WO1996040308A1 - Treatments to reduce thrombogeneticity in heart valves made from titanium and its alloys - Google Patents
Treatments to reduce thrombogeneticity in heart valves made from titanium and its alloys Download PDFInfo
- Publication number
- WO1996040308A1 WO1996040308A1 PCT/US1996/009104 US9609104W WO9640308A1 WO 1996040308 A1 WO1996040308 A1 WO 1996040308A1 US 9609104 W US9609104 W US 9609104W WO 9640308 A1 WO9640308 A1 WO 9640308A1
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- component
- silicon
- titanium
- diamond
- carbon
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- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00005—The prosthesis being constructed from a particular material
- A61F2310/00011—Metals or alloys
- A61F2310/00035—Other metals or alloys
- A61F2310/00101—Molybdenum or Mo-based alloys
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00005—The prosthesis being constructed from a particular material
- A61F2310/00011—Metals or alloys
- A61F2310/00035—Other metals or alloys
- A61F2310/00107—Palladium or Pd-based alloys
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00005—The prosthesis being constructed from a particular material
- A61F2310/00011—Metals or alloys
- A61F2310/00035—Other metals or alloys
- A61F2310/00137—Tungsten or W-based alloys
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00005—The prosthesis being constructed from a particular material
- A61F2310/00011—Metals or alloys
- A61F2310/00035—Other metals or alloys
- A61F2310/00149—Platinum or Pt-based alloys
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2310/00—Prostheses classified in A61F2/28 or A61F2/30 - A61F2/44 being constructed from or coated with a particular material
- A61F2310/00389—The prosthesis being coated or covered with a particular material
- A61F2310/00574—Coating or prosthesis-covering structure made of carbon, e.g. of pyrocarbon
- A61F2310/0058—Coating made of diamond or of diamond-like carbon DLC
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B29—WORKING OF PLASTICS; WORKING OF SUBSTANCES IN A PLASTIC STATE IN GENERAL
- B29C—SHAPING OR JOINING OF PLASTICS; SHAPING OF MATERIAL IN A PLASTIC STATE, NOT OTHERWISE PROVIDED FOR; AFTER-TREATMENT OF THE SHAPED PRODUCTS, e.g. REPAIRING
- B29C71/00—After-treatment of articles without altering their shape; Apparatus therefor
- B29C71/0009—After-treatment of articles without altering their shape; Apparatus therefor using liquids, e.g. solvents, swelling agents
- B29C2071/0027—Removing undesirable residual components, e.g. solvents, unreacted monomers
-
- B—PERFORMING OPERATIONS; TRANSPORTING
- B29—WORKING OF PLASTICS; WORKING OF SUBSTANCES IN A PLASTIC STATE IN GENERAL
- B29K—INDEXING SCHEME ASSOCIATED WITH SUBCLASSES B29B, B29C OR B29D, RELATING TO MOULDING MATERIALS OR TO MATERIALS FOR MOULDS, REINFORCEMENTS, FILLERS OR PREFORMED PARTS, e.g. INSERTS
- B29K2023/00—Use of polyalkenes or derivatives thereof as moulding material
- B29K2023/04—Polymers of ethylene
- B29K2023/06—PE, i.e. polyethylene
- B29K2023/0658—PE, i.e. polyethylene characterised by its molecular weight
- B29K2023/0683—UHMWPE, i.e. ultra high molecular weight polyethylene
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10S—TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10S623/00—Prosthesis, i.e. artificial body members, parts thereof, or aids and accessories therefor
- Y10S623/92—Method or apparatus for preparing or treating prosthetic
- Y10S623/922—Heart
Definitions
- the present invention relates to decreasing the thrombogeneticity of heart valves and other medical implants made from titanium and its alloys.
- Titanium has become a popular metal for the manufacture of human implants.
- the FDA considers titanium and many of its alloys ("titanium based materials") to be biocompatible.
- Titanium based materials also are easily machined, are not overly brittle, and are durable enough for the manufacture of most medical implants. Unfortunately, titanium based materials also tend to encourage thrombogenesis. This tendency is undesirable, particularly for implants used in the circulatory system.
- An example of a medical implant that is used in the circulatory system is a heart valve. A method for reducing the thrombogeneticity of titanium and its alloys would be highly desirable.
- the present invention provides a method for coating a titanium based component with amorphous diamond-like carbon to reduce the thrombogeneticity of the component.
- the titanium based component is a heart valve.
- the component is placed in a vacuum chamber and heated to about 600°-650°C (1112-1202°F). Thereafter, silicon is deposited onto the component, and the component is simultaneously bombarded with a beam of energetic ions to form a metal-silicide bonding layer. The component then is cooled to at least below about 100°C (212°F), preferably about 80°C (176°F), and a diamond ⁇ like carbon precursor is condensed onto the metal-silicide bonding layer. The precursor is simultaneously bombarded with a beam of energetic ions, preferably nitrogen ions, to form a coating of diamond-like carbon.
- Amorphous carbon, or “diamond-like carbon” (“DLC”) is a biocompatible coating material that is less thrombogenic than titanium.
- DLC diamond-like carbon
- a primary concern about using DLC for medical implants is the strength of the bond that forms between the substrate and the DLC coating.
- the present invention provides a method for coating titanium based components, particularly components for use in the circulatory system, with a tightly adhered coat of DLC to reduce the thrombogeneticity of the component.
- the present invention ensures strong adherence between the DLC and the surface of the titanium based component by forming a titanium-silicide interlayer.
- a titanium-silicide interlayer In order to knit the successive layers of metal-silicon-DLC together effectively, it is necessary to supply a bond-interface for the metal- silicon bond as well as for the silicon-DLC bond. Without limiting the present invention, it is believed that the present method achieves this result by forming strong interatomic bonds having a character that is intermediate to the type of bond that exists between the atoms in the metal and the type of bonds that exist in the silicon.
- Silicon is chosen as the substance to form the interlayer because (a) DLC is known to adhere better to silicon than to any other substrat —which is attributed to strong SiC bonds formed at the interface of the two materials—and (b) titanium is known to react with silicon to form a disilicide (TiS 2 ) when reacted with silicon.
- the method for coating the titanium based components uses ion beam assisted deposition of silicon, followed by deposition of DLC. After conventional cleaning of the component to remove superficial contaminants, such as grease, the component is placed in a vacuum chamber that has been evacuated to a base pressure of preferably less than about 10" 5 torr.
- the component then is bombarded with ions, preferably argon ions, at an energy range between about 10 - 100 keV, preferably around 10 keV. This ion bombardment provides an effective means to remove some of the remaining adsorbed atoms from the surface.
- ions preferably argon ions
- Titanium based components tend to have a thin oxide layer on their surface which should be removed in order to form the suicide interlayer. This is accomplished by heating the titanium component sufficiently to "dissolve" the oxide layer.
- the component preferably should be heated to about 600-650°C (1112-1202°F) before condensing silicon on the surface of the component.
- silicon can be deposited on the surface of the component using known means.
- a preferred means is to position the workpiece directly over a volatilization hearth which is maintained at a preferred temperature of about 1900°C (3450°F), until a preferred coating thickness of between about 100-200 nm has been achieved.
- the thickness of the coating may be monitored by standard methods, e. g. , using the frequency change of a quartz crystal oscillator.
- the component preferably should be simultaneously bombarded with an energetic beam of ions, preferably nitrogen ions, at an energy range between about 500 eV to 100 keV, preferably between about 10-20 keV, in order to form a layer of titanium suicide at the titanium-silicon interface.
- Nitrogen is preferred for the ion beams of the present invention because nitrogen ions actually will bond with the substrate/coating or interlayer. Inert ions, such as argon and/or helium ions, will not bond with the substrate/film. The use of inert ions could result in bubbling and/or a weaker coating. Although it has not been proven, it is believed that strong carbon-nitrogen bonds form in the DLC layer when the ions used to make the DLC are nitrogen ions. In any event, the use of a beam of nitrogen ions can result in DLC coatings that increase wear resistance and decrease friction up to 5-7 times more than DLC coatings formed using other types of ions.
- the component should be cooled to at least below about 100°C (212°F), preferably to about 80°C (176°F). The cooling preferably should be done without removing the component from the vacuum chamber.
- a diamond-like carbon (DLC) precursor should be deposited.
- the DLC precursor is polyphenyl ether.
- Preferable diffusion pump fluids include, but are not necessarily limited to: polyphenyl ether; polydimethyl siloxane; pentaphenyltrimethyl siloxane; and, elcosyl napthalene.
- the precursor is vaporized and condensed onto the surface of the component using known means. Generally, the precursor is placed in a reservoir, heated to between about 150 ⁇ C-170°C (302°F-338°F), and directed onto the cooled component. Substantially simultaneously, the component should be bombarded, either in a continuous or interrupted fashion, with an energetic beam of ions.
- a preferred ion source is nitrogen.
- Other suitable ions include, but are not necessarily limited to, argon, hydrogen, silicon, methane, helium, or neon.
- the ion beam should have an energy between about 500 eV to 100 keV, preferably between about 10-30 keV. The energy of bombardment must be sufficient to ionize the constituent molecules in the precursor film, and to rupture the bonds between hydrogen and other atoms, thereby releasing the hydrogen into the surrounding vacuum to be pumped away.
- the rate of arrival of the ions should be controlled in relation to the rate of arrival of the precursor molecules. This process should require about one ion for every 100 atoms in the final product coating; however, the ion-to-atom ratio will vary according to the mass and energy of the ion species. Typically, 100 eV must be deposited for each carbon atom in the coating. Persons of ordinary skill in the art will recognize how to achieve the correct linear energy of transfer in the ionizing process. The procedure should be continued until a thickness of DLC between about 100 nm-10 microns is achieved.
- a DLC coating of approximately 1 micron in thickness is prepared by nitrogen ion bombardment of a polyphenyl ether precursor.
- a titanium based heart valve comprised of a titanium alloy containing vanadium and aluminum is cleaned in isopropyl alcohol prior to coating. Isopropyl alcohol is chosen because it leaves few, if any, residues. Wear testing reveals that, under some circumstances, there could be a loss of adhesion of the coating.
- a titanium alloy heart valve of the same composition as in Example 1 is treated using a bond-coat of silicon.
- the component After conventional solvent cleaning of the component to remove superficial contaminants, such as grease, the component is placed in a vacuum chamber that has been evacuated to a base pressure of 10" 5 torr. The component then is bombarded with nitrogen ions at an energy of about 10 keV to remove some of the remaining adsorbed atoms from the surface. The component is heated to about 600°C (1112°F). Silicon then is deposited onto the outer surface of the component. The workpiece is positioned directly over the volatilization hearth which is maintained at a temperature of about 1900°C (3450°F), until a preferred coating thickness of about 100 nm has been achieved. The thickness of the coating is monitored by standard methods, e. g. , using the frequency change of a quartz crystal oscillator.
- the component is simultaneously bombarded with an energetic beam of nitrogen ions at an energy of about 20 keV and an ion-to-atom ratio of at least 1 ion to 10 silicon atoms for about 15 minutes to form a layer of metal suicide at the metal-silicon interface.
- the component is cooled to about 80°C without removing the component from the vacuum chamber.
- Polyphenyl ether is heated to at least about 150°C (302°F) and condensed onto the surface of the component.
- the component simultaneously is bombarded with an energetic beam nitrogen ions having an energy of about 20 keV and an ion-to-atom ratio of at least 1 ion to 100 precursor molecules. The procedure is continued until a thickness of DLC of about 100 nm is achieved.
Abstract
Description
Claims
Priority Applications (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP9501505A JPH11506807A (en) | 1995-06-07 | 1996-06-06 | Method for reducing thrombus formation in titanium and its alloy heart valves |
EP96918178A EP0833672A1 (en) | 1995-06-07 | 1996-06-06 | Treatments to reduce thrombogeneticity in heart valves made from titanium and its alloys |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US08/472,495 US5605714A (en) | 1994-03-29 | 1995-06-07 | Treatments to reduce thrombogeneticity in heart valves made from titanium and its alloys |
US08/472,495 | 1995-06-07 |
Publications (1)
Publication Number | Publication Date |
---|---|
WO1996040308A1 true WO1996040308A1 (en) | 1996-12-19 |
Family
ID=23875728
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/US1996/009104 WO1996040308A1 (en) | 1995-06-07 | 1996-06-06 | Treatments to reduce thrombogeneticity in heart valves made from titanium and its alloys |
Country Status (4)
Country | Link |
---|---|
US (1) | US5605714A (en) |
EP (1) | EP0833672A1 (en) |
JP (1) | JPH11506807A (en) |
WO (1) | WO1996040308A1 (en) |
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- 1996-06-06 JP JP9501505A patent/JPH11506807A/en active Pending
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Cited By (7)
Publication number | Priority date | Publication date | Assignee | Title |
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WO2003035928A2 (en) * | 2001-10-25 | 2003-05-01 | Nttf Gmbh | Mechanically and thermodynamically stable amorphous carbon layers for temperature-sensitive surfaces |
WO2003035928A3 (en) * | 2001-10-25 | 2003-12-24 | Nttf Gmbh | Mechanically and thermodynamically stable amorphous carbon layers for temperature-sensitive surfaces |
WO2004101841A2 (en) * | 2003-05-14 | 2004-11-25 | Friedrich-Baur Gmbh | Method for producing ceramic gradient layers on a metallic substrate by means of an in situ reaction with non-oxidising precursor in a si-c-n (m) system |
WO2004101841A3 (en) * | 2003-05-14 | 2005-04-14 | Friedrich Baur Gmbh | Method for producing ceramic gradient layers on a metallic substrate by means of an in situ reaction with non-oxidising precursor in a si-c-n (m) system |
US8997349B2 (en) | 2010-09-17 | 2015-04-07 | Thoratec Corporation | Manufacturing method for medical equipment for reducing platelet adhesion on a surface in contact with blood |
CN112522673A (en) * | 2021-02-18 | 2021-03-19 | 中南大学湘雅医院 | Biomedical magnesium alloy surface rare earth composite film and preparation method thereof |
CN112522673B (en) * | 2021-02-18 | 2021-04-27 | 中南大学湘雅医院 | Biomedical magnesium alloy surface rare earth composite film and preparation method thereof |
Also Published As
Publication number | Publication date |
---|---|
EP0833672A1 (en) | 1998-04-08 |
US5605714A (en) | 1997-02-25 |
JPH11506807A (en) | 1999-06-15 |
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