US20020144757A1 - Stainless steel alloy with improved radiopaque characteristics - Google Patents
Stainless steel alloy with improved radiopaque characteristics Download PDFInfo
- Publication number
- US20020144757A1 US20020144757A1 US10/103,411 US10341102A US2002144757A1 US 20020144757 A1 US20020144757 A1 US 20020144757A1 US 10341102 A US10341102 A US 10341102A US 2002144757 A1 US2002144757 A1 US 2002144757A1
- Authority
- US
- United States
- Prior art keywords
- alloy
- stainless steel
- steel alloy
- series
- austenitic
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Abandoned
Links
- 229910001256 stainless steel alloy Inorganic materials 0.000 title claims abstract description 11
- 229910045601 alloy Inorganic materials 0.000 claims abstract description 52
- 239000000956 alloy Substances 0.000 claims abstract description 52
- 229910001220 stainless steel Inorganic materials 0.000 claims abstract description 34
- 239000010935 stainless steel Substances 0.000 claims abstract description 22
- KDLHZDBZIXYQEI-UHFFFAOYSA-N Palladium Chemical compound [Pd] KDLHZDBZIXYQEI-UHFFFAOYSA-N 0.000 claims abstract description 7
- 229910052741 iridium Inorganic materials 0.000 claims abstract description 7
- BASFCYQUMIYNBI-UHFFFAOYSA-N platinum Chemical compound [Pt] BASFCYQUMIYNBI-UHFFFAOYSA-N 0.000 claims abstract description 7
- GKOZUEZYRPOHIO-UHFFFAOYSA-N iridium atom Chemical compound [Ir] GKOZUEZYRPOHIO-UHFFFAOYSA-N 0.000 claims abstract description 6
- 239000010931 gold Substances 0.000 claims abstract description 4
- PCHJSUWPFVWCPO-UHFFFAOYSA-N gold Chemical compound [Au] PCHJSUWPFVWCPO-UHFFFAOYSA-N 0.000 claims abstract description 3
- 229910052737 gold Inorganic materials 0.000 claims abstract description 3
- 229910052762 osmium Inorganic materials 0.000 claims abstract description 3
- SYQBFIAQOQZEGI-UHFFFAOYSA-N osmium atom Chemical compound [Os] SYQBFIAQOQZEGI-UHFFFAOYSA-N 0.000 claims abstract description 3
- 229910052763 palladium Inorganic materials 0.000 claims abstract description 3
- 229910052697 platinum Inorganic materials 0.000 claims abstract description 3
- 229910052702 rhenium Inorganic materials 0.000 claims abstract description 3
- WUAPFZMCVAUBPE-UHFFFAOYSA-N rhenium atom Chemical compound [Re] WUAPFZMCVAUBPE-UHFFFAOYSA-N 0.000 claims abstract description 3
- 229910052715 tantalum Inorganic materials 0.000 claims abstract description 3
- GUVRBAGPIYLISA-UHFFFAOYSA-N tantalum atom Chemical compound [Ta] GUVRBAGPIYLISA-UHFFFAOYSA-N 0.000 claims abstract description 3
- WFKWXMTUELFFGS-UHFFFAOYSA-N tungsten Chemical compound [W] WFKWXMTUELFFGS-UHFFFAOYSA-N 0.000 claims abstract description 3
- 229910052721 tungsten Inorganic materials 0.000 claims abstract description 3
- 239000010937 tungsten Substances 0.000 claims abstract description 3
- XEEYBQQBJWHFJM-UHFFFAOYSA-N Iron Chemical compound [Fe] XEEYBQQBJWHFJM-UHFFFAOYSA-N 0.000 claims description 17
- ZOKXTWBITQBERF-UHFFFAOYSA-N Molybdenum Chemical compound [Mo] ZOKXTWBITQBERF-UHFFFAOYSA-N 0.000 claims description 11
- 229910052750 molybdenum Inorganic materials 0.000 claims description 11
- 239000011733 molybdenum Substances 0.000 claims description 11
- 229910052742 iron Inorganic materials 0.000 claims description 9
- 229910000851 Alloy steel Inorganic materials 0.000 claims description 8
- 238000005260 corrosion Methods 0.000 abstract description 9
- 230000007797 corrosion Effects 0.000 abstract description 8
- 239000011651 chromium Substances 0.000 description 23
- PXHVJJICTQNCMI-UHFFFAOYSA-N Nickel Chemical compound [Ni] PXHVJJICTQNCMI-UHFFFAOYSA-N 0.000 description 15
- 229910001566 austenite Inorganic materials 0.000 description 14
- 229910000831 Steel Inorganic materials 0.000 description 13
- 239000010959 steel Substances 0.000 description 13
- 229910052804 chromium Inorganic materials 0.000 description 11
- IJGRMHOSHXDMSA-UHFFFAOYSA-N Atomic nitrogen Chemical compound N#N IJGRMHOSHXDMSA-UHFFFAOYSA-N 0.000 description 10
- 229910052799 carbon Inorganic materials 0.000 description 10
- 239000011572 manganese Substances 0.000 description 10
- 238000000034 method Methods 0.000 description 10
- 229910052748 manganese Inorganic materials 0.000 description 9
- 229910052759 nickel Inorganic materials 0.000 description 8
- OKTJSMMVPCPJKN-UHFFFAOYSA-N Carbon Chemical compound [C] OKTJSMMVPCPJKN-UHFFFAOYSA-N 0.000 description 7
- VYZAMTAEIAYCRO-UHFFFAOYSA-N Chromium Chemical compound [Cr] VYZAMTAEIAYCRO-UHFFFAOYSA-N 0.000 description 7
- PWHULOQIROXLJO-UHFFFAOYSA-N Manganese Chemical compound [Mn] PWHULOQIROXLJO-UHFFFAOYSA-N 0.000 description 7
- 229910052757 nitrogen Inorganic materials 0.000 description 7
- 230000002411 adverse Effects 0.000 description 6
- 230000008901 benefit Effects 0.000 description 5
- 239000000463 material Substances 0.000 description 5
- 238000002844 melting Methods 0.000 description 5
- 230000008018 melting Effects 0.000 description 5
- 229910000617 Mangalloy Inorganic materials 0.000 description 4
- 230000014509 gene expression Effects 0.000 description 4
- 239000000203 mixture Substances 0.000 description 4
- 238000012986 modification Methods 0.000 description 4
- 230000004048 modification Effects 0.000 description 4
- -1 chromium carbides Chemical class 0.000 description 3
- OGSYQYXYGXIQFH-UHFFFAOYSA-N chromium molybdenum nickel Chemical compound [Cr].[Ni].[Mo] OGSYQYXYGXIQFH-UHFFFAOYSA-N 0.000 description 3
- VNNRSPGTAMTISX-UHFFFAOYSA-N chromium nickel Chemical compound [Cr].[Ni] VNNRSPGTAMTISX-UHFFFAOYSA-N 0.000 description 3
- 238000005336 cracking Methods 0.000 description 3
- 239000006104 solid solution Substances 0.000 description 3
- 239000000243 solution Substances 0.000 description 3
- 238000005482 strain hardening Methods 0.000 description 3
- 238000005728 strengthening Methods 0.000 description 3
- 230000007704 transition Effects 0.000 description 3
- 239000010963 304 stainless steel Substances 0.000 description 2
- 229910000619 316 stainless steel Inorganic materials 0.000 description 2
- XKRFYHLGVUSROY-UHFFFAOYSA-N Argon Chemical compound [Ar] XKRFYHLGVUSROY-UHFFFAOYSA-N 0.000 description 2
- OAICVXFJPJFONN-UHFFFAOYSA-N Phosphorus Chemical compound [P] OAICVXFJPJFONN-UHFFFAOYSA-N 0.000 description 2
- 229910000589 SAE 304 stainless steel Inorganic materials 0.000 description 2
- NINIDFKCEFEMDL-UHFFFAOYSA-N Sulfur Chemical compound [S] NINIDFKCEFEMDL-UHFFFAOYSA-N 0.000 description 2
- 238000005275 alloying Methods 0.000 description 2
- 229910000963 austenitic stainless steel Inorganic materials 0.000 description 2
- 230000015572 biosynthetic process Effects 0.000 description 2
- 230000002939 deleterious effect Effects 0.000 description 2
- 238000010438 heat treatment Methods 0.000 description 2
- 150000001247 metal acetylides Chemical class 0.000 description 2
- 229910052698 phosphorus Inorganic materials 0.000 description 2
- 239000011574 phosphorus Substances 0.000 description 2
- 238000001556 precipitation Methods 0.000 description 2
- 210000002307 prostate Anatomy 0.000 description 2
- 238000010791 quenching Methods 0.000 description 2
- 230000000171 quenching effect Effects 0.000 description 2
- 238000007670 refining Methods 0.000 description 2
- 229910052710 silicon Inorganic materials 0.000 description 2
- 239000000126 substance Substances 0.000 description 2
- 229910052717 sulfur Inorganic materials 0.000 description 2
- 239000011593 sulfur Substances 0.000 description 2
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 description 2
- 229910000859 α-Fe Inorganic materials 0.000 description 2
- 241000269350 Anura Species 0.000 description 1
- 241001465754 Metazoa Species 0.000 description 1
- 206010070834 Sensitisation Diseases 0.000 description 1
- VVTSZOCINPYFDP-UHFFFAOYSA-N [O].[Ar] Chemical compound [O].[Ar] VVTSZOCINPYFDP-UHFFFAOYSA-N 0.000 description 1
- 238000010521 absorption reaction Methods 0.000 description 1
- 239000002253 acid Substances 0.000 description 1
- 238000002583 angiography Methods 0.000 description 1
- 238000010171 animal model Methods 0.000 description 1
- 238000000137 annealing Methods 0.000 description 1
- 230000003466 anti-cipated effect Effects 0.000 description 1
- 229910052786 argon Inorganic materials 0.000 description 1
- 230000006399 behavior Effects 0.000 description 1
- 230000009286 beneficial effect Effects 0.000 description 1
- 238000005266 casting Methods 0.000 description 1
- 150000001875 compounds Chemical class 0.000 description 1
- 238000009749 continuous casting Methods 0.000 description 1
- 238000001816 cooling Methods 0.000 description 1
- 239000013078 crystal Substances 0.000 description 1
- 238000005261 decarburization Methods 0.000 description 1
- 230000007547 defect Effects 0.000 description 1
- 238000013461 design Methods 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 238000002594 fluoroscopy Methods 0.000 description 1
- 238000005242 forging Methods 0.000 description 1
- 238000000227 grinding Methods 0.000 description 1
- 206010020718 hyperplasia Diseases 0.000 description 1
- 239000012535 impurity Substances 0.000 description 1
- 230000006698 induction Effects 0.000 description 1
- 238000013152 interventional procedure Methods 0.000 description 1
- 238000004519 manufacturing process Methods 0.000 description 1
- 238000005065 mining Methods 0.000 description 1
- 150000004767 nitrides Chemical class 0.000 description 1
- 238000004663 powder metallurgy Methods 0.000 description 1
- 230000008569 process Effects 0.000 description 1
- 238000009877 rendering Methods 0.000 description 1
- 230000000717 retained effect Effects 0.000 description 1
- 230000008313 sensitization Effects 0.000 description 1
- 239000010703 silicon Substances 0.000 description 1
- 238000012360 testing method Methods 0.000 description 1
- 210000003708 urethra Anatomy 0.000 description 1
- 210000005166 vasculature Anatomy 0.000 description 1
- 230000000007 visual effect Effects 0.000 description 1
- 238000012800 visualization Methods 0.000 description 1
Classifications
-
- C—CHEMISTRY; METALLURGY
- C22—METALLURGY; FERROUS OR NON-FERROUS ALLOYS; TREATMENT OF ALLOYS OR NON-FERROUS METALS
- C22C—ALLOYS
- C22C38/00—Ferrous alloys, e.g. steel alloys
- C22C38/18—Ferrous alloys, e.g. steel alloys containing chromium
- C22C38/40—Ferrous alloys, e.g. steel alloys containing chromium with nickel
- C22C38/44—Ferrous alloys, e.g. steel alloys containing chromium with nickel with molybdenum or tungsten
-
- C—CHEMISTRY; METALLURGY
- C22—METALLURGY; FERROUS OR NON-FERROUS ALLOYS; TREATMENT OF ALLOYS OR NON-FERROUS METALS
- C22C—ALLOYS
- C22C38/00—Ferrous alloys, e.g. steel alloys
- C22C38/002—Ferrous alloys, e.g. steel alloys containing In, Mg, or other elements not provided for in one single group C22C38/001 - C22C38/60
-
- C—CHEMISTRY; METALLURGY
- C22—METALLURGY; FERROUS OR NON-FERROUS ALLOYS; TREATMENT OF ALLOYS OR NON-FERROUS METALS
- C22C—ALLOYS
- C22C38/00—Ferrous alloys, e.g. steel alloys
- C22C38/18—Ferrous alloys, e.g. steel alloys containing chromium
- C22C38/40—Ferrous alloys, e.g. steel alloys containing chromium with nickel
- C22C38/58—Ferrous alloys, e.g. steel alloys containing chromium with nickel with more than 1.5% by weight of manganese
Definitions
- This invention relates to an austenitic steel alloy, and in particular to such an alloy and an article made therefrom in which the elements are closely controlled to provide a unique combination of high tensile strength, ductility, good resistance to stress cracking and corrosion, and have improved radiopaque characteristics.
- Austenite generally does not exist at room temperature in plain-carbon and low-alloy steels, other than as small amounts of retained austenite that did not transform during rapid cooling.
- austenite is the dominant microstructure.
- sufficient quantities of alloying elements that stabilize austenite at room temperature are present (e.g., manganese and nickel).
- the crystal structure of austenite is face-centered cubic (fcc) as compared to ferrite, which has a body centered cubic (bcc) lattice.
- An fcc alloy has certain desirable characteristics; for example, it has low-temperature toughness, excellent weldability, and is nonmagnetic. Because of their high alloy content, austenitic steels are usually corrosion resistant. Disadvantages of the austenitic steels are their relative high costs, their susceptibility to stress-corrosion cracking (certain austenitic steels), the fact that they cannot be strengthened other than by cold working, and interstitial solid-solution strengthening.
- the austenitic stainless steels (e.g., type 301, 302, 303, 304, 305, 308, 309, 310, 314, 316, 317, 321, 330, 347, 348, and 384) generally contain from 6 to 22% nickel to stabilize the austenite microstructure at room temperature. They also contain other alloying elements, such as chromium (16 to 26%) for corrosion resistance, and smaller amounts of manganese and molybdenum.
- the widely used type 304 stainless steel contains 18 to 20% Cr and 8 to 10.5% Ni, and is also called 18-8 stainless steel.
- the yield strength of annealed type 304 stainless steel is typically 290 MPa (40 ksi), with a tensile strength of about 580 MPa (84 ksi).
- both yield and tensile strength can be substantially increased by cold working.
- the increase in strength is offset by a substantial decrease in ductility, for example, from about 55% elongation in the annealed condition to about 25% elongation after cold working.
- Some austenitic stainless steels (type 200, 201, 202, and 205) employ interstitial solid-solution strengthening with nitrogen addition.
- Austenite like ferrite, can be strengthened by interstitial elements such as carbon and nitrogen.
- carbon is usually excluded because of the deleterious effect associated with precipitation of chromium carbides on austenite grain boundaries (a process called sensitization).
- These chromium carbides deplete the grain-boundary regions of chromium, and the denuded boundaries are extremely susceptible to corrosion.
- Such steels can be desensitized by heating to high temperature to dissolve the carbides and place the chromium back into solution in the austenite. Nitrogen, on the other hand, is soluble in austenite and is added for strengthening.
- type 201 stainless steel has composition ranges of 5.5 to 7.5% Mn, 16 to 18% Cr, 3.5 to 5.5% Ni, and 0.25% N.
- the other type 2xx series of steels contain from 0.25 to 0.40% N.
- austenitic manganese steel Another important austenitic steel is austenitic manganese steel. Developed by Sir Robert Hadfield in the late 1890s, these steels remain austenitic after water quenching and have considerable strength and toughness. A typical Hadfield manganese steel contains 10 to 14% Mn, 0.95 to 1.4% C, and 0.3 to 1% Si. Solution annealing is necessary to suppress the formation of iron carbides. The carbon must be in solid solution to stabilize the austenite. When completely austenitic, these steels can be work hardened to provide higher hardness and wear resistance. A work-hardened Hadfield manganese steel has excellent resistance to abrasive wear under heavy loading. Because of this characteristic, these steels are ideal forjaw crushers and other crushing and grinding components in the mining industry. Also, Hadfield manganese steels have long been used for railway frogs (components used at the junction point of two railroad lines).
- AISI Types 304L, 316L, 321 and 347 stainless steels are austenitic, chromium-nickel and chromium-nickel-molybdenum stainless steels having the following compositions in weight percent: Type 304 L Type 316 L Type 321 Type 347 wt. % wt. % wt. % wt. % wt.
- chromium-nickel and chromium-nickel-molybdenum stainless steels are known to be useful for applications which require good non-magnetic behavior, in combination with good corrosion resistance.
- One disadvantage of the series 300 stainless steels is their poor radiopacity.
- a stent made from standard 300 series stainless steel can not be sufficiently radiopaque for clinical observation due to the thin cross-section of the struts. Therefore, this present invention alloy can be useful in clinical observations because it can be radiopaque in these cross-sections.
- chromium-nickel and chromium-nickel-molybdenum stainless steels particularly for these alloys having increased radiopaque characteristics.
- the invention generally relates to an austenitic 300 series stainless steel alloy that provides better radiopacity than is provided by the known austenitic stainless steels.
- One application for the present invention is to use the austenitic stainless steel alloy with increased radiopacity for fabricating intravascular stents.
- the interventionalist uses angiographic and fluoroscopic techniques that employ X-rays and materials that are radiopaque to the X-rays to visualize the location or placement of the particular device within the human vasculature.
- stents are fabricated from a variety of stainless steels, with the 316 series representing a large percentage of the stainless steel used to fabricate currently marketed stents.
- the typical composition of 316 series stainless steel is shown in Table I. TABLE I Component (%) C Mn Si P S Cr Mo Ni Fe Standard 316 0.020 1.760 0.470 0.014 0.002 17.490 2.790 14.680 62.774
- Modified stainless steel of the 300 series for increasing radiopaque characteristic could be produced by creating alloys containing varying amounts of elements that have dense mass and radiopaque characteristics.
- the chemical make-up of standard series 300 stainless steel, using series 316 as an example, along with the possible chemical ranges of various such alloys are shown on the following Table. TABLE II Component (%) C Mn Si P S Cr Mo Ni Fe X Standard 316 0.020 1.760 0.470 0.014 0.002 17.490 2.790 14.680 62.774 0.000
- Modified 300A ⁇ 0.030 ⁇ 2.000 ⁇ 0.750 ⁇ 0.023 ⁇ 0.010 12.000- 000- 10.000- 46.185- 2.000- 20.000 3.000 18.000 74.000 10.000
- Another object of the present invention is to provide a material which has superior properties, including radiopacity, for fabricating any stent design or format.
- the alloy according to the present invention comprises a stainless steel series 300 compound used to fabricate a stent which replaces a portion of the iron or molybdenum component of the 300 series with one or combination of several elements containing radiopaque properties.
- elements are gold (Au), osmium (Os), palladium (Pd), platinum (Pt), rhenium (Re), tantalum (Ta), tungsten (W) or iridium (Ir).
- This group consists of elements with dense masses. The dense mass provides these materials with improved absorption of X-rays thus providing improved radiopaque characteristics.
- X-rays employed in angiogram procedures or cineograms allow the visualization of certain devices, such as a stent, during all phases of a standard clinical procedure.
- the alloy for fabricating stents contains a range of 2.0 to 10.0 percent of one or more of these radiopaque elements, with a preferred range of 4.0 to 5.0 percent. Replacing too much of the radiopaque element with the iron or molybdenum component could possible decrease the beneficial qualities of 300 series stainless steel for manufacturing stents without contributing significantly improved radiopaque characteristics. It is anticipated that various combinations of the radiopaque elements can be used to replace the iron or molybdenum component without adversely affecting the ability to form austenite.
- the alloy for fabricating a series 300 stainless steel with improved radiopaque properties can contain up to 0.03% of carbon.
- the carbon element contributes to good hardness capability and high tensile strength by combining with other elements such as chromium and molybdenum to form carbides during heat treatment. However, too much carbon adversely affects the fracture toughness of this alloy.
- Chromium contributes to the good hardenability corrosion resistance and hardness capability of this alloy and benefits the desired low ductile-brittle transition temperature of the alloy. Therefore, at least about 12%, and preferably at least about 17.5% chromium is present. Above about 20% chromium the alloy is susceptible to rapid overaging such that the unique combination of high tensile strength and high fracture toughness is not attainable.
- Nickel contributes to the hardenability of this alloy such that the alloy can be hardened with or without rapid quenching techniques. Nickel benefits the fracture toughness and stress corrosion cracking resistance provided by this alloy and contributes to the desired low ductile-to-brittle transition temperature. Accordingly, at least about 10.0%, and preferably at least about 14.7% nickel is present. Above about 18% nickel, the fracture toughness and impact toughness of the alloy can be adversely affected because the solubility of carbon in the alloy is reduced which may result in carbide precipitation in the grain boundaries when the alloy is cooled at a slow rate, such as when air cooled following forging.
- Molybdenum is present in this alloy because it benefits the desired low ductile brittle transition temperature of the alloy. Above about 3% molybdenum the fracture toughness of the alloy is adversely affected. Preferably, molybdenum is limited to not more than about 1.2%. However, the entire portion of the molybdenum can be replaced with certain radiopaque elements such as Ta without adversely affecting the desired characteristics of the alloy.
- the alloy for fabricating a series 300 stainless steel stent with radiopaque properties can also contain up to 2.0% manganese.
- Manganese is partly depended upon to maintain the austenitic, nonmagnetic character of the alloy. Manganese also plays a role, in part, providing resistance to corrosive attack.
- the balance of the alloy according to the present invention is essentially iron except for the usual impurities found in commercial grades of alloys intended for similar service or use.
- the levels of such elements must be controlled so as not to adversely affect the desired properties of this alloy.
- phosphorus is limited to not more than about 0.008% and sulfur is limited to not more 0.004%.
- the alloy for fabricating a series 300 stainless steel alloy with radiopaque properties can contain up to 0.75% silicon.
- the alloy for fabricating a series 300 stainless steel stent with radiopaque properties can contain up to 0.023% and 0.002% phosphorus and sulfur, respectively, without affecting the desirable properties.
- the alloy of the present invention can be formed into a variety of shapes for a wide variety of uses and lends itself to the formation of billets, bars, rod, wire, strip, plate, or sheet using conventional practices.
- the alloy according to the present invention can be useful in a variety of applications requiring high strength and radiopaque characteristics, for example, to fabricate stents of other medical applications.
- the alloy according to the present invention provides a unique combination of tensile strength and radiopaque characteristics not provided by known series 300 stainless steel alloys. This alloy is well suited to applications where high strength, biocompatibility and radiopacity are required.
- the alloy of the present invention is readily melted using conventional and/or vacuum melting techniques. For best results, as when additional refining is desired, a multiple melting practice is preferred. The preferred practice is to melt a heat in a vacuum induction furnace (VIM) and cast the heat in the form of an electrode. The electrode is then remelted in a vacuum arc furnace (VAR) and recast into one or more ingots.
- VIP vacuum induction furnace
- VAR vacuum arc furnace
- the alloy can be prepared from heats which can be melted under argon cover and cast as ingots.
- the ingots can be maintained at a temperature range of 2100-2300 degree F. (1149-1260 degree C.) for 2 hours and then pressed into billets.
- the billets may be ground to remove surface defects and the ends cut off.
- the billets can then be hot rolled to form intermediate bars with an intermediate diameter.
- the intermediate bars are hot rolled to a diameter of 0.7187 in. (1.82 cm) from a temperature range of 2100-2300.degree. F. (1 149-1260.degree. C.).
- the round bars are straightened and then turned to a final diameter or alternately, sheets are rolled to the desired diameter with optional intermediate anneals are required. All of the bars or sheets can be pointed, solution annealed, water quenched, and acid cleaned to remove surface scale.
- stents can be fabricated from the present invention alloy and testing in animal studies utilizing standard angiography equipment.
- the stent fabricated from the alloy can be deployed in an animal model with other FDA approved stents with know radiopacity characteristics.
Abstract
Description
- This application is a continuation-in-part of application Ser. No. 09/612,157 filed on Jul. 7, 2000. It was disclosed in the application that this inventions is an austenitic steel alloy having radiopaque characteristics.
- This invention relates to an austenitic steel alloy, and in particular to such an alloy and an article made therefrom in which the elements are closely controlled to provide a unique combination of high tensile strength, ductility, good resistance to stress cracking and corrosion, and have improved radiopaque characteristics.
- Austenite generally does not exist at room temperature in plain-carbon and low-alloy steels, other than as small amounts of retained austenite that did not transform during rapid cooling. However, in certain high-alloy steels, such as the austenitic stainless steels and Hadfield austenitic manganese steel, austenite is the dominant microstructure. In these steels, sufficient quantities of alloying elements that stabilize austenite at room temperature are present (e.g., manganese and nickel). The crystal structure of austenite is face-centered cubic (fcc) as compared to ferrite, which has a body centered cubic (bcc) lattice. An fcc alloy has certain desirable characteristics; for example, it has low-temperature toughness, excellent weldability, and is nonmagnetic. Because of their high alloy content, austenitic steels are usually corrosion resistant. Disadvantages of the austenitic steels are their relative high costs, their susceptibility to stress-corrosion cracking (certain austenitic steels), the fact that they cannot be strengthened other than by cold working, and interstitial solid-solution strengthening.
- The austenitic stainless steels (e.g., type 301, 302, 303, 304, 305, 308, 309, 310, 314, 316, 317, 321, 330, 347, 348, and 384) generally contain from 6 to 22% nickel to stabilize the austenite microstructure at room temperature. They also contain other alloying elements, such as chromium (16 to 26%) for corrosion resistance, and smaller amounts of manganese and molybdenum. The widely used type 304 stainless steel contains 18 to 20% Cr and 8 to 10.5% Ni, and is also called 18-8 stainless steel. The yield strength of annealed type 304 stainless steel is typically 290 MPa (40 ksi), with a tensile strength of about 580 MPa (84 ksi). However, both yield and tensile strength can be substantially increased by cold working. However, the increase in strength is offset by a substantial decrease in ductility, for example, from about 55% elongation in the annealed condition to about 25% elongation after cold working.
- Some austenitic stainless steels (type 200, 201, 202, and 205) employ interstitial solid-solution strengthening with nitrogen addition. Austenite, like ferrite, can be strengthened by interstitial elements such as carbon and nitrogen. However, carbon is usually excluded because of the deleterious effect associated with precipitation of chromium carbides on austenite grain boundaries (a process called sensitization). These chromium carbides deplete the grain-boundary regions of chromium, and the denuded boundaries are extremely susceptible to corrosion. Such steels can be desensitized by heating to high temperature to dissolve the carbides and place the chromium back into solution in the austenite. Nitrogen, on the other hand, is soluble in austenite and is added for strengthening. To prevent nitrogen from forming deleterious nitrides, manganese is added to lower the activity of nitrogen in the austenite, as well as to stabilize the austenite. For example, type 201 stainless steel has composition ranges of 5.5 to 7.5% Mn, 16 to 18% Cr, 3.5 to 5.5% Ni, and 0.25% N. The other type 2xx series of steels contain from 0.25 to 0.40% N.
- Another important austenitic steel is austenitic manganese steel. Developed by Sir Robert Hadfield in the late 1890s, these steels remain austenitic after water quenching and have considerable strength and toughness. A typical Hadfield manganese steel contains 10 to 14% Mn, 0.95 to 1.4% C, and 0.3 to 1% Si. Solution annealing is necessary to suppress the formation of iron carbides. The carbon must be in solid solution to stabilize the austenite. When completely austenitic, these steels can be work hardened to provide higher hardness and wear resistance. A work-hardened Hadfield manganese steel has excellent resistance to abrasive wear under heavy loading. Because of this characteristic, these steels are ideal forjaw crushers and other crushing and grinding components in the mining industry. Also, Hadfield manganese steels have long been used for railway frogs (components used at the junction point of two railroad lines).
- AISI Types 304L, 316L, 321 and 347 stainless steels are austenitic, chromium-nickel and chromium-nickel-molybdenum stainless steels having the following compositions in weight percent:
Type 304 L Type 316 L Type 321 Type 347 wt. % wt. % wt. % wt. % C 0.03 max 0.03 max 0.08 max 0.08 max Mn 2.00 max 2.00 max 2.00 max 2.00 max Si 1.00 max 1.00 max 1.00 max 1.00 max P 0.045 max 0.045 max 0.045 max 0.045 max S 0.03 max 0.03 max 0.03 max 0.03 max Cr 18.0-20.0 16.0-18.0 17.0-19.0 17.0-19.0 Ni 8.0-12.0 10.-14.0 9.0-12.0 9.0-13.0 N 0.10 max 0.10 max 0.10 max — Mo — 2.0-3.0 — — Fe Bal. Bal. Bal. Bal. - The above-listed chromium-nickel and chromium-nickel-molybdenum stainless steels are known to be useful for applications which require good non-magnetic behavior, in combination with good corrosion resistance. One disadvantage of the series 300 stainless steels is their poor radiopacity. For example, a stent made from standard 300 series stainless steel can not be sufficiently radiopaque for clinical observation due to the thin cross-section of the struts. Therefore, this present invention alloy can be useful in clinical observations because it can be radiopaque in these cross-sections. There continues to be a demand for improved chromium-nickel and chromium-nickel-molybdenum stainless steels, particularly for these alloys having increased radiopaque characteristics.
- Given the foregoing, it would be highly desirable to have an austenitic stainless steel that provides better radiopacity than is provided by the known austenitic stainless steels.
- The invention generally relates to an austenitic 300 series stainless steel alloy that provides better radiopacity than is provided by the known austenitic stainless steels. One application for the present invention is to use the austenitic stainless steel alloy with increased radiopacity for fabricating intravascular stents. In this clinical setting, the interventionalist uses angiographic and fluoroscopic techniques that employ X-rays and materials that are radiopaque to the X-rays to visualize the location or placement of the particular device within the human vasculature. Typically stents are fabricated from a variety of stainless steels, with the 316 series representing a large percentage of the stainless steel used to fabricate currently marketed stents. The typical composition of 316 series stainless steel is shown in Table I.
TABLE I Component (%) C Mn Si P S Cr Mo Ni Fe Standard 316 0.020 1.760 0.470 0.014 0.002 17.490 2.790 14.680 62.774 - While the 300 series of stainless steel has several characteristics, such as strength, flexibility, fatigue resistance, biocompatibility, etc. rendering it a good material to make an intravascular stent, one significant disadvantage of 316 series stainless steel, as well as other 300 series of stainless steel, is that they have relatively low radiopaque qualities and therefore not readably visual under fluoroscopic observation. A need has arisen to modify the stainless steel composition so it has radiopaque properties while at the same time, maintaining those characteristics which render it as a material of choice for fabricating stents.
- Modified stainless steel of the 300 series for increasing radiopaque characteristic could be produced by creating alloys containing varying amounts of elements that have dense mass and radiopaque characteristics. The chemical make-up of standard series 300 stainless steel, using series 316 as an example, along with the possible chemical ranges of various such alloys are shown on the following Table.
TABLE II Component (%) C Mn Si P S Cr Mo Ni Fe X Standard 316 0.020 1.760 0.470 0.014 0.002 17.490 2.790 14.680 62.774 0.000 Modified 300A ≦0.030 ≦2.000 ≦0.750 ≦0.023 ≦0.010 12.000- 000- 10.000- 46.185- 2.000- 20.000 3.000 18.000 74.000 10.000 - Other features and advantages of the present invention will become more apparent from the following detailed description of the invention.
- It is an object of the present invention to provide an austenitic 300 series stainless steel alloy that provides better radiopacity than is provided by the known austenitic stainless steels.
- It is another object of the present invention to provide a stent or prosthesis which can be readily delivered to, expanded and embedded into an obstruction or vessel wall with relatively high radiopaque characteristics for fluoroscopy during all phases of the interventional procedure.
- Another object of the present invention is to provide a material which has superior properties, including radiopacity, for fabricating any stent design or format.
- The alloy according to the present invention comprises a stainless steel series 300 compound used to fabricate a stent which replaces a portion of the iron or molybdenum component of the 300 series with one or combination of several elements containing radiopaque properties. Examples of such elements are gold (Au), osmium (Os), palladium (Pd), platinum (Pt), rhenium (Re), tantalum (Ta), tungsten (W) or iridium (Ir). This group consists of elements with dense masses. The dense mass provides these materials with improved absorption of X-rays thus providing improved radiopaque characteristics. By including one or more of these elements in a series 300 stainless steel, thereby creating the present invention alloy, X-rays employed in angiogram procedures or cineograms allow the visualization of certain devices, such as a stent, during all phases of a standard clinical procedure. The alloy for fabricating stents contains a range of 2.0 to 10.0 percent of one or more of these radiopaque elements, with a preferred range of 4.0 to 5.0 percent. Replacing too much of the radiopaque element with the iron or molybdenum component could possible decrease the beneficial qualities of 300 series stainless steel for manufacturing stents without contributing significantly improved radiopaque characteristics. It is anticipated that various combinations of the radiopaque elements can be used to replace the iron or molybdenum component without adversely affecting the ability to form austenite.
- The foregoing, as well as additional objects and advantages of the present invention, achieved in a series 300 stainless steel alloy, is compared with standard 316 stainless steel and summarized in Tables III through XI below, containing in weight percent, about:
TABLE III Component (%) C Mn Si P S Cr Mo Ni Fe X Standard 316 0.020 1.760 0.470 0.014 0.002 17.490 2.790 14.680 62.774 0.000 Modified 300A ≦0.030 ≦2.000 ≦0.750 ≦0.023 ≦0.010 12.000- 0.00- 10.000- 46.185- 2.000- 20.000 3.000 18.000 74.000 10.000 -
TABLE IV Component (%) C Mn Si P S Cr Mo Ni Fe Au Standard 316 0.020 1.760 0.470 0.014 0.002 17.490 2.790 14.680 62.774 0.000 Modified 316B ≦0.030 ≦2.000 ≦0.750 ≦0.023 ≦0.010 12.000- 0.00- 10.000- 46.185- 2.000- 20.000 3.000 18.000 74.000 10.000 -
TABLE V Component (%) C Mn Si P S Cr Mo Ni Fe Os Standard 316 0.020 1.760 0.470 0.014 0.002 17.490 2.790 14.680 62.774 0.000 Modified 316B ≦0.030 ≦2.000 ≦0.750 ≦0.023 ≦0.010 12.000- 0.00- 10.000- 46.185- 2.000- 20.000 3.000 18.000 74.000 10.000 -
TABLE VI Component (%) C Mn Si P S Cr Mo Ni Fe Pd Standard 316 0.020 1.760 0.470 0.014 0.002 17.490 2.790 14.680 62.774 0.000 Modified 316B ≦0.030 ≦2.000 ≦0.750 ≦0.023 ≦0.010 12.000- 0.00- 10.000- 46.185- 2.000- 20.000 3.000 18.000 74.000 10.000 -
TABLE VII Component (%) C Mn Si P S Cr Mo Ni Fe Pt Standard 316 0.020 1.760 0.470 0.014 0.002 17.490 2.790 14.680 62.774 0.000 Modified 316B ≦0.030 ≦2.000 ≦0.750 ≦0.023 ≦0.010 12.000- 0.00- 10.000- 46.185- 2.000- 20.000 3.000 18.000 74.000 10.000 -
TABLE VIII Component (%) C Mn Si P S Cr Mo Ni Fe Re Standard 316 0.020 1.760 0.470 0.014 0.002 17.490 2.790 14.680 62.774 0.000 Modified 316B ≦0.030 ≦2.000 ≦0.750 ≦0.023 ≦0.010 12.000- 0.00- 10.000- 46.185- 2.000- 20.000 3.000 18.000 74.000 10.000 -
TABLE IX Component (%) C Mn Si P S Cr Mo Ni Fe Ta Standard 316 0.020 1.760 0.470 0.014 0.002 17.490 2.790 14.680 62.774 0.000 Modified 316B ≦0.030 ≦2.000 ≦0.750 ≦0.023 ≦0.010 12.000- 0.00- 10.000- 46.185- 2.000- 20.000 3.000 18.000 74.000 10.000 -
TABLE X Component (%) C Mn Si P S Cr Mo Ni Fe W Standard 316 0.020 1.760 0.470 0.014 0.002 17.490 2.790 14.680 62.774 0.000 Modified 316B ≦0.030 ≦2.000 ≦0.750 ≦0.023 ≦0.010 12.000- 0.00- 10.000- 46.185- 2.000- 20.000 3.000 18.000 74.000 10.000 -
TABLE XI Component (%) C Mn Si P S Cr Mo Ni Fe Ir Standard 316 0.020 1.760 0.470 0.014 0.002 17.490 2.790 14.680 62.774 0.000 Modified 316B ≦0.030 ≦2.000 ≦0.750 ≦0.023 ≦0.010 12.000- 0.00- 10.000- 46.185- 2.000- 20.000 3.000 18.000 74.000 10.000 - The alloy for fabricating a series 300 stainless steel with improved radiopaque properties can contain up to 0.03% of carbon. The carbon element contributes to good hardness capability and high tensile strength by combining with other elements such as chromium and molybdenum to form carbides during heat treatment. However, too much carbon adversely affects the fracture toughness of this alloy.
- Chromium contributes to the good hardenability corrosion resistance and hardness capability of this alloy and benefits the desired low ductile-brittle transition temperature of the alloy. Therefore, at least about 12%, and preferably at least about 17.5% chromium is present. Above about 20% chromium the alloy is susceptible to rapid overaging such that the unique combination of high tensile strength and high fracture toughness is not attainable.
- Nickel contributes to the hardenability of this alloy such that the alloy can be hardened with or without rapid quenching techniques. Nickel benefits the fracture toughness and stress corrosion cracking resistance provided by this alloy and contributes to the desired low ductile-to-brittle transition temperature. Accordingly, at least about 10.0%, and preferably at least about 14.7% nickel is present. Above about 18% nickel, the fracture toughness and impact toughness of the alloy can be adversely affected because the solubility of carbon in the alloy is reduced which may result in carbide precipitation in the grain boundaries when the alloy is cooled at a slow rate, such as when air cooled following forging.
- Molybdenum is present in this alloy because it benefits the desired low ductile brittle transition temperature of the alloy. Above about 3% molybdenum the fracture toughness of the alloy is adversely affected. Preferably, molybdenum is limited to not more than about 1.2%. However, the entire portion of the molybdenum can be replaced with certain radiopaque elements such as Ta without adversely affecting the desired characteristics of the alloy.
- The alloy for fabricating a series 300 stainless steel stent with radiopaque properties can also contain up to 2.0% manganese. Manganese is partly depended upon to maintain the austenitic, nonmagnetic character of the alloy. Manganese also plays a role, in part, providing resistance to corrosive attack.
- The balance of the alloy according to the present invention is essentially iron except for the usual impurities found in commercial grades of alloys intended for similar service or use. The levels of such elements must be controlled so as not to adversely affect the desired properties of this alloy. For example, phosphorus is limited to not more than about 0.008% and sulfur is limited to not more 0.004%. In addition, the alloy for fabricating a series 300 stainless steel alloy with radiopaque properties can contain up to 0.75% silicon. Furthermore, the alloy for fabricating a series 300 stainless steel stent with radiopaque properties can contain up to 0.023% and 0.002% phosphorus and sulfur, respectively, without affecting the desirable properties.
- No special techniques are required in melting, casting, or working the alloy of the present invention. Arc melting followed by argon-oxygen decarburization is the preferred method of melting and refining, but other practices can be used. In addition, this alloy can be made using powder metallurgy techniques, if desired. This alloy is also suitable for continuous casting techniques.
- The alloy of the present invention can be formed into a variety of shapes for a wide variety of uses and lends itself to the formation of billets, bars, rod, wire, strip, plate, or sheet using conventional practices.
- The alloy according to the present invention can be useful in a variety of applications requiring high strength and radiopaque characteristics, for example, to fabricate stents of other medical applications.
- It is apparent from the foregoing description and the accompanying examples, that the alloy according to the present invention provides a unique combination of tensile strength and radiopaque characteristics not provided by known series 300 stainless steel alloys. This alloy is well suited to applications where high strength, biocompatibility and radiopacity are required.
- The terms and expressions which have been employed herein are used as terms of description and not of limitation. There is no intention in the use of such terms and expressions to exclude any equivalents of the features described or any portions thereof. It is recognized, however, that various modifications are possible within the scope of the invention claimed.
- While the invention has been illustrated and described herein in terms of its use as an intravascular stent, it will be apparent to those skilled in the art that the stent can be used in other instances such as to expand prostate urethras in cases of prostate hyperplasia. Other modifications and improvements may be made without departing from the scope of the invention.
- Other modifications and improvements can be made to the invention without departing from the scope thereof.
- The alloy of the present invention is readily melted using conventional and/or vacuum melting techniques. For best results, as when additional refining is desired, a multiple melting practice is preferred. The preferred practice is to melt a heat in a vacuum induction furnace (VIM) and cast the heat in the form of an electrode. The electrode is then remelted in a vacuum arc furnace (VAR) and recast into one or more ingots.
- The alloy can be prepared from heats which can be melted under argon cover and cast as ingots. The ingots can be maintained at a temperature range of 2100-2300 degree F. (1149-1260 degree C.) for 2 hours and then pressed into billets. The billets may be ground to remove surface defects and the ends cut off. The billets can then be hot rolled to form intermediate bars with an intermediate diameter. The intermediate bars are hot rolled to a diameter of 0.7187 in. (1.82 cm) from a temperature range of 2100-2300.degree. F. (1 149-1260.degree. C.). The round bars are straightened and then turned to a final diameter or alternately, sheets are rolled to the desired diameter with optional intermediate anneals are required. All of the bars or sheets can be pointed, solution annealed, water quenched, and acid cleaned to remove surface scale.
- To evaluate improved radiopacity of the present invention, stents can be fabricated from the present invention alloy and testing in animal studies utilizing standard angiography equipment. The stent fabricated from the alloy can be deployed in an animal model with other FDA approved stents with know radiopacity characteristics.
- The terms and expressions that have been employed herein are used as terms of description and not of limitation. There is no intention in the use of such terms and expressions to exclude any equivalents of the features described or any portions thereof. It is recognized, however, that various modifications are possible within the scope of the invention claimed.
Claims (9)
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US10/103,411 US20020144757A1 (en) | 2000-07-07 | 2002-03-20 | Stainless steel alloy with improved radiopaque characteristics |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US61215700A | 2000-07-07 | 2000-07-07 | |
US10/103,411 US20020144757A1 (en) | 2000-07-07 | 2002-03-20 | Stainless steel alloy with improved radiopaque characteristics |
Related Parent Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US61215700A Continuation-In-Part | 2000-07-07 | 2000-07-07 |
Publications (1)
Publication Number | Publication Date |
---|---|
US20020144757A1 true US20020144757A1 (en) | 2002-10-10 |
Family
ID=24451960
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/103,411 Abandoned US20020144757A1 (en) | 2000-07-07 | 2002-03-20 | Stainless steel alloy with improved radiopaque characteristics |
Country Status (1)
Country | Link |
---|---|
US (1) | US20020144757A1 (en) |
Cited By (105)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20040204749A1 (en) * | 2003-04-11 | 2004-10-14 | Richard Gunderson | Stent delivery system with securement and deployment accuracy |
US20040267348A1 (en) * | 2003-04-11 | 2004-12-30 | Gunderson Richard C. | Medical device delivery systems |
US20060079953A1 (en) * | 2004-10-08 | 2006-04-13 | Gregorich Daniel J | Medical devices and methods of making the same |
US20060100696A1 (en) * | 2004-11-10 | 2006-05-11 | Atanasoska Ljiljana L | Medical devices and methods of making the same |
US20060097242A1 (en) * | 2004-11-10 | 2006-05-11 | Mitsubishi Denki Kabushiki Kaisha | Semiconductor light-emitting device |
US20060153729A1 (en) * | 2005-01-13 | 2006-07-13 | Stinson Jonathan S | Medical devices and methods of making the same |
US20060222844A1 (en) * | 2005-04-04 | 2006-10-05 | Stinson Jonathan S | Medical devices including composites |
US20060224231A1 (en) * | 2005-03-31 | 2006-10-05 | Gregorich Daniel J | Endoprostheses |
US20060229711A1 (en) * | 2005-04-05 | 2006-10-12 | Elixir Medical Corporation | Degradable implantable medical devices |
US20060259126A1 (en) * | 2005-05-05 | 2006-11-16 | Jason Lenz | Medical devices and methods of making the same |
US20060276910A1 (en) * | 2005-06-01 | 2006-12-07 | Jan Weber | Endoprostheses |
US20060276875A1 (en) * | 2005-05-27 | 2006-12-07 | Stinson Jonathan S | Medical devices |
US20070114701A1 (en) * | 2005-11-18 | 2007-05-24 | Stenzel Eric B | Methods and apparatuses for manufacturing medical devices |
US20080069858A1 (en) * | 2006-09-20 | 2008-03-20 | Boston Scientific Scimed, Inc. | Medical devices having biodegradable polymeric regions with overlying hard, thin layers |
US20080071344A1 (en) * | 2006-09-18 | 2008-03-20 | Boston Scientific Scimed, Inc. | Medical device with porous surface |
US20080071355A1 (en) * | 2006-09-14 | 2008-03-20 | Boston Scientific Scimed, Inc. | Medical Devices with Drug-Eluting Coating |
WO2008063775A2 (en) * | 2006-10-13 | 2008-05-29 | Boston Scientific Limited | Medical devices including hardened alloys |
US20080160259A1 (en) * | 2006-12-28 | 2008-07-03 | Boston Scientific Scimed, Inc. | Medical devices and methods of making the same |
US20080161900A1 (en) * | 2006-06-20 | 2008-07-03 | Boston Scientific Scimed, Inc. | Medical devices including composites |
US20080294238A1 (en) * | 2007-05-25 | 2008-11-27 | Boston Scientific Scimed, Inc. | Connector Node for Durable Stent |
US20090118814A1 (en) * | 2007-11-02 | 2009-05-07 | Boston Scientific Scimed, Inc. | Endoprosthesis coating |
US20090118812A1 (en) * | 2007-11-02 | 2009-05-07 | Boston Scientific Scimed, Inc. | Endoprosthesis coating |
US20090149942A1 (en) * | 2007-07-19 | 2009-06-11 | Boston Scientific Scimed, Inc. | Endoprosthesis having a non-fouling surface |
US20090299468A1 (en) * | 2008-05-29 | 2009-12-03 | Boston Scientific Scimed, Inc. | Endoprosthesis coating |
US20090319032A1 (en) * | 2008-06-18 | 2009-12-24 | Boston Scientific Scimed, Inc | Endoprosthesis coating |
US20100010620A1 (en) * | 2008-07-09 | 2010-01-14 | Boston Scientific Scimed, Inc. | Stent |
US20100057188A1 (en) * | 2008-08-28 | 2010-03-04 | Boston Scientific Scimed, Inc. | Endoprostheses with porous regions and non-polymeric coating |
US20100063584A1 (en) * | 2008-09-05 | 2010-03-11 | Boston Scientific Scimed, Inc. | Endoprostheses |
US20100217370A1 (en) * | 2009-02-20 | 2010-08-26 | Boston Scientific Scimed, Inc. | Bioerodible Endoprosthesis |
WO2010101988A2 (en) | 2009-03-04 | 2010-09-10 | Boston Scientific Scimed, Inc. | Endoprostheses |
US20100305682A1 (en) * | 2006-09-21 | 2010-12-02 | Cleveny Technologies | Specially configured and surface modified medical device with certain design features that utilize the intrinsic properties of tungsten, zirconium, tantalum and/or niobium |
US20110022162A1 (en) * | 2009-07-23 | 2011-01-27 | Boston Scientific Scimed, Inc. | Endoprostheses |
US7931683B2 (en) | 2007-07-27 | 2011-04-26 | Boston Scientific Scimed, Inc. | Articles having ceramic coated surfaces |
US7938855B2 (en) | 2007-11-02 | 2011-05-10 | Boston Scientific Scimed, Inc. | Deformable underlayer for stent |
US7942926B2 (en) | 2007-07-11 | 2011-05-17 | Boston Scientific Scimed, Inc. | Endoprosthesis coating |
US7955382B2 (en) | 2006-09-15 | 2011-06-07 | Boston Scientific Scimed, Inc. | Endoprosthesis with adjustable surface features |
US7976915B2 (en) | 2007-05-23 | 2011-07-12 | Boston Scientific Scimed, Inc. | Endoprosthesis with select ceramic morphology |
US7981150B2 (en) | 2006-11-09 | 2011-07-19 | Boston Scientific Scimed, Inc. | Endoprosthesis with coatings |
US7985252B2 (en) | 2008-07-30 | 2011-07-26 | Boston Scientific Scimed, Inc. | Bioerodible endoprosthesis |
US7998192B2 (en) | 2008-05-09 | 2011-08-16 | Boston Scientific Scimed, Inc. | Endoprostheses |
US8002821B2 (en) | 2006-09-18 | 2011-08-23 | Boston Scientific Scimed, Inc. | Bioerodible metallic ENDOPROSTHESES |
US8002823B2 (en) | 2007-07-11 | 2011-08-23 | Boston Scientific Scimed, Inc. | Endoprosthesis coating |
WO2011119430A1 (en) | 2010-03-26 | 2011-09-29 | Boston Scientific Scimed, Inc. | Endoprosthesis |
US20110238153A1 (en) * | 2010-03-26 | 2011-09-29 | Boston Scientific Scimed, Inc. | Endoprostheses |
US8029554B2 (en) | 2007-11-02 | 2011-10-04 | Boston Scientific Scimed, Inc. | Stent with embedded material |
WO2011126708A1 (en) | 2010-04-06 | 2011-10-13 | Boston Scientific Scimed, Inc. | Endoprosthesis |
US8048150B2 (en) | 2006-04-12 | 2011-11-01 | Boston Scientific Scimed, Inc. | Endoprosthesis having a fiber meshwork disposed thereon |
US8052745B2 (en) | 2007-09-13 | 2011-11-08 | Boston Scientific Scimed, Inc. | Endoprosthesis |
US8052744B2 (en) | 2006-09-15 | 2011-11-08 | Boston Scientific Scimed, Inc. | Medical devices and methods of making the same |
US8052743B2 (en) | 2006-08-02 | 2011-11-08 | Boston Scientific Scimed, Inc. | Endoprosthesis with three-dimensional disintegration control |
US8057534B2 (en) | 2006-09-15 | 2011-11-15 | Boston Scientific Scimed, Inc. | Bioerodible endoprostheses and methods of making the same |
US8066763B2 (en) | 1998-04-11 | 2011-11-29 | Boston Scientific Scimed, Inc. | Drug-releasing stent with ceramic-containing layer |
US8067054B2 (en) | 2007-04-05 | 2011-11-29 | Boston Scientific Scimed, Inc. | Stents with ceramic drug reservoir layer and methods of making and using the same |
US8070797B2 (en) | 2007-03-01 | 2011-12-06 | Boston Scientific Scimed, Inc. | Medical device with a porous surface for delivery of a therapeutic agent |
US8080055B2 (en) | 2006-12-28 | 2011-12-20 | Boston Scientific Scimed, Inc. | Bioerodible endoprostheses and methods of making the same |
US8089029B2 (en) | 2006-02-01 | 2012-01-03 | Boston Scientific Scimed, Inc. | Bioabsorbable metal medical device and method of manufacture |
US8128689B2 (en) | 2006-09-15 | 2012-03-06 | Boston Scientific Scimed, Inc. | Bioerodible endoprosthesis with biostable inorganic layers |
US8187620B2 (en) | 2006-03-27 | 2012-05-29 | Boston Scientific Scimed, Inc. | Medical devices comprising a porous metal oxide or metal material and a polymer coating for delivering therapeutic agents |
US8221822B2 (en) | 2007-07-31 | 2012-07-17 | Boston Scientific Scimed, Inc. | Medical device coating by laser cladding |
WO2012096995A2 (en) | 2011-01-11 | 2012-07-19 | Boston Scientific Scimed, Inc. | Coated medical devices |
US8231980B2 (en) | 2008-12-03 | 2012-07-31 | Boston Scientific Scimed, Inc. | Medical implants including iridium oxide |
US8236046B2 (en) | 2008-06-10 | 2012-08-07 | Boston Scientific Scimed, Inc. | Bioerodible endoprosthesis |
US8267992B2 (en) | 2009-03-02 | 2012-09-18 | Boston Scientific Scimed, Inc. | Self-buffering medical implants |
US8287937B2 (en) | 2009-04-24 | 2012-10-16 | Boston Scientific Scimed, Inc. | Endoprosthese |
WO2012142319A1 (en) | 2011-04-13 | 2012-10-18 | Micell Technologies, Inc. | Stents having controlled elution |
US8303643B2 (en) | 2001-06-27 | 2012-11-06 | Remon Medical Technologies Ltd. | Method and device for electrochemical formation of therapeutic species in vivo |
US8382824B2 (en) | 2008-10-03 | 2013-02-26 | Boston Scientific Scimed, Inc. | Medical implant having NANO-crystal grains with barrier layers of metal nitrides or fluorides |
US8431149B2 (en) | 2007-03-01 | 2013-04-30 | Boston Scientific Scimed, Inc. | Coated medical devices for abluminal drug delivery |
WO2013090145A1 (en) | 2011-12-13 | 2013-06-20 | Boston Scientific Scimed, Inc. | Decalcifying heart valve |
US8574615B2 (en) | 2006-03-24 | 2013-11-05 | Boston Scientific Scimed, Inc. | Medical devices having nanoporous coatings for controlled therapeutic agent delivery |
US8668732B2 (en) | 2010-03-23 | 2014-03-11 | Boston Scientific Scimed, Inc. | Surface treated bioerodible metal endoprostheses |
US8758429B2 (en) | 2005-07-15 | 2014-06-24 | Micell Technologies, Inc. | Polymer coatings containing drug powder of controlled morphology |
US8771343B2 (en) | 2006-06-29 | 2014-07-08 | Boston Scientific Scimed, Inc. | Medical devices with selective titanium oxide coatings |
US8795762B2 (en) | 2010-03-26 | 2014-08-05 | Battelle Memorial Institute | System and method for enhanced electrostatic deposition and surface coatings |
US8808726B2 (en) | 2006-09-15 | 2014-08-19 | Boston Scientific Scimed. Inc. | Bioerodible endoprostheses and methods of making the same |
US8815275B2 (en) | 2006-06-28 | 2014-08-26 | Boston Scientific Scimed, Inc. | Coatings for medical devices comprising a therapeutic agent and a metallic material |
US8815273B2 (en) | 2007-07-27 | 2014-08-26 | Boston Scientific Scimed, Inc. | Drug eluting medical devices having porous layers |
US8834913B2 (en) | 2008-12-26 | 2014-09-16 | Battelle Memorial Institute | Medical implants and methods of making medical implants |
US8840660B2 (en) | 2006-01-05 | 2014-09-23 | Boston Scientific Scimed, Inc. | Bioerodible endoprostheses and methods of making the same |
US8852625B2 (en) | 2006-04-26 | 2014-10-07 | Micell Technologies, Inc. | Coatings containing multiple drugs |
US8900292B2 (en) | 2007-08-03 | 2014-12-02 | Boston Scientific Scimed, Inc. | Coating for medical device having increased surface area |
US8900651B2 (en) | 2007-05-25 | 2014-12-02 | Micell Technologies, Inc. | Polymer films for medical device coating |
US8920491B2 (en) | 2008-04-22 | 2014-12-30 | Boston Scientific Scimed, Inc. | Medical devices having a coating of inorganic material |
US8920490B2 (en) | 2010-05-13 | 2014-12-30 | Boston Scientific Scimed, Inc. | Endoprostheses |
US8932346B2 (en) | 2008-04-24 | 2015-01-13 | Boston Scientific Scimed, Inc. | Medical devices having inorganic particle layers |
CN105821343A (en) * | 2016-05-24 | 2016-08-03 | 江苏金基特钢有限公司 | Production method of special steel |
US9433516B2 (en) | 2007-04-17 | 2016-09-06 | Micell Technologies, Inc. | Stents having controlled elution |
US9486431B2 (en) | 2008-07-17 | 2016-11-08 | Micell Technologies, Inc. | Drug delivery medical device |
CN106148852A (en) * | 2015-04-02 | 2016-11-23 | 上海微创医疗器械(集团)有限公司 | A kind of alloy material and implantable medical devices |
US9510856B2 (en) | 2008-07-17 | 2016-12-06 | Micell Technologies, Inc. | Drug delivery medical device |
US9539593B2 (en) | 2006-10-23 | 2017-01-10 | Micell Technologies, Inc. | Holder for electrically charging a substrate during coating |
US9737642B2 (en) | 2007-01-08 | 2017-08-22 | Micell Technologies, Inc. | Stents having biodegradable layers |
US9789233B2 (en) | 2008-04-17 | 2017-10-17 | Micell Technologies, Inc. | Stents having bioabsorbable layers |
US9981072B2 (en) | 2009-04-01 | 2018-05-29 | Micell Technologies, Inc. | Coated stents |
US10117972B2 (en) | 2011-07-15 | 2018-11-06 | Micell Technologies, Inc. | Drug delivery medical device |
US10188772B2 (en) | 2011-10-18 | 2019-01-29 | Micell Technologies, Inc. | Drug delivery medical device |
US10232092B2 (en) | 2010-04-22 | 2019-03-19 | Micell Technologies, Inc. | Stents and other devices having extracellular matrix coating |
US10272606B2 (en) | 2013-05-15 | 2019-04-30 | Micell Technologies, Inc. | Bioabsorbable biomedical implants |
US10464100B2 (en) | 2011-05-31 | 2019-11-05 | Micell Technologies, Inc. | System and process for formation of a time-released, drug-eluting transferable coating |
US10835396B2 (en) | 2005-07-15 | 2020-11-17 | Micell Technologies, Inc. | Stent with polymer coating containing amorphous rapamycin |
US11039943B2 (en) | 2013-03-12 | 2021-06-22 | Micell Technologies, Inc. | Bioabsorbable biomedical implants |
US11369498B2 (en) | 2010-02-02 | 2022-06-28 | MT Acquisition Holdings LLC | Stent and stent delivery system with improved deliverability |
US11426494B2 (en) | 2007-01-08 | 2022-08-30 | MT Acquisition Holdings LLC | Stents having biodegradable layers |
CN116623105A (en) * | 2023-07-24 | 2023-08-22 | 中科艾尔(北京)科技有限公司 | Ultra-high purity 316L stainless steel and preparation method thereof |
US11904118B2 (en) | 2010-07-16 | 2024-02-20 | Micell Medtech Inc. | Drug delivery medical device |
Citations (11)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US2451749A (en) * | 1946-05-31 | 1948-10-19 | Kreisler Mfg Corp Jacques | Bracelet or the like and method of making the same |
US4244754A (en) * | 1975-07-05 | 1981-01-13 | The Foundation: The Research Institute Of Electric And Magnetic Alloys | Process for producing high damping capacity alloy and product |
US4830003A (en) * | 1988-06-17 | 1989-05-16 | Wolff Rodney G | Compressive stent and delivery system |
US4891080A (en) * | 1988-06-06 | 1990-01-02 | Carpenter Technology Corporation | Workable boron-containing stainless steel alloy article, a mechanically worked article and process for making thereof |
US5449373A (en) * | 1994-03-17 | 1995-09-12 | Medinol Ltd. | Articulated stent |
US5607442A (en) * | 1995-11-13 | 1997-03-04 | Isostent, Inc. | Stent with improved radiopacity and appearance characteristics |
US5690670A (en) * | 1989-12-21 | 1997-11-25 | Davidson; James A. | Stents of enhanced biocompatibility and hemocompatibility |
US5876432A (en) * | 1994-04-01 | 1999-03-02 | Gore Enterprise Holdings, Inc. | Self-expandable helical intravascular stent and stent-graft |
US5919126A (en) * | 1997-07-07 | 1999-07-06 | Implant Sciences Corporation | Coronary stent with a radioactive, radiopaque coating |
US6077298A (en) * | 1999-02-20 | 2000-06-20 | Tu; Lily Chen | Expandable/retractable stent and methods thereof |
US6471721B1 (en) * | 1999-12-30 | 2002-10-29 | Advanced Cardiovascular Systems, Inc. | Vascular stent having increased radiopacity and method for making same |
-
2002
- 2002-03-20 US US10/103,411 patent/US20020144757A1/en not_active Abandoned
Patent Citations (11)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US2451749A (en) * | 1946-05-31 | 1948-10-19 | Kreisler Mfg Corp Jacques | Bracelet or the like and method of making the same |
US4244754A (en) * | 1975-07-05 | 1981-01-13 | The Foundation: The Research Institute Of Electric And Magnetic Alloys | Process for producing high damping capacity alloy and product |
US4891080A (en) * | 1988-06-06 | 1990-01-02 | Carpenter Technology Corporation | Workable boron-containing stainless steel alloy article, a mechanically worked article and process for making thereof |
US4830003A (en) * | 1988-06-17 | 1989-05-16 | Wolff Rodney G | Compressive stent and delivery system |
US5690670A (en) * | 1989-12-21 | 1997-11-25 | Davidson; James A. | Stents of enhanced biocompatibility and hemocompatibility |
US5449373A (en) * | 1994-03-17 | 1995-09-12 | Medinol Ltd. | Articulated stent |
US5876432A (en) * | 1994-04-01 | 1999-03-02 | Gore Enterprise Holdings, Inc. | Self-expandable helical intravascular stent and stent-graft |
US5607442A (en) * | 1995-11-13 | 1997-03-04 | Isostent, Inc. | Stent with improved radiopacity and appearance characteristics |
US5919126A (en) * | 1997-07-07 | 1999-07-06 | Implant Sciences Corporation | Coronary stent with a radioactive, radiopaque coating |
US6077298A (en) * | 1999-02-20 | 2000-06-20 | Tu; Lily Chen | Expandable/retractable stent and methods thereof |
US6471721B1 (en) * | 1999-12-30 | 2002-10-29 | Advanced Cardiovascular Systems, Inc. | Vascular stent having increased radiopacity and method for making same |
Cited By (160)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8066763B2 (en) | 1998-04-11 | 2011-11-29 | Boston Scientific Scimed, Inc. | Drug-releasing stent with ceramic-containing layer |
US8303643B2 (en) | 2001-06-27 | 2012-11-06 | Remon Medical Technologies Ltd. | Method and device for electrochemical formation of therapeutic species in vivo |
US20040204749A1 (en) * | 2003-04-11 | 2004-10-14 | Richard Gunderson | Stent delivery system with securement and deployment accuracy |
US20040267348A1 (en) * | 2003-04-11 | 2004-12-30 | Gunderson Richard C. | Medical device delivery systems |
US7473271B2 (en) | 2003-04-11 | 2009-01-06 | Boston Scientific Scimed, Inc. | Stent delivery system with securement and deployment accuracy |
US9737427B2 (en) | 2004-04-09 | 2017-08-22 | Boston Scientific Scimed, Inc. | Medical device delivery systems |
US9066826B2 (en) | 2004-04-09 | 2015-06-30 | Boston Scientific Scimed, Inc. | Medical device delivery systems |
US20050228478A1 (en) * | 2004-04-09 | 2005-10-13 | Heidner Matthew C | Medical device delivery systems |
WO2005099622A1 (en) | 2004-04-09 | 2005-10-27 | Boston Scientific Limited | Medical device delivery systems |
US7749264B2 (en) | 2004-10-08 | 2010-07-06 | Boston Scientific Scimed, Inc. | Medical devices and methods of making the same |
US7344560B2 (en) | 2004-10-08 | 2008-03-18 | Boston Scientific Scimed, Inc. | Medical devices and methods of making the same |
US20060079953A1 (en) * | 2004-10-08 | 2006-04-13 | Gregorich Daniel J | Medical devices and methods of making the same |
US20060097242A1 (en) * | 2004-11-10 | 2006-05-11 | Mitsubishi Denki Kabushiki Kaisha | Semiconductor light-emitting device |
US20060100696A1 (en) * | 2004-11-10 | 2006-05-11 | Atanasoska Ljiljana L | Medical devices and methods of making the same |
US7727273B2 (en) | 2005-01-13 | 2010-06-01 | Boston Scientific Scimed, Inc. | Medical devices and methods of making the same |
US7938854B2 (en) | 2005-01-13 | 2011-05-10 | Boston Scientific Scimed, Inc. | Medical devices and methods of making the same |
US20100228336A1 (en) * | 2005-01-13 | 2010-09-09 | Stinson Jonathan S | Medical devices and methods of making the same |
US20060153729A1 (en) * | 2005-01-13 | 2006-07-13 | Stinson Jonathan S | Medical devices and methods of making the same |
US20060224231A1 (en) * | 2005-03-31 | 2006-10-05 | Gregorich Daniel J | Endoprostheses |
EP2353554A1 (en) | 2005-03-31 | 2011-08-10 | Boston Scientific Limited | Stent |
US8435280B2 (en) | 2005-03-31 | 2013-05-07 | Boston Scientific Scimed, Inc. | Flexible stent with variable width elements |
US7641983B2 (en) | 2005-04-04 | 2010-01-05 | Boston Scientific Scimed, Inc. | Medical devices including composites |
US20060222844A1 (en) * | 2005-04-04 | 2006-10-05 | Stinson Jonathan S | Medical devices including composites |
US20060229711A1 (en) * | 2005-04-05 | 2006-10-12 | Elixir Medical Corporation | Degradable implantable medical devices |
US10350093B2 (en) | 2005-04-05 | 2019-07-16 | Elixir Medical Corporation | Degradable implantable medical devices |
US20060259126A1 (en) * | 2005-05-05 | 2006-11-16 | Jason Lenz | Medical devices and methods of making the same |
US20060276875A1 (en) * | 2005-05-27 | 2006-12-07 | Stinson Jonathan S | Medical devices |
EP2191794A2 (en) | 2005-05-27 | 2010-06-02 | Boston Scientific Limited | Medical devices |
US20090214373A1 (en) * | 2005-05-27 | 2009-08-27 | Boston Scientific Scimed, Inc. | Medical Devices |
US20060276910A1 (en) * | 2005-06-01 | 2006-12-07 | Jan Weber | Endoprostheses |
US8758429B2 (en) | 2005-07-15 | 2014-06-24 | Micell Technologies, Inc. | Polymer coatings containing drug powder of controlled morphology |
US9827117B2 (en) | 2005-07-15 | 2017-11-28 | Micell Technologies, Inc. | Polymer coatings containing drug powder of controlled morphology |
US10835396B2 (en) | 2005-07-15 | 2020-11-17 | Micell Technologies, Inc. | Stent with polymer coating containing amorphous rapamycin |
US11911301B2 (en) | 2005-07-15 | 2024-02-27 | Micell Medtech Inc. | Polymer coatings containing drug powder of controlled morphology |
US10898353B2 (en) | 2005-07-15 | 2021-01-26 | Micell Technologies, Inc. | Polymer coatings containing drug powder of controlled morphology |
US20070114701A1 (en) * | 2005-11-18 | 2007-05-24 | Stenzel Eric B | Methods and apparatuses for manufacturing medical devices |
US7799153B2 (en) | 2005-11-18 | 2010-09-21 | Boston Scientific Scimed, Inc. | Methods and apparatuses for manufacturing medical devices |
US8840660B2 (en) | 2006-01-05 | 2014-09-23 | Boston Scientific Scimed, Inc. | Bioerodible endoprostheses and methods of making the same |
US8089029B2 (en) | 2006-02-01 | 2012-01-03 | Boston Scientific Scimed, Inc. | Bioabsorbable metal medical device and method of manufacture |
US8574615B2 (en) | 2006-03-24 | 2013-11-05 | Boston Scientific Scimed, Inc. | Medical devices having nanoporous coatings for controlled therapeutic agent delivery |
US8187620B2 (en) | 2006-03-27 | 2012-05-29 | Boston Scientific Scimed, Inc. | Medical devices comprising a porous metal oxide or metal material and a polymer coating for delivering therapeutic agents |
US8048150B2 (en) | 2006-04-12 | 2011-11-01 | Boston Scientific Scimed, Inc. | Endoprosthesis having a fiber meshwork disposed thereon |
US8852625B2 (en) | 2006-04-26 | 2014-10-07 | Micell Technologies, Inc. | Coatings containing multiple drugs |
US11007307B2 (en) | 2006-04-26 | 2021-05-18 | Micell Technologies, Inc. | Coatings containing multiple drugs |
US9737645B2 (en) | 2006-04-26 | 2017-08-22 | Micell Technologies, Inc. | Coatings containing multiple drugs |
US11850333B2 (en) | 2006-04-26 | 2023-12-26 | Micell Medtech Inc. | Coatings containing multiple drugs |
US9415142B2 (en) | 2006-04-26 | 2016-08-16 | Micell Technologies, Inc. | Coatings containing multiple drugs |
US9011516B2 (en) | 2006-06-20 | 2015-04-21 | Boston Scientific Scimed, Inc. | Medical devices including composites |
US20080161900A1 (en) * | 2006-06-20 | 2008-07-03 | Boston Scientific Scimed, Inc. | Medical devices including composites |
US8815275B2 (en) | 2006-06-28 | 2014-08-26 | Boston Scientific Scimed, Inc. | Coatings for medical devices comprising a therapeutic agent and a metallic material |
US8771343B2 (en) | 2006-06-29 | 2014-07-08 | Boston Scientific Scimed, Inc. | Medical devices with selective titanium oxide coatings |
US8052743B2 (en) | 2006-08-02 | 2011-11-08 | Boston Scientific Scimed, Inc. | Endoprosthesis with three-dimensional disintegration control |
US8353949B2 (en) | 2006-09-14 | 2013-01-15 | Boston Scientific Scimed, Inc. | Medical devices with drug-eluting coating |
US20080071355A1 (en) * | 2006-09-14 | 2008-03-20 | Boston Scientific Scimed, Inc. | Medical Devices with Drug-Eluting Coating |
US8052744B2 (en) | 2006-09-15 | 2011-11-08 | Boston Scientific Scimed, Inc. | Medical devices and methods of making the same |
US8808726B2 (en) | 2006-09-15 | 2014-08-19 | Boston Scientific Scimed. Inc. | Bioerodible endoprostheses and methods of making the same |
US8128689B2 (en) | 2006-09-15 | 2012-03-06 | Boston Scientific Scimed, Inc. | Bioerodible endoprosthesis with biostable inorganic layers |
US8057534B2 (en) | 2006-09-15 | 2011-11-15 | Boston Scientific Scimed, Inc. | Bioerodible endoprostheses and methods of making the same |
US7955382B2 (en) | 2006-09-15 | 2011-06-07 | Boston Scientific Scimed, Inc. | Endoprosthesis with adjustable surface features |
US8002821B2 (en) | 2006-09-18 | 2011-08-23 | Boston Scientific Scimed, Inc. | Bioerodible metallic ENDOPROSTHESES |
US20080071344A1 (en) * | 2006-09-18 | 2008-03-20 | Boston Scientific Scimed, Inc. | Medical device with porous surface |
US20080069858A1 (en) * | 2006-09-20 | 2008-03-20 | Boston Scientific Scimed, Inc. | Medical devices having biodegradable polymeric regions with overlying hard, thin layers |
US20100305682A1 (en) * | 2006-09-21 | 2010-12-02 | Cleveny Technologies | Specially configured and surface modified medical device with certain design features that utilize the intrinsic properties of tungsten, zirconium, tantalum and/or niobium |
US8769794B2 (en) * | 2006-09-21 | 2014-07-08 | Mico Innovations, Llc | Specially configured and surface modified medical device with certain design features that utilize the intrinsic properties of tungsten, zirconium, tantalum and/or niobium |
WO2008063775A3 (en) * | 2006-10-13 | 2009-10-22 | Boston Scientific Limited | Medical devices including hardened alloys |
US7780798B2 (en) | 2006-10-13 | 2010-08-24 | Boston Scientific Scimed, Inc. | Medical devices including hardened alloys |
WO2008063775A2 (en) * | 2006-10-13 | 2008-05-29 | Boston Scientific Limited | Medical devices including hardened alloys |
US9539593B2 (en) | 2006-10-23 | 2017-01-10 | Micell Technologies, Inc. | Holder for electrically charging a substrate during coating |
US7981150B2 (en) | 2006-11-09 | 2011-07-19 | Boston Scientific Scimed, Inc. | Endoprosthesis with coatings |
WO2008082698A2 (en) | 2006-12-28 | 2008-07-10 | Boston Scientific Limited | Medical devices and methods of making the same |
US20080160259A1 (en) * | 2006-12-28 | 2008-07-03 | Boston Scientific Scimed, Inc. | Medical devices and methods of making the same |
US8715339B2 (en) | 2006-12-28 | 2014-05-06 | Boston Scientific Scimed, Inc. | Bioerodible endoprostheses and methods of making the same |
US9034456B2 (en) | 2006-12-28 | 2015-05-19 | Boston Scientific Scimed, Inc. | Medical devices and methods of making the same |
US8080055B2 (en) | 2006-12-28 | 2011-12-20 | Boston Scientific Scimed, Inc. | Bioerodible endoprostheses and methods of making the same |
US11426494B2 (en) | 2007-01-08 | 2022-08-30 | MT Acquisition Holdings LLC | Stents having biodegradable layers |
US10617795B2 (en) | 2007-01-08 | 2020-04-14 | Micell Technologies, Inc. | Stents having biodegradable layers |
US9737642B2 (en) | 2007-01-08 | 2017-08-22 | Micell Technologies, Inc. | Stents having biodegradable layers |
US8070797B2 (en) | 2007-03-01 | 2011-12-06 | Boston Scientific Scimed, Inc. | Medical device with a porous surface for delivery of a therapeutic agent |
US8431149B2 (en) | 2007-03-01 | 2013-04-30 | Boston Scientific Scimed, Inc. | Coated medical devices for abluminal drug delivery |
US8067054B2 (en) | 2007-04-05 | 2011-11-29 | Boston Scientific Scimed, Inc. | Stents with ceramic drug reservoir layer and methods of making and using the same |
US9775729B2 (en) | 2007-04-17 | 2017-10-03 | Micell Technologies, Inc. | Stents having controlled elution |
US9433516B2 (en) | 2007-04-17 | 2016-09-06 | Micell Technologies, Inc. | Stents having controlled elution |
US9486338B2 (en) | 2007-04-17 | 2016-11-08 | Micell Technologies, Inc. | Stents having controlled elution |
US7976915B2 (en) | 2007-05-23 | 2011-07-12 | Boston Scientific Scimed, Inc. | Endoprosthesis with select ceramic morphology |
US8211162B2 (en) | 2007-05-25 | 2012-07-03 | Boston Scientific Scimed, Inc. | Connector node for durable stent |
US20080294238A1 (en) * | 2007-05-25 | 2008-11-27 | Boston Scientific Scimed, Inc. | Connector Node for Durable Stent |
US8900651B2 (en) | 2007-05-25 | 2014-12-02 | Micell Technologies, Inc. | Polymer films for medical device coating |
US8790392B2 (en) | 2007-07-11 | 2014-07-29 | Boston Scientific Scimed, Inc. | Endoprosthesis coating |
US7942926B2 (en) | 2007-07-11 | 2011-05-17 | Boston Scientific Scimed, Inc. | Endoprosthesis coating |
US20110224783A1 (en) * | 2007-07-11 | 2011-09-15 | Boston Scientific Scimed, Inc. | Endoprosthesis coating |
US8002823B2 (en) | 2007-07-11 | 2011-08-23 | Boston Scientific Scimed, Inc. | Endoprosthesis coating |
US9284409B2 (en) | 2007-07-19 | 2016-03-15 | Boston Scientific Scimed, Inc. | Endoprosthesis having a non-fouling surface |
US20090149942A1 (en) * | 2007-07-19 | 2009-06-11 | Boston Scientific Scimed, Inc. | Endoprosthesis having a non-fouling surface |
US7931683B2 (en) | 2007-07-27 | 2011-04-26 | Boston Scientific Scimed, Inc. | Articles having ceramic coated surfaces |
US8815273B2 (en) | 2007-07-27 | 2014-08-26 | Boston Scientific Scimed, Inc. | Drug eluting medical devices having porous layers |
US8221822B2 (en) | 2007-07-31 | 2012-07-17 | Boston Scientific Scimed, Inc. | Medical device coating by laser cladding |
US8900292B2 (en) | 2007-08-03 | 2014-12-02 | Boston Scientific Scimed, Inc. | Coating for medical device having increased surface area |
US8052745B2 (en) | 2007-09-13 | 2011-11-08 | Boston Scientific Scimed, Inc. | Endoprosthesis |
US8029554B2 (en) | 2007-11-02 | 2011-10-04 | Boston Scientific Scimed, Inc. | Stent with embedded material |
US7938855B2 (en) | 2007-11-02 | 2011-05-10 | Boston Scientific Scimed, Inc. | Deformable underlayer for stent |
US8216632B2 (en) | 2007-11-02 | 2012-07-10 | Boston Scientific Scimed, Inc. | Endoprosthesis coating |
US20090118814A1 (en) * | 2007-11-02 | 2009-05-07 | Boston Scientific Scimed, Inc. | Endoprosthesis coating |
US20090118812A1 (en) * | 2007-11-02 | 2009-05-07 | Boston Scientific Scimed, Inc. | Endoprosthesis coating |
US9789233B2 (en) | 2008-04-17 | 2017-10-17 | Micell Technologies, Inc. | Stents having bioabsorbable layers |
US10350333B2 (en) | 2008-04-17 | 2019-07-16 | Micell Technologies, Inc. | Stents having bioabsorable layers |
US8920491B2 (en) | 2008-04-22 | 2014-12-30 | Boston Scientific Scimed, Inc. | Medical devices having a coating of inorganic material |
US8932346B2 (en) | 2008-04-24 | 2015-01-13 | Boston Scientific Scimed, Inc. | Medical devices having inorganic particle layers |
US7998192B2 (en) | 2008-05-09 | 2011-08-16 | Boston Scientific Scimed, Inc. | Endoprostheses |
US20090299468A1 (en) * | 2008-05-29 | 2009-12-03 | Boston Scientific Scimed, Inc. | Endoprosthesis coating |
US8236046B2 (en) | 2008-06-10 | 2012-08-07 | Boston Scientific Scimed, Inc. | Bioerodible endoprosthesis |
US8449603B2 (en) | 2008-06-18 | 2013-05-28 | Boston Scientific Scimed, Inc. | Endoprosthesis coating |
US20090319032A1 (en) * | 2008-06-18 | 2009-12-24 | Boston Scientific Scimed, Inc | Endoprosthesis coating |
US9078777B2 (en) | 2008-07-09 | 2015-07-14 | Boston Scientific Scimed, Inc. | Stent with non-round cross-section in an unexpanded state |
US20100010620A1 (en) * | 2008-07-09 | 2010-01-14 | Boston Scientific Scimed, Inc. | Stent |
US9981071B2 (en) | 2008-07-17 | 2018-05-29 | Micell Technologies, Inc. | Drug delivery medical device |
US10350391B2 (en) | 2008-07-17 | 2019-07-16 | Micell Technologies, Inc. | Drug delivery medical device |
US9510856B2 (en) | 2008-07-17 | 2016-12-06 | Micell Technologies, Inc. | Drug delivery medical device |
US9486431B2 (en) | 2008-07-17 | 2016-11-08 | Micell Technologies, Inc. | Drug delivery medical device |
US7985252B2 (en) | 2008-07-30 | 2011-07-26 | Boston Scientific Scimed, Inc. | Bioerodible endoprosthesis |
US20100057188A1 (en) * | 2008-08-28 | 2010-03-04 | Boston Scientific Scimed, Inc. | Endoprostheses with porous regions and non-polymeric coating |
US8114153B2 (en) | 2008-09-05 | 2012-02-14 | Boston Scientific Scimed, Inc. | Endoprostheses |
US20100063584A1 (en) * | 2008-09-05 | 2010-03-11 | Boston Scientific Scimed, Inc. | Endoprostheses |
US8382824B2 (en) | 2008-10-03 | 2013-02-26 | Boston Scientific Scimed, Inc. | Medical implant having NANO-crystal grains with barrier layers of metal nitrides or fluorides |
US8231980B2 (en) | 2008-12-03 | 2012-07-31 | Boston Scientific Scimed, Inc. | Medical implants including iridium oxide |
US8834913B2 (en) | 2008-12-26 | 2014-09-16 | Battelle Memorial Institute | Medical implants and methods of making medical implants |
US20100217370A1 (en) * | 2009-02-20 | 2010-08-26 | Boston Scientific Scimed, Inc. | Bioerodible Endoprosthesis |
US8267992B2 (en) | 2009-03-02 | 2012-09-18 | Boston Scientific Scimed, Inc. | Self-buffering medical implants |
WO2010101988A2 (en) | 2009-03-04 | 2010-09-10 | Boston Scientific Scimed, Inc. | Endoprostheses |
US8071156B2 (en) | 2009-03-04 | 2011-12-06 | Boston Scientific Scimed, Inc. | Endoprostheses |
US10653820B2 (en) | 2009-04-01 | 2020-05-19 | Micell Technologies, Inc. | Coated stents |
US9981072B2 (en) | 2009-04-01 | 2018-05-29 | Micell Technologies, Inc. | Coated stents |
US8287937B2 (en) | 2009-04-24 | 2012-10-16 | Boston Scientific Scimed, Inc. | Endoprosthese |
US20110022162A1 (en) * | 2009-07-23 | 2011-01-27 | Boston Scientific Scimed, Inc. | Endoprostheses |
US11369498B2 (en) | 2010-02-02 | 2022-06-28 | MT Acquisition Holdings LLC | Stent and stent delivery system with improved deliverability |
US8668732B2 (en) | 2010-03-23 | 2014-03-11 | Boston Scientific Scimed, Inc. | Surface treated bioerodible metal endoprostheses |
US20110238153A1 (en) * | 2010-03-26 | 2011-09-29 | Boston Scientific Scimed, Inc. | Endoprostheses |
US9687864B2 (en) | 2010-03-26 | 2017-06-27 | Battelle Memorial Institute | System and method for enhanced electrostatic deposition and surface coatings |
US8895099B2 (en) | 2010-03-26 | 2014-11-25 | Boston Scientific Scimed, Inc. | Endoprosthesis |
US20110238149A1 (en) * | 2010-03-26 | 2011-09-29 | Boston Scientific Scimed, Inc. | Endoprosthesis |
WO2011119430A1 (en) | 2010-03-26 | 2011-09-29 | Boston Scientific Scimed, Inc. | Endoprosthesis |
US8795762B2 (en) | 2010-03-26 | 2014-08-05 | Battelle Memorial Institute | System and method for enhanced electrostatic deposition and surface coatings |
WO2011126708A1 (en) | 2010-04-06 | 2011-10-13 | Boston Scientific Scimed, Inc. | Endoprosthesis |
US8834560B2 (en) | 2010-04-06 | 2014-09-16 | Boston Scientific Scimed, Inc. | Endoprosthesis |
US10232092B2 (en) | 2010-04-22 | 2019-03-19 | Micell Technologies, Inc. | Stents and other devices having extracellular matrix coating |
US8920490B2 (en) | 2010-05-13 | 2014-12-30 | Boston Scientific Scimed, Inc. | Endoprostheses |
US11904118B2 (en) | 2010-07-16 | 2024-02-20 | Micell Medtech Inc. | Drug delivery medical device |
WO2012096995A2 (en) | 2011-01-11 | 2012-07-19 | Boston Scientific Scimed, Inc. | Coated medical devices |
WO2012142319A1 (en) | 2011-04-13 | 2012-10-18 | Micell Technologies, Inc. | Stents having controlled elution |
US10464100B2 (en) | 2011-05-31 | 2019-11-05 | Micell Technologies, Inc. | System and process for formation of a time-released, drug-eluting transferable coating |
US10729819B2 (en) | 2011-07-15 | 2020-08-04 | Micell Technologies, Inc. | Drug delivery medical device |
US10117972B2 (en) | 2011-07-15 | 2018-11-06 | Micell Technologies, Inc. | Drug delivery medical device |
US10188772B2 (en) | 2011-10-18 | 2019-01-29 | Micell Technologies, Inc. | Drug delivery medical device |
US11357623B2 (en) | 2011-12-13 | 2022-06-14 | Boston Scientific Scimed, Inc. | Decalcifying heart valve |
US9987130B2 (en) | 2011-12-13 | 2018-06-05 | Boston Scientific Scimed, Inc. | Decalcifying heart valve |
WO2013090145A1 (en) | 2011-12-13 | 2013-06-20 | Boston Scientific Scimed, Inc. | Decalcifying heart valve |
US11039943B2 (en) | 2013-03-12 | 2021-06-22 | Micell Technologies, Inc. | Bioabsorbable biomedical implants |
US10272606B2 (en) | 2013-05-15 | 2019-04-30 | Micell Technologies, Inc. | Bioabsorbable biomedical implants |
CN106148852A (en) * | 2015-04-02 | 2016-11-23 | 上海微创医疗器械(集团)有限公司 | A kind of alloy material and implantable medical devices |
CN105821343A (en) * | 2016-05-24 | 2016-08-03 | 江苏金基特钢有限公司 | Production method of special steel |
CN116623105A (en) * | 2023-07-24 | 2023-08-22 | 中科艾尔(北京)科技有限公司 | Ultra-high purity 316L stainless steel and preparation method thereof |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US20020144757A1 (en) | Stainless steel alloy with improved radiopaque characteristics | |
US8580189B2 (en) | Stainless steel alloy having lowered nickel-chrominum toxicity and improved biocompatibility | |
US7780798B2 (en) | Medical devices including hardened alloys | |
EP1373590B1 (en) | Ultra-high-strength precipitation-hardenable stainless steel and elongated strip made therefrom | |
US6238455B1 (en) | High-strength, titanium-bearing, powder metallurgy stainless steel article with enhanced machinability | |
EP2220261B1 (en) | Lean austenitic stainless steel | |
EP1423548B1 (en) | Duplex steel alloy | |
EP2287346A1 (en) | Bainitic steels with boron | |
EP2455508A1 (en) | High strength / corrosion-resistant,.austenitic stainless steel with carbon - nitrogen complex additive, and method for manufacturing same | |
US11779477B2 (en) | Radiopaque intraluminal stents | |
KR101363674B1 (en) | High strength, high toughness steel alloy | |
US20130103161A1 (en) | Iron Based Alloys for Bioabsorbable Stent | |
US8034197B2 (en) | Ultra-high strength stainless steels | |
EP2676685A1 (en) | Stent composed of an iron alloy | |
JP2002502464A (en) | Nickel-free stainless steel for biomedical applications | |
US6793745B2 (en) | Maraging type spring steel | |
EP1087029A2 (en) | Improved steel composition | |
Herliansyah et al. | The effect of annealing temperature on the physical and mechanical properties of stainless steel 316L for stent application | |
US11702714B2 (en) | High fracture toughness, high strength, precipitation hardenable stainless steel | |
Craig et al. | Mechanical properties and microstructure of platinum enhanced radiopaque stainless steel (PERSS) alloys | |
JP2000239799A (en) | Ni-FREE TWO-PHASE STAINLESS STEEL FOR LIVING BODY | |
EP2634277B1 (en) | Co-based alloy for living body and stent | |
WO2021204811A1 (en) | Bioresorbable fe-mn-si-x alloys for medical implants | |
CN109778079B (en) | Stainless steel for medical instruments, manufacturing method, heat treatment method and application | |
WO2001079576A1 (en) | High-strength precipitation-hardenable stainless steel suitable for casting in air |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
AS | Assignment |
Owner name: SCIMED LIFE SYSTEMS, INC., MINNESOTA Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:CRAIG, CHARLES HORACE;RADISCH, HERBERT R., JR.;TROZERA, THOMAS;REEL/FRAME:013080/0722 Effective date: 20020626 |
|
AS | Assignment |
Owner name: BOSTON SCIENTIFIC SCIMED, INC., MINNESOTA Free format text: CHANGE OF NAME;ASSIGNOR:SCIMED LIFE SYSTEMS, INC.;REEL/FRAME:018505/0868 Effective date: 20050101 Owner name: BOSTON SCIENTIFIC SCIMED, INC.,MINNESOTA Free format text: CHANGE OF NAME;ASSIGNOR:SCIMED LIFE SYSTEMS, INC.;REEL/FRAME:018505/0868 Effective date: 20050101 |
|
STCB | Information on status: application discontinuation |
Free format text: ABANDONED -- AFTER EXAMINER'S ANSWER OR BOARD OF APPEALS DECISION |