embodiment of the invention (Figure 21) includes an expandable stent body 10 having a ring section 30 with a proximal-to-distal axis 14. The valve also includes a sleeve 400 that has a generally tubular wall with a free end 402 and with surfaces 403 and 404. In the collapsed state shown, surface 403 is the inner surface of the tube and surface 404 is the outer surface. In the radially collapsed state of the stent body 10, the tubular wall protrudes from the proximal end of the stent so that the free end 402 of the tubular wall is proximal to the ring section 30. Otherwise expressed, in this state, the free end 402 of the tubular wall is axially offset from the ring section and axially offset from the stent body. Thus, Figure 21 shows the collapsed or folded stent 30 and the collapsed or folded sleeve 400 at different locations substantially not superimposed along the proximal-distal axis of the valve. Elements 30 and 400 can be connected between sf, p. eg, in an interface between them. But preferably they don't overlap, at least not greatly. Thus, in this state the thickness of the tubular wall 400 is not added to the diameter of the stent. This is desirable to maintain the outside diameter, and therefore the circumferential size of the valve as small as possible for a less invasive administration in the patient.
Figure 22 shows the structure of Figure 21 when implanted in the patient. In particular, Figure 22 shows the ring section 30 in a radially expanded state. The sleeve 400 is also radially expanded and the reverse (turned inside out) has been turned around so that it is now arranged around the outside of at least a portion of the ring section 30 of the stent body. Note that surface 403 is now on the outside of the tube. In the conversion from the collapsed state to the operating state, the free end 402 of the tube moves relative to the stent body. Accordingly, the free end 402 is referred to herein as a "mobile" part of the sleeve. In the operative state shown in Figure 22, the free end or movable part is axially aligned with part of the ring section 30. In this state the sleeve 400 helps to ensure proper sealing of the valve in the patient's surrounding native tissue. .
Tubular sleeve 400 may be turned over during administration of the valve in the patient but before the valve is fully seated at the site of valve implantation in the patient. Depending on the resilient properties of the tubular sleeve 400, the radial expansion of the stent body may cause the tubular sleeve to turn from the inside out as shown. Alternatively or additionally, the tubular sleeve may have a free or undistorted shape so that it naturally tends to turn from the inside out as shown in Figure 22 when it is not constricted. The tubular sleeve can be forcedly distorted to the state represented in Figure 21, and another element of the administration device can be built in that position. Thus, as shown in Figure 23, after the sleeve 400 has emerged from the distal end of an administration sleeve 500, the sleeve tends to turn resiliently around the outside of the stent body 10. Figure 24 shows an alternative or addition in which sutures or wires 510 are used to pull the mobile or end element 402 of the sleeve 400 above and around the outside of the stent body 10. This movement can be performed before, during or after the expansion of the body of stent. By way of example only, when the administration device includes an elongated probe, the sutures or wires 510 can be extended along the administration device to a handle or other element accessible to the operator. In addition, the sutures can be provided as loops that can be removed from the sleeve by selectively pulling one end of the loop. For example, sutures 510a and 510b are parts of a unit loop that extend through holes in the sleeve. Pulling both ends of the loop simultaneously tends to pull the free edge or mobile part 402. Pulling one end of the loop will remove the suture from the cuff. Figure 25 shows yet another alternative or addition in which alloy members with shape memory (eg, nitinol) 410 in the sleeve 400 cause the sleeve to turn over when the sleeve is released from the system constriction of administration within the patient at or near the valve implant site.
A sleeve with a movable part can be arranged to form a seal with any part of the native anatomy. For example, Figure 26 shows a prosthetic valve 10 fully implanted in a patient, with the sleeve 400 that has turned around the outside of the stent body 10 and pressed radially outward against the valves 6 of the patient's native stenotic heart valve to seal the prosthetic valve against the PV leak.
Figure 27 is generally like Figure 21, but in Figure 27 the sleeve 400 is longer than in Figure
21. Figure 28 is generally like Figure 23, but shows the structure of Figure 28 after it has been implanted in a patient. In the structure of Figures 27 and 28, the sleeve 400 has an axial extension that is approximately the same as the axial extension of the ring portion 20 of the stent body. In this embodiment, the proximal end of the stent can be arranged proximal to the native valve ring 2, and even a part of the sleeve 400 will still reach and seal against native structures such as the ring 2 and the stenotic leaflets 6. The structure of the figures 27 and 28 incorporates a balloon 601 disposed in the administration device within the stent body, such as within the ring region 30 of the stent body, to forcefully expand the stent body. This structure also includes an additional balloon 603 that is disposed within the sleeve when the stent is in the radially collapsed state. The sleeve 400 can be rotated from the inside out by inflating the balloon 603 before or during the expansion of the stent body. In additional variants, the balloon can be arranged to expand progressively, starting at the free end 402, to help turn the stent inside out. By way of example only, balloon 603 can include a plurality of chambers arranged along the axis of the structure, so that these balloons can be inflated in sequence.
In other embodiments, the movable part of the sleeve can be moved relative to the stent body by coupling with native anatomical structures. For example, the cuff can be constructed and administered so that it snaps into the patient's native stenotic heart valve leaflets during administration. Figures 2931 show examples of this action. The valve of Figure 30 is generally similar to the valves of Figures 22 and 28, but shows the addition of hook-shaped coupling elements 420 at the free end 402 of the sleeve 400 remote from the stent 30. Figure 30 shows the structure of figure 29 in a deployment phase. In this phase, the tubular sleeve has been deformed to a configuration in which the hook members or hooks 420 can be coupled (hooked on) to the distal ridges of the patient's native stenotic leaflets 6. Once the hitch members have been engaged, the stent body moves proximally with respect to the native anatoirna. As shown in Figure 31, the proximal movement of the stent body 10 to the space limited by native leaflets 6 causes the sleeve 400 to turn inside out around the outside of the stent 10. This is aided by the fact that the hooks 420 secure the free end 402 of the sleeve 400 to the distal edges of the leaflets 6. Ultimately (as shown in Figure 31), the sleeve 400 is sandwiched between the body of stent 10 and native leaflets 6. The presence of the hooks 420 on native valves 6 helps the sleeve 400 to seal the prosthetic valve against PV leakage, and also helps to anchor the valve at the site in the patient.
The coupling elements or hooks 420 may be of any suitable material. One possibility is that the hooks 420 are made of nitinol and extend through the fabric or other material of the sleeve 400. The hooks 420 can be connected to the ring section 30 or other parts of the stent body, and can be formed integrally with the stent body.
In the procedure of Figures 29-31, the mobile element moves during the proximal movement of the valve, from the aorta 5 to the left vent 1. In a further variant, the mobile element is deployed by the movement in the opposite distal direction regarding the native anatomy. In that case, the hooks 420 'can be arranged to engage in the ring 2 as shown in Figure 32. In this arrangement, the tubular sleeve element initially protrudes from the distal end of the ring section 30. The members of 420 'hitch is coupled to native anatomical structures such as the LVOT. The free end or movable element moves proximally with respect to the ring section 30 of the stent body as the stent body moves distally with respect to the native anatomy.
The mobile part of the sleeve may include the entire sleeve or any part of the sleeve. In addition, the movement of the mobile part of the sleeve can occur in different ways to rotate the sleeve from the inside out. For example, the structure of Figure 33 incorporates a sleeve 400 and a stent body 10 having a ring region 30. During the advance of the valve inside the patient, the stent is constrested in its radially collapsed state by a sheath 605 The sleeve 400 includes a resilient tube having an internal diameter not formed approximately equal to or greater than the external diameter of the ring region 30 in its radially collapsed state. During the advance into the patient, the sleeve is retained in a collapsed state by an additional sheath 607 separated from the sheath 605. During deployment, sheath 607 moves axially A1 relative to the sheath, to release at least the part of the sleeve 400 closest to the body of the stent and allow it to expand. While the sheath 605 moves axially in the A2 direction relative to the stent body, the sleeve also moves relative to the stent body before the stent body fully expands to its radially operative expanded state. For example, the administration device may include sutures 510 similar to those discussed above with reference to Figure 24 for moving the sleeve. As the stent body expands, it attaches to the inside of the sleeve. When the stent body is forcedly expanded by a balloon or mechanical element, the sleeve can slide over the outside of the stent body
to pull the sleeve around the outside of the stent body before or during operation of the expansion device.
Although the valves have been previously treated with reference to the implantation of the valves in native valves that naturally occur from a patient, the valves can also be implanted within previously implanted prosthetic valves. In such a procedure, the previously implanted prosthetic valve constitutes the native valve. For example, the sleeve will seal against previously implanted prosthetic valve structures such as, for example, against the interior of the previously implanted stent body and sleeve, or the interior surfaces of previously implanted prosthetic valve leaflets.
The following points refer to additional examples:
1. A prosthetic heart valve to replace a native heart valve that has a native valve ring comprising:
(a) a stent body that includes a generally tubular ring region that has a proximal-to-distal axis and that has a radially collapsed state and a radially expanded state, the ring region increases in diameter during the transition from the state radially collapsed to the radially expanded state;
(b) one or more prosthetic valve elements mounted on the stent body and operative to allow distal flow through the ring region, but to substantially block the flow proximally through the ring region; Y
(c) a sleeve secured to the stent body, the sleeve comprising
(i) a first sleeve part covering at least a part of the ring region for arrangement in said native valve ring, the first sleeve part has a first diameter when the ring region is in the radially expanded state and
(ii) a second sleeve part proximal to the first sleeve part, the second sleeve part has a second diameter when the ring region is in the radially expanded state, the second diameter being larger than the first diameter, the second being sleeve part adapted for coupling with the native tissue proximal to the native valve ring.
2. A valve as claimed in point 1 wherein the stent body includes a flared section proximal to the ring region, the flared section has a diameter larger than the ring region when the stent body is in the expanded configuration At least one part of the second sleeve part extends along the flared section of the stent body.
3. A prosthetic heart valve comprising:
(a) a stent body that includes a generally tubular ring region that has a proximal-to-distal axis and that has a radially collapsed state and a radially expanded state, the ring region increases in diameter and decreases in axial length during the transition from the radially collapsed state to the radially expanded state;
(c) a sleeve secured to the stent body and surrounding the ring region, the sleeve has one or more folds adapted to collapse in axial directions and expand in radial directions in the transition of the stent body from the radially collapsed state to the state radially expanded.
(a) a stent body that includes a generally tubular ring region having a proximal-distal axis;
(c) a sleeve secured to the stent body and surrounding the ring region; Y
(d) one or more predisposition elements separated from the sleeve mechanically connected to the stent body and to the sleeve, the one or more predisposition elements are adapted to predispose at least a part of the sleeve out with respect to the stent body.
5. A valve as claimed in item 6, wherein the stent body is an expandable metal stent body having a radially collapsed state and a radially expanded state, the ring region increases in diameter during the transition from the state collapsed radially to the radially expanded state.
6. A valve as claimed in point 5 wherein the one or more predisposition elements include one or more springs.
7. A valve as claimed in point 6 where the springs are integrally formed with the stent body.
8. A valve as claimed in point 6 wherein the springs include a plurality of helical springs, each of the helical springs has a spring shaft and an elongate member extending in a plurality of turns around the spring axis .
9. A valve as claimed in point 8 wherein the turns of each spring are curved about an axis transverse to the spring axis and parallel to the proximal-to-distal axis of the stent body.
10. A valve as claimed in point 5 wherein the one or more predisposition elements include a hygroscopic material.
11. A valve as claimed in item 10 wherein the one or more valve elements include a plurality of prosthetic valve leaflets arranged at least partially within the ring region and the hygroscopic material is offset proximally or distally. the valve leaflets at least when the stent body is in the radially collapsed state.
12. A valve as claimed in item 10 wherein the hygroscopic material includes a helical hygroscopic element that extends around the ring region.
13. A valve as claimed in point 5 wherein the one or more predisposition elements include a resilient ring that extends circumferentially around the ring region, the ring has a main part that rests on the body of the stent and a free edge not connected to the stent body, the ring is constructed and arranged so that with the radial expansion of the ring, the ring is deformed and said deformation predisposes the free edge outward with respect to the main part and the body of the stent .
(c) a sleeve secured to the stent body that extends around the ring region, the sleeve includes a ring that extends circumferentially around the body of the stent, the ring has a main part that rests on the body of the stent and a free edge not connected to the stent body, the ring is constructed and arranged so that with the radial expansion of the ring, the ring is deformed and said deformation predisposes the free edge outward with respect to the main part and the body of the stent .
(c) a sleeve secured to the stent body, the sleeve has a movable part movable in an axial direction with respect to the stent body so that when the stent body is in the radially collapsed state, the movable part of the sleeve is axially deviated from the ring region of the stent body and the mobile part of the sleeve can be moved to an operative position in which the mobile part of the sleeve extends around the ring section.
16. A valve as claimed in point 15 wherein the sleeve has a generally tubular wall with a fixed end connected to the stent body and a free end that protrudes axially away from the ring section when the stent body is in the radially collapsed state, the mobile part of the sleeve includes the free end of the tubular wall, the tubular wall is constructed and arranged so that the tubular wall can be rotated from the inside out to bring the free end of the tubular wall to the operative position, The free end of the tubular wall extends around the ring region when the sleeve is in the operative position.
17. A valve as claimed in point 16 wherein the sleeve is constructed and arranged to rotate from the inside out to bring the free end of the tubular wall to the operational position at least in part in response to the transition of the region of ring from the radially collapsed state to the radially expanded state.
18. A valve as claimed in item 16 which further comprises sleeve coupling elements connected to the free end of the sleeve, the sleeve coupling elements are constructed and arranged to be coupled to one or more features of the native anatoirna so that The sleeve can be turned inside out at least in part by the axial movement of the stent body relative to the coupled features of the native anatomy.
19. A valve as claimed in item 18 where the free end of the sleeve protrudes proximally from the ring region of the stent body and where the coupling features are adapted to engage the native valve leaflets.
20. A prosthetic heart valve comprising:
(c) a sleeve defining one or more pockets outside the ring region, each of said pockets has an outer wall, an open side oriented in a first axial direction and having a closed side oriented in a second opposite axial direction to the first axial direction so that the flow of blood in the second axial direction will tend to force the blood inside the pocket and predispose the outside of the pocket outward with respect to the stent body.
21. A valve as claimed in item 20 wherein one or more pockets include a plurality of pockets having open sides oriented distally.
(c) a sleeve that extends around the ring region, the sleeve has a plurality of regions circumferentially spaced from each other, each region has a radial thickness, the radial thicknesses of at least one of the regions is different from the radial thickness of at least one of the other regions when the sleeve is in an operational configuration.
23. A valve as claimed in item 22, wherein at least one of the regions includes hollow chambers so that the sleeve can be brought to the operational configuration by inflating the hollow chambers.
24. A valve as claimed in item 23 where the hollow chambers are constructed and arranged so that the one or more hollow chambers can be inflated independently of one or more of the other hollow chambers.
25. A valve as claimed in item 22 wherein the plurality of regions includes three bulk regions circumferentially spaced between sf and intermediate regions disposed between the bulk regions, the bulk regions have greater radial thickness than the intermediate regions.
26. A valve as claimed in item 22 wherein the plurality of regions includes two bulk regions circumferentially spaced between sf and intermediate regions disposed between the bulk regions, the bulk regions have greater radial thickness than the intermediate regions.
27. A valve as claimed in any of the preceding points wherein said one or more valve elements include a plurality of flexible prosthetic valve leaflets arranged at least partially within said ring region.
28. A method of treating a patient that comprises the stages of:
(a) inserting a prosthetic valve that includes a stent body, one or more prosthetic valve elements connected to the stent body and a sleeve that extends over at least a part of the stent body inside the patient while the stent body and sleeve they are in a radially collapsed state;
(b) bringing the stent and sleeve body to a radially expanded state and placing the stent and sleeve body so that a first part of the sleeve is coupled to a native valve ring and a second part of the sleeve is coupled to native tissue adjacent to the ring; Y
(c) fix the second part of the sleeve to the native tissue.
29. The method of item 28 wherein said second part of said sleeve is fixed to said native tissue by means of sutures or staples.
30. The method of item 28 wherein said fixing step includes applying energy to said second part of said sleeve to form an adhesion with the native tissue.
31. The method of item 28 where the native valve ring is the ring of the native aortic valve and where the second part of the sleeve is coupled to the outlet tract of the native left vent.
32. A kit for carrying out a method as claimed in any of points 38-31 which includes (i) a prosthetic valve that includes a stent body, one or more prosthetic valve elements connected to the stent body and a sleeve that it extends over at least a part of the stent body; and (ii) at least one fixing tool adapted to fix the sleeve to native fabric.
Although the invention of this specification has been described with reference to particular embodiments, it should be understood that these embodiments are merely illustrative of the principles and applications of the present invention. Therefore it is to be understood that numerous modifications can be made to the illustrative embodiments and that other arrangements can be devised without departing from the scope of the present invention as defined by the appended claims.
1. A prosthetic heart valve (100), comprising:
(a) a collapsible stent (10) for mounting in an administration and expandable device when implanted, which includes a generally tubular ring region (30) having a proximal-distal axis (14) when implanted;
(b) a valve element (70) mounted inside the stent and operative when implanted, to allow flow in the anterograde direction (D) through the ring region from a proximal end to a distal end; characterized by
(c) a sleeve (200) mounted on the stent, the sleeve including an inner wall, an outer wall outside the inner wall and outside the stent, and at least one pocket, the outer wall being arranged around the periphery of the ring region and having an edge oriented in the anterograde direction, where each pocket of the at least one pocket has an opening oriented in the anterograde direction when implanted cooperatively, defined by the inner wall and the edge of the outer wall, and the At least one pocket has a size and shape to be filled with blood with the bloody flow around the outside of the stent in a retrograde direction to predispose the outer wall to the coupling with a native valve ring to prevent perivalvular leakage.
2. The prosthetic heart valve (100) according to claim 1, wherein the inner wall extends in an anterograde direction beyond the edge of the outer wall.
3. The prosthetic heart valve (100) according to claim 1 or claim 2, wherein there is a plurality of openings, and the openings are arranged in the same plane perpendicular to the proximal-distal axis (14), and are arranged around the periphery of the stent.
4. The prosthetic heart valve (100) according to any one of claims 1 to 3, wherein the at least one pocket includes a plurality of pockets.
5. The prosthetic heart valve (100) according to any one of claims 1 to 4, wherein the stent is self-expanding.
6. The prosthetic heart valve (100) according to any one of claims 1 to 4, wherein the stent is balloon expandable.
7. A set for administering a prosthetic heart valve to an objective place in a patient, comprising:
(a) an administration device that has a shrink sleeve; Y
(b) the prosthetic heart valve (100) according to any one of claims 1 to 6, mounted on the administration device and covered by the sheath.
8. The assembly according to claim 7, wherein the administration device includes an expandable member for moving the stent from a collapsed state to an expanded state.
9. The assembly according to claim 8, wherein the expandable member is a balloon.
ES14180622.4T 2008-07-15 2009-07-15 Collapsible and re-expandable prosthetic heart valve sleeve designs and complementary technological applications Active ES2586111T3 (en)
US13499508P true 2008-07-15 2008-07-15
US134995P 2008-07-15
ES2586111T3 true ES2586111T3 (en) 2016-10-11
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ES14180623.2T Active ES2584315T3 (en) 2008-07-15 2009-07-15 Collapsible and re-expandable prosthetic heart valve sleeve designs and complementary technological applications
ES15201538.4T Active ES2616743T3 (en) 2008-07-15 2009-07-15 Collapsible and re-expandable prosthetic heart valve sleeve designs and complementary technological applications
ES15201540.0T Active ES2616693T3 (en) 2008-07-15 2009-07-15 Collapsible and re-expandable prosthetic heart valve sleeve designs and complementary technological applications
ES14180625T Active ES2570592T3 (en) 2008-07-15 2009-07-15 Collapsible and re-expandable prosthetic heart valve sleeve designs and complementary technological applications
ES14180622.4T Active ES2586111T3 (en) 2008-07-15 2009-07-15 Collapsible and re-expandable prosthetic heart valve sleeve designs and complementary technological applications
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EP3025680A1 (en) 2016-06-01
EP2299938A2 (en) 2011-03-30
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