Variable force stent design

Abstract

Disclosed are example embodiments of a stent. The stent is formed by cutting cells from a tubular shape. The tubular shape may include multiple distinct areas, including a first area configured to produce a strong radial force to expand, and a second area, adjacent to the first area, configured to produce a smaller radial force to expand. The strong radial force generated by the first area may be designed to provide significant support to the vessel walls, effectively maintaining patency in the targeted region. In contrast, the second area, which generates a smaller radial force relative to the first area, may be optimized to minimize pressure on adjacent sections of a vessel, reducing the risk of injury to those areas. This strategic distribution of radial forces within the stent structure may enable the stent to address varying levels of stenosis, offering both robust support and gentle expansion.

Description

VARIABLE FORCE STENT DESIGNCROSS-REFERENCE TO RELATED APPLICATION

[0001] This Patent Application claims priority to U.S. Provisional Patent Application No. 63 / 537,076, filed on September 7, 2023, and entitled “VARIABLE FORCE STENT DESIGN.” The disclosure of the prior Application is considered part of and is incorporated by reference into this Patent Application.TECHNICAL FIELD

[0002] The disclosure relates generally to the field of stents, and specifically and not by way of limitation, some embodiments are related to a variable force stent design.BACKGROUND

[0003] Intracranial artery stenosis is a narrowing of the arteries in the brain. This narrowing is usually the result of a build-up of plaque within the arteries, a condition called intracranial atherosclerosis. Intracranial artery stenosis can worsen over time to completely block the artery which may lead to stroke.

[0004] FIG. 7A is a diagram illustrating the need for an improved stent that addresses one or more issues with current self-expanding stents designs. Current self-expanding stents designed to treat arterial stenosis are designed around a repeating cell design that produces consistent radial force across the body of the stent. Producing consistent radial force across the body of the stent creates a uniform expansive radial force across the vessel. Intracranial stenosis is unique in that the diseased vessel is often focal, with a width of 4-5mm.

[0005] A need exists for an improved stent that addresses one or more issues with current selfexpanding stents designs. Thus, in the case of intracranial stenosis with the diseased vessel focal, a stent with concentrated expansive force in the center of the stent may be preferable, while the distal and proximal portions of the stent may only be necessary to aid in landing and stability of the stent implant, as illustrated in FIG. 7A.SUMMARY

[0006] In one example implementation, an embodiment includes a stent with concentrated expansive force in the center of the stent and distal and proximal portions of the stent may create a smaller radial force and may only be necessary to aid in landing and stability of the stent implant.

[0007] Disclosed are example embodiments of a stent including a shape formed by cutting cells from a, tubular shape having: a first area, the first area configured to produce a strong radial force to expand, and a second area, the second area configured to produce a smaller radial force to expand relative to the strong radial force to expand of the first area.

[0008] Disclosed are example embodiments of a stent including a shape formed by cutting cells from a tubular shape having: a first area, the first area configured to produce a strong radial force to expand, and a second area, the second area configured to produce a smaller radial force to expand relative to the strong radial force to expand of the first area. The stent further including a third area, the third area configured to produce a second smaller radial force to expand relative to the strong radial force to expand of the first area.

[0009] Disclosed are example embodiments of a stent including a shape formed by cutting cells from a tubular shape having: a first area of narrower struts, a second area of wider struts, next to the first area of narrower struts, and a third area of narrower struts, next to the second area of wider struts.

[0010] Disclosed are example embodiments of a stent including a shape formed by cutting cells from a tubular shape having: a distal area of narrower struts, a center area of wider struts, next to the distal area of narrower struts, and a proximal area of narrower struts, next to the center area of wider struts.

[0011] The features and advantages described in the specification are not all-inclusive. In particular, many additional features and advantages will be apparent to one of ordinary skill in the art in view of the drawings, specification, and claims. Moreover, it should be noted that the language used in the specification has been principally selected for readability and instructional purposes and may not have been selected to delineate or circumscribe the disclosed subject matter.BRIEF DESCRIPTION OF THE DRAWINGS

[0012] The foregoing summary, as well as the following detailed description, is better understood when read in conjunction with the accompanying drawings. The accompanying drawings, whichare incorporated herein and form part of the specification, illustrate a plurality of embodiments and, together with the description, further serve to explain the principles involved and to enable a person skilled in the relevant art(s) to make and use the disclosed technologies.

[0013] FIG. 1 is a diagram illustrating an example stent in accordance with the systems and methods described herein.

[0014] FIG. 2 is a diagram further illustrating the example stent of FIG. 1 in accordance with the systems and methods described herein.

[0015] FIG. 3 is a diagram illustrating another example stent in accordance with the systems and methods described herein.

[0016] FIG. 4 is a diagram illustrating another example stent in accordance with the systems and methods described herein.

[0017] FIG. 5 is a diagram further illustrating the example stent of FIG. 1 in accordance with the systems and methods described herein.

[0018] FIG. 6 is a diagram illustrating example placement of the example stent of FIG. 1 in accordance with the systems and methods described herein.

[0019] As discussed above, FIG. 7A is a diagram illustrating the need for an improved stent that addresses one or more issues with current self-expanding stents designs discussed above.

[0020] FIG. 7B is a diagram illustrating example placement of the example stents of FIGS. 1-6 in accordance with the systems and methods described herein. The example stent of FIG. 7B (and FIGS. 1-5).

[0021] The figures and the following description describe certain embodiments by way of illustration only. One skilled in the art will readily recognize from the following description that alternative embodiments of the structures and methods illustrated herein may be employed without departing from the principles described herein. Reference will now be made in detail to several embodiments, examples of which are illustrated in the accompanying figures. It is noted that wherever practicable similar or like reference numbers may be used in the figures to indicate similar or like functionality.DETAILED DESCRIPTION

[0022] FIG. 1 is a diagram illustrating an example stent 100 in accordance with the systems and methods described herein. The embodiment of FIG. 1 includes a stent 100 with a concentratedexpansive force in its center, while the distal portion 104 and proximal portion 104 generate smaller radial forces, primarily aiding in the landing and stability of the stent implant. The stent 100 may include a tubular shape formed by cutting cells 108 from a tubular shape. The tubular shape may have a first area of narrower struts, a second area of wider struts, next to the first area of narrower struts, and a third area of narrower struts, next to the second area of wider struts.

[0023] In some embodiments, the first area of narrower struts and the third area of narrower struts may be a distal portion 104 of the stent 100 and a proximal portion 106 of the stent 100 or a proximal portion 106 of the stent 100 and a distal portion 104 of the stent 100, respectively. The distal and proximal portion 106 of the stent 100 may generate a smaller radial force compared to the center of the stent 100. For example, the central segment 102 may exert an outward radial force of approximately 1.8 N / cm, while the distal portion 104 and the proximal portion 106 may exert an outward radial force of approximately 0.67 N / cm. The radial force of the distal portion 104 and the proximal portion 106 may range from 20% to 90% of the radial force of the center segment 102. The second area of wider struts may be next to the first area of narrower struts and the third area of narrower struts may be the center of the stent 100, as in the illustrated example of FIG. 1. However, it will be understood that different combinations of narrower struts and wider struts producing smaller radial forces and larger radial forces are contemplated.

[0024] In some embodiments, the stent 100 may be constructed using a combination of materials that offer both flexibility and strength. For example, nitinol, known for its superelastic properties and shape memory, can be used to create the central portion of the stent 100 where a higher radial force is required. The proximal portion 106 and the distal portion, which require less force, can be constructed from stainless steel or cobalt-chromium alloys, providing the necessary structural support while maintaining overall stent flexibility.

[0025] In selecting materials for the stent 100, important considerations may include balancing flexibility with the mechanical strength required to withstand the dynamic environment of intracranial arteries. Nitinol, a nickel -titanium alloy known for its superelasticity and shape memory properties, is particularly suitable for the central portion of the stent 100. Nitinol’s ability to endure large deformations and return to its original shape ensures the stent can be delivered through tortuous vessels and then expand to its intended form. Stainless steel and cobalt-chromium alloys may be utilized in the distal and proximal portions of the stent 100, where reduced radial force is advantageous. These materials may offer the structural rigidity needed to stabilize the stentwithin the artery while providing the flexibility necessary for the vessel’s natural movement. The selection of these materials may also take into account their established biocompatibility, reducing the risk of adverse reactions post-implantation.

[0026] Additionally, the stent design may incorporate different strut geometries in various sections of the stent 100. The central portion may feature wider struts to enhance radial force, while the end sections may use narrower struts to allow for smoother expansion and better accommodation to the vessel's natural curvature. This configuration ensures that the stent 100 can be delivered efficiently through tortuous vascular pathways and deployed accurately at the site of the stenosis.

[0027] The manufacturing process for stent 100 may involve precision laser cutting, which may be instrumental in achieving the intricate patterns necessary for varying radial forces. The laser cutting parameters, including wavelength, intensity, and speed, may be optimized to minimize thermal damage to the surrounding material. Following the cutting process, the stent may undergo electropolishing, a process that removes microscopic burrs and smoothens the surface of the stent, which may reduce the risk of thrombus formation. Electropolishing may not only enhances the stent’s biocompatibility but may also improves the stent’s durability by possibly eliminating potential stress concentrators that could lead to structural failure over time. This manufacturing sequence may support the retention of the stent 100's designed mechanical properties and performance throughout its intended lifespan.

[0028] As illustrated in FIG. 1, the stent 100 may be laser cut. For example, a sheet of material may have material cut away using the laser and leaving a stent behind. The stent 100 may eventually be expanded, e.g., in an artery, as discussed with respect to FIGS. 6-7.

[0029] In certain embodiments, the stent 100 may be coated with drug-eluting layers designed to prevent restenosis by releasing medications, such as sirolimus or paclitaxel, over an extended period. The drug-eluting coatings can be selectively applied to the central portion of the stent 100, where restenosis is most likely to occur, thereby minimizing the risk of artery re-narrowing while reducing systemic drug exposure. Additionally, the drug-eluting layer can be optimized to deliver a controlled dosage of the therapeutic agent, tailored to the specific needs of the treated artery. This customization can be achieved through varying the thickness of the coating or by using different polymer matrices that control the release rate of the drug. This targeted approach enhances the efficacy of the stent 100 in preventing restenosis while maintaining a favorable safety profile.

[0030] In some embodiments, the drug-eluting layer that may be on the stent 100 may play a role in preventing restenosis. In an example, a polymer matrix may house the therapeutic agents may be engineered to release drugs such as sirolimus or paclitaxel at a controlled rate, which may ensure consistent therapeutic levels are maintained within the vessel wall. The thickness of this layer may be strategically varied along the stent’s length to address the areas of highest restenosis risk, typically in regions of high radial force. This approach may minimize systemic drug exposure, reducing the likelihood of adverse effects while enhancing the efficacy of the localized treatment. Moreover, the polymer matrix may be designed to degrade at specific rates, providing sustained drug release over weeks or months, depending on the clinical situation.

[0031] FIG. 2 is a diagram further illustrating the example stent 100 of FIG. 1 in accordance with the systems and methods described herein. In the illustrated example embodiment, the width of the middle strut sections may be wider than the width at the edges. The structure may have the width of the middle strut sections wider than the width at the edges. Having the width of the middle strut sections wider than the width at the edges may make the radial force at the middle higher than the radial force at the edges. A two-dimensional representation of an example laser cut pattern is illustrated in FIG. 2. In the illustrated example of FIG. 2, the middle strut sections may have widths of 80pm (0.080mm) while the external edges may have a width of 60pm (0.060mm). It will be understood, however, that the middle strut sections may have other widths, such as 60pm (0.060mm) to 100pm (, 100mm) while the external edges may have a width of 40pm (0.040mm) to 80pm (0.080mm).

[0032] The stent 100 may be tailored to meet the specific anatomical and pathological needs of individual patients. For instance, in cases where arterial stenosis is more pronounced, the stent may be designed with additional sections of wider struts in the central area, thereby providing increased radial force. Conversely, for less severe stenosis, the stent may be configured with more uniform strut widths to deliver a balanced radial force throughout its length. This customization may also apply to the stent's overall length and diameter, allowing the stent to be adjusted to fit the precise dimensions of the patient’s artery. This adaptability may help ensure that the stent 100 provides optimal support across a range of clinical scenarios, from minor narrowing to significant arterial blockages.

[0033] The stent 100 may also include radiopaque markers that are integrated into the design to enhance visibility during imaging procedures, such as X-ray or fluoroscopy. These markers arestrategically placed at the ends or along the length of the stent 100, ensuring precise placement and deployment within the artery. Radiopaque markers are particularly beneficial in complex procedures, such as those involving intracranial arteries, where accurate positioning of the stent 100 is critical to the success of the treatment.

[0034] In addition to radiopaque markers, the stent's design may feature zones of varying flexibility. For example, the central portion of the stent 100, which requires higher radial force, may be designed with stiffer struts, while the proximal portion 106 and distal portion 104 may have more flexible struts. This variation in stiffness allows the stent 100 to conform to the natural shape of the artery, reducing the risk of vessel trauma and improving overall patient outcomes.

[0035] FIG. 3 is a diagram illustrating another example stent 300 in accordance with the systems and methods described herein. Another method to create a variable radial force stent may be with asymmetry in the design of the cells. Cells with smaller areas 304 may effectively give the struts shorter lever arms 302 compared to the neighboring cells 304, which may have larger areas which may effectively give these struts longer lever arms. The struts shorter lever arms 302 may increase the radial force in the middle of the stent 300.

[0036] While the stent 100 may be designed to address the challenges of intracranial artery stenosis, potential complications such as stent migration and incomplete expansion may arise during deployment. The design, which, in some embodiments, may feature varying radial forces, may mitigate these issues by ensuring the stent anchors firmly at the stenosis site while expanding sufficiently to maintain vessel patency. The stronger radial force in the central portion may counteract the pressure of the plaque, promoting stable positioning of the stent, while the reduced force at the ends may minimize trauma to surrounding healthy tissues. Additionally, the flexible design may allow the stent to conform to the natural curvature of the artery, which may reduce the likelihood of vessel trauma or improper stent placement.

[0037] For certain applications, the stent 300 may be designed to be bioresorbable, meaning that it gradually dissolves in the body after serving its purpose. Bioresorbable stents are made from polymers such as polylactic acid (PLA) or polyglycolic acid (PGA), which degrade over time, leaving behind a naturally healed vessel. This approach can be particularly beneficial in treating conditions where temporary support is sufficient, and long-term implantation of foreign material is not desirable.

[0038] The bioresorbable stent 300 can also be designed with drug-eluting properties, combining mechanical support with localized drug delivery. As the stent 300 degrades, it releases therapeutic agents that prevent restenosis, promoting healing while gradually reducing the foreign material load on the artery. This dual-functionality offers an advanced solution for managing arterial stenosis with a focus on long-term patient safety and efficacy. Additionally, the design of the stent 300 can incorporate variable radial force zones, further enhancing its adaptability to different clinical scenarios.

[0039] FIG. 4 is a diagram illustrating another example stent in accordance with the systems and methods described herein. The amount of radial force fall-off may be increased by additional asymmetry, creating cells of increasing size. In the illustrated example, the smallest cells are in the middle 402, increasing to the cells 404, and finally increasing to the cells 406. The area of each cell are cells 402 have less area than cells 404 which have less area than cells 406. The struts' shorter lever arms 402 may increase the radial force in the middle of the stent, with the amount of radial force falling off from there.

[0040] FIG. 5 is a diagram further illustrating the example stent 100 of FIG. 1 in accordance with the systems and methods described herein. FIG. 5 illustrates the stent 100 in a first, unexpanded state. In some example embodiments, the stent 100 may be manufactured in the first, unexpanded state. In some example embodiments, the stent 100 may be shipped in the first, unexpanded state. In some example embodiments, the stent 100 may be implanted into an artery in the first, unexpanded state. After the stent 100 gets to the portion of the artery where it is intended to be installed, the stent 100 may be expanded from the first, unexpanded state, to a second, expanded state. As one example, the stent 100 may expand as an “as cut stent” from 2.0 mm diameter to 5.5 mm diameter maximum in one example embodiment. However, a multitude of other sized stents are possible. The stent 100 is also illustrated in the second, expanded stated in FIG. 5.

[0041] The stent 100 illustrated in FIG. 5 may exhibit a concentrated expansive force in its central portion, with the distal and proximal sections generating smaller radial forces, primarily aiding in the landing and stability of the stent implant. The stent 100 depicted in FIG. 5 may be formed by cutting cells from a tubular shape.

[0042] In some embodiments, the customization of the stent 100 may be further refined based on pre-procedural imaging data. Advanced imaging techniques such as high-resolution MRI, CT angiography, or intravascular ultrasound (IVUS) may be used to generate detailed models of thepatient’s vascular anatomy. These models may help clinicians select the optimal stent configuration, including length, diameter, and radial force distribution, tailored to the specific characteristics of the target vessel. For instance, in cases where the vessel exhibits significant calcification or tortuosity, a stent with enhanced flexibility and gradual radial force variation may be selected to ensure proper deployment and long-term patency. This patient-specific approach may improve procedural outcomes by reducing the likelihood of complications such as stent migration, malapposition, or restenosis.

[0043] Once the optimal stent configuration has been determined, the deployment process may involve the use of a specialized delivery system designed to ensure precise placement within the target vessel. The delivery system may incorporate features such as an adjustable catheter tip and real-time imaging feedback to guide the stent through complex vascular pathways. During deployment, the stent 100 may be carefully navigated to the site of the stenosis, where it may be gradually expanded to conform to the vessel walls. The expansion process may be monitored in real-time using fluoroscopy or intravascular ultrasound to ensure that the stent is properly positioned and fully apposed to the vessel wall.

[0044] After the stent 100 has been deployed, post-implantation monitoring may be critical to assess the long-term efficacy of the intervention. Patients may undergo periodic follow-up imaging studies, such as angiography or duplex ultrasound, to evaluate the stent's patency and detect any signs of restenosis or other complications. In cases where restenosis is observed, adjunctive therapies such as balloon angioplasty or additional stenting may be employed to restore vessel patency. Additionally, patients may be prescribed antiplatelet or anticoagulant medications to reduce the risk of thrombus formation within the stent. The combination of these post-implantation strategies may help to ensure the long-term success of the stent and the overall health of the patient.

[0045] In some advanced applications, the stent 100 may be integrated with sensor technologies that allow for continuous monitoring of the vessel's condition. These sensors may be embedded within the stent's structure and capable of transmitting real-time data on parameters such as blood flow, pressure gradients, and endothelial cell health. This data may be wirelessly transmitted to an external monitoring device, where it may be analyzed to detect early signs of restenosis or other complications. Such a system may enable proactive management of the patient’s condition, allowing for timely interventions that could prevent the progression of vascular disease and improve long-term outcomes.

[0046] FIG. 6 is a diagram 600 illustrating example placement of the example stents of FIGS. 1-5 in accordance with the systems and methods described herein. FIG. 6 illustrates intracranial arteries. Intracranial arteries may be more torturous, and it may be harder to deliver a stent, e.g., as compared to stent delivery in a carotid artery. The carotid artery is generally not torturous and it may be easier to deliver a stent to the carotid artery. The stents 100, 300 described herein may be used in conjunction with various structures of the body. Some examples include, but are not limited to the anterior communicating artery, posterior communicating artery, facial artery, lingual artery, anterior cerebral artery, middle cerebral artery, ophthalmic artery, posterior cerebral artery, basilar artery, Anterior Inferior Cerebellar Artery (AICA), Posterior Inferior Cerebellar Artery (PICA), vertebral artery, internal carotid artery, external carotid artery, common carotid artery, subclavian artery, and / or innominate artery.

[0047] The tortuous nature of intracranial arteries presents unique challenges for stent delivery. As stents navigate these complex pathways, they must maintain structural integrity and flexibility to avoid complications such as vessel damage or misplacement. The design of the stents described herein, with varying radial force distribution and flexible strut geometries, ensures that they can adapt to the intricate curves and bends of the intracranial arteries. This adaptability is critical for successful deployment in these high-risk areas, where traditional stents may falter.

[0048] The distribution of radial force along the length of the stent is crucial for its effectiveness in treating intracranial stenosis. The central portion of the stent exerts a stronger radial force to ensure adequate vessel expansion and plaque stabilization, while the distal and proximal ends exert lower forces to minimize the risk of trauma to the surrounding healthy tissue. This strategic distribution not only aids in the initial placement of the stent but also enhances long-term outcomes by reducing the likelihood of restenosis or stent migration.

[0049] While the stents described herein are particularly well-suited for intracranial arteries, their design principles can be applied to other complex vascular regions as well. For instance, these stents can be used in peripheral arteries, coronary arteries, and other vessels where precise radial force distribution is necessary to prevent complications such as vessel collapse or excessive expansion. The versatility of the stent design allows it to be tailored to various clinical scenarios, making it a valuable tool in the treatment of a wide range of vascular diseases.

[0050] In some examples, a stent 652 may be delivered in a microcatheter. The stent 650 may be any of the example stents of FIGS. 1-5. In an example, the stent may be an Intracranial Atherosclerotic Disease (ICAD) stent.

[0051] The stents 100, 300 described herein are compatible with various microcatheter systems, allowing for precise delivery in narrow and tortuous vessels. The flexibility and variable radial force of these stents ensure that they can be navigated through the microcatheter without causing excessive friction or resistance. This compatibility is crucial for procedures that require high precision, such as the treatment of intracranial atherosclerotic disease (ICAD).

[0052] By optimizing the design of the stent for both flexibility and radial force distribution, the disclosed embodiments aim to improve long-term patient outcomes. The ability of the stent to conform to the natural anatomy of the vessel while providing sufficient support to prevent restenosis is a significant advancement over traditional stent designs. Moreover, the drug-eluting capabilities of the stents further enhance their efficacy, reducing the need for repeat interventions and improving overall patient prognosis.

[0053] In some cases, a stent may need to be customized to address specific patient anatomy or disease conditions. The modular design of the stents allows for adjustments in strut width, material composition, and drug-eluting properties, enabling healthcare providers to tailor the stent to the unique needs of each patient. This level of customization ensures that the stent not only addresses the current stenosis but also provides a durable solution that accommodates potential changes in the vessel over time.

[0054] The stent 650 may deliver a variable radial force 654 (the radial force 654 may generally occur along the entire stent, e.g., at points where the wires make contact with a wall. However, symbolically, the radial force is represented by radial force 654 arrows in FIG. 6). The stronger the radio force, the more the stent pushes against the inner wall of the micro catheter, making it harder for the stent to move forward.

[0055] As discussed above, FIG. 7A is a diagram illustrating the need for an improved stent that addresses one or more issues with current self-expanding stents designs discussed above. Current self-expanding stents designed to treat arterial stenosis are designed around a repeating cell design that produces consistent radial force across the body of the stent. Producing consistent radial force across the body of the stent creates a uniform expansive radial force across the vessel.

[0056] In the case of intracranial stenosis with the diseased vessel focal, a stent with concentrated expansive force in the center of the stent may be preferable, while the distal and proximal portions of the stent may only be necessary to aid in landing and stability of the stent implant, as illustrated in FIG. 7A. As illustrated in FIG. 7A, an artery 700 may be such that a stronger radial force may be required in a portion of an artery 702.

[0057] The area 704 on either side of the portion of the artery 702 that requires the stronger radial force may not require the stronger radial force. Rather, the area 704 on either side of the portion of the artery 702 that requires the stronger radial force may just need to aid in the landing and stability of the stent implant. Note, however, that reference to a portion of an artery 702 that requires the stronger radial force is not intended to indicate that no other portions of the artery (or portions of other arteries) will need such stenting. For example, multiple arteries may need such stenting due to intracranial atherosclerosis disease. Additionally, some arteries may have multiple areas that may need such stenting due to intracranial atherosclerosis disease. Areas where strong radial force is required to expand may be separated by areas that do not require strong radial force. These areas that do not require strong radial force may provide enough space that some areas are not stented at all, while other areas, e.g., adjacent to areas where strong radial forces are required, may aid in landing and stability of the stent implant.

[0058] FIG. 7B is a diagram illustrating example placement of the example stent of FIGS. 1-6 in accordance with the systems and methods described herein. The stent may provide an area of stronger radial force and an area of smaller radial force. In the illustrated example of FIG. 7B, the area of stronger radial force may generally be in the center of the stent. In the illustrated example of FIG. 7B, the area of smaller radial force may generally be on each side of the center of the stent. In other words, the area of smaller radial force may generally be on each side of the area of stronger radial force of the stent.

[0059] In some examples, a stent may be custom designed based on the issues in a particular artery 700 of a particular patient. For example, the width of the area producing stronger radial force may vary, and similarly, the width of the area producing smaller radial force may also vary. In some examples, the width of each area of smaller radial force may vary relative to each other, e.g., one side having smaller radial force may be wider than another side having smaller radial force. In some examples, the width of the areas of smaller radial force may vary relative to the area ofstronger radial force. In some examples, stents may have multiple areas of stronger and / or smaller radial force, e.g., based on the condition of a particular artery that the stent may be installed in.

[0060] An example embodiment may be a stent including a shape formed by cutting cells from a tubular shape. The tubular shape may have a first area. The first area may be configured to produce a strong radial force to expand. The stent may have a second area. The second area may be configured to produce a smaller radial force to expand relative to the strong radial force to expand of the first area.

[0061] In an example embodiment, the stent may further include a third area. The third area may be configured to produce a second smaller radial force to expand relative to the strong radial force to expand of the first area.

[0062] In an example embodiment, the stent may include the first area, centered between the second area and the third area.

[0063] In an example embodiment, the stent may include a first smaller radial force that equals the second smaller radial force.

[0064] In an example embodiment, the stent may include three zones of radial force, with two zones of radial force being equal.

[0065] In an example embodiment, the stent may include an additional zone of radial force.

[0066] In an example embodiment, a stent may include a shape formed by cutting cells from a tubular shape. The tubular shape may have a distal area of narrower struts, a center area of wider struts, next to the distal area of narrower struts, and a proximal area of narrower struts, next to the center area of wider struts.

[0067] In an example embodiment, the distal area and the proximal area may be configured to produce smaller radial forces to expand relative to a strong radial force to expand the center area.

[0068] In an example embodiment, the center area may be centered between the proximal area and the distal area.

[0069] In an example embodiment, the smaller radial forces of the distal area and the proximal area may be equal.

[0070] In an example embodiment, the stent may include three zones of radial force, with two zones of radial force being equal.

[0071] In an example embodiment, the stent may further include an additional zone of radial force.

[0072] In an example embodiment, a stent may include a shape formed from by cutting cells from a tubular shape. The tubular shape may have a first area of narrower struts, a second area of wider struts, next to the first area of narrower struts, and a third area of narrower struts, next to the second area of wider struts.

[0073] In an example embodiment, the first area and the third area may be configured to produce smaller radial forces to expand relative to strong radial force to expand the second area.

[0074] In an example embodiment, the second area may be centered between the first area and the second area.

[0075] In an example embodiment, the smaller radial forces of the first area and the third area are equal.

[0076] In an example embodiment, the stent may include three zones of radial force, with two zones of radial force being equal.

[0077] In one embodiment, the stent may further include an additional zone with a distinct radial force.

[0078] In an example embodiment, the stent may further include another additional zone of radial force.

[0079] One or more elements or aspects or steps, or any portion(s) thereof, from one or more of any of the systems and methods described herein may be combined with one or more elements or aspects or steps, or any portion(s) thereof, from one or more of any of the other systems and methods described herein and combinations thereof, to form one or more additional implementations and / or claims of the present disclosure.

[0080] One or more of the components, steps, features, and / or functions illustrated in the figures may be rearranged and / or combined into a single component, block, feature or function or embodied in several components, steps, or functions. Additional elements, components, steps, and / or functions may also be added without departing from the disclosure. The apparatus, devices, and / or components illustrated in the Figures may be configured to perform one or more of the methods, features, or steps described in the Figures. The algorithms described herein may also be efficiently implemented in software and / or embedded in hardware.

[0081] Reference in the specification to “one embodiment” or “an embodiment” means that a particular feature, structure, or characteristic described in connection with the embodiment is included in at least one embodiment of the invention. The appearances of the phrase “in oneembodiment” in various places in the specification are not necessarily all referring to the same embodiment.

[0082] The foregoing description of the embodiments of the present invention has been presented for the purposes of illustration and description. It is not intended to be exhaustive or to limit the present invention to the precise form disclosed. Many modifications and variations are possible in light of the above teaching. It is intended that the scope of the present invention be limited not by this detailed description, but rather by the claims of this application. As will be understood by those familiar with the art, the present invention may be embodied in other specific forms without departing from the spirit or essential characteristics thereof. Likewise, the particular naming and division of the modules, routines, features, attributes, methodologies and other aspects are not mandatory or significant, and the mechanisms that implement the present invention or its features may have different names, divisions and / or formats.

[0083] The previous description is provided to enable any person skilled in the art to practice the various aspects described herein. Various modifications to these aspects will be readily apparent to those skilled in the art, and the generic principles defined herein may be applied to other aspects. Thus, the claims are not intended to be limited to the aspects shown herein, but is to be accorded the full scope consistent with the language claims, wherein reference to an element in the singular is not intended to mean “one and only one” unless specifically so stated, but rather “one or more.” The word “exemplary” is used herein to mean “serving as an example, instance, or illustration.” Any aspect described herein as “exemplary” is not necessarily to be construed as preferred or advantageous over other aspects. Unless specifically stated otherwise, the term “some” refers to one or more. Combinations such as “at least one of A, B, or C,” “one or more of A, B, or C,” “at least one of A, B, and C,” “one or more of A, B, and C,” and “A, B, C, or any combination thereof’ include any combination of A, B, and / or C, and may include multiples of A, multiples of B, or multiples of C. Specifically, combinations such as “at least one of A, B, or C,” “one or more of A,B, or C,” “at least one of A, B, and C,” “one or more of A, B, and C,” and “A, B, C, or any combination thereof’ may be A only, B only, C only, A and B, A and C, B and C, or A and B andC, where any such combinations may contain one or more member or members of A, B, or C. All structural and functional equivalents to the elements of the various aspects described throughout this disclosure that are known or later come to be known to those of ordinary skill in the art are expressly incorporated herein by reference and are intended to be encompassed by the claims.Moreover, nothing disclosed herein is intended to be dedicated to the public regardless of whether such disclosure is explicitly recited in the claims. The words “module,” “mechanism,” “element,” “device,” and the like may not be a substitute for the word “means.” As such, no claim element is to be construed as a means plus function unless the element is expressly recited using the phrase “means for.”

Claims

CLAIMSWHAT IS CLAIMED IS:

1. A stent comprising: a shape formed by cutting cells from a tubular shape, the tubular shape having: a first area, the first area configured to produce a strong radial force to expand, and a second area, the second area configured to produce a smaller radial force to expand relative to the strong radial force to expand of the first area.

2. The stent of claim 1, further comprising a third area, the third area configured to produce a second smaller radial force to expand relative to the strong radial force to expand of the first area.

3. The stent of claim 2, wherein the first area is centered between the second area and the third area.

4. The stent of claim 2, wherein the smaller radial force equals the second smaller radial force.

5. The stent of claim 2, wherein the stent includes three zones of radial force, with two zones of radial force being equal.

6. The stent of claim 5, further comprising an additional zone of radial force.

7. A stent comprising: a shape formed by cutting cells from a tubular shape, the tubular shape having: a distal area of narrower struts; a center area of wider struts, next to the distal area of narrower struts; and a proximal area of narrower struts, next to the center area of wider struts.

8. The stent of claim 7, wherein the distal area and the proximal area are configured to produce smaller radial forces to expand relative to a strong radial force to expand the center area.

9. The stent of claim 8, wherein the center area is centered between the proximal area and the distal area.

10. The stent of claim 8, wherein the smaller radial forces of the distal area and the proximal area are equal.

11. The stent of claim 7, wherein the stent includes three zones of radial force, with two zones of radial force being equal.

12. The stent of claim 11, further comprising an additional zone of radial force.

13. A stent compri sing : a shape formed by cutting cells from a tubular shape, the tubular shape having: a first area of narrower struts; a second area of wider struts, next to the first area of narrower struts; and a third area of narrower struts, next to the second area of wider struts.

14. The stent of claim 13, wherein the first area and the third area are configured to produce smaller radial forces to expand relative to strong radial force to expand the second area.

15. The stent of claim 14, wherein the second area is centered between the first area and the second area.

16. The stent of claim 14, wherein the smaller radial forces of the first area and the third area are equal.

17. The stent of claim 13, wherein the stent includes three zones of radial force, with two zones of radial force being equal.

18. The stent of claim 17, further comprising an additional zone of radial force.

19. The stent of claim 18, further comprising another additional zone of radial force.

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