ABSTRACT
Abstract
A solid lubricant for use in a medical device for lubrication of a synovial joint, wherein said lubricant comprises at least one of: a high-molecular weight hyaluronic acid; a crosslinked high-molecular weight hyaluronic acid; and a hyaluronic acid of at least two different high-molecular weights being crosslinked to form a semisolid gel.
Description
This application is a continuation of U.S. application Ser. No. 15/049,155, filed on 22 Feb. 2016, which is a continuation of U.S. application Ser. No. 13/382,853, filed on 6 Jan. 2012, which is the U.S. national phase of International Application No. PCT/SE2010/050801, filed 12 Jul. 2010, which designated the U.S. and claims the benefit of U.S. Provisional Nos. 61/229,755, filed 30 Jul. 2009; 61/229,738 filed 30 Jul. 2009; 61/229,739 filed 30 Jul. 2009; 61/229,743 filed 30 Jul. 2009; 61/229,745 filed 30 Jul. 2009; 61/229,746 filed 30 Jul. 2009; 61/229,747 filed 30 Jul. 2009; 61/229,748 filed 30 Jul. 2009; 61/229,751 filed 30 Jul. 2009; 61/229,752 filed 30 Jul. 2009; 61/229,761 filed 30 Jul. 2009; 61/229,767 filed 30 Jul. 2009; 61/229,778 filed 30 Jul. 2009; 61/229,786 filed 30 Jul. 2009; 61/229,789 filed 30 Jul. 2009; 61/229,796 filed 30 Jul. 2009; 61/229,735 filed 30 Jul. 2009; and which claims priority to Swedish Application Nos.: 0900981-2 filed 10 Jul. 2009; 0900957-2 filed 10 Jul. 2009; 0900958-0 filed 10 Jul. 2009; 0900959-8 filed 10 Jul. 2009; 0900960-6 filed 10 Jul. 2009; 0900962-2 filed 10 Jul. 2009; 0900963-0 filed 10 Jul. 2009; 0900965-5 filed 10 Jul. 2009; 0900966-3 filed 10 Jul. 2009; 0900968-9 filed 10 Jul. 2009; 0900969-7 filed 10 Jul. 2009; 0900970-5 filed 10 Jul. 2009; 0900972-1 filed 10 Jul. 2009; 0900973-9 filed 10 Jul. 2009; 090097 4-7 filed 10 Jul. 2009; 0900976-2 filed 10 Jul. 2009 and 0900978-8 filed 10 Jul. 2009, the entire contents of each of which are hereby incorporated by reference.
FIELD OF INVENTION
The present invention relates generally to a medical device for implantation in a joint, and a method of providing said medical device.
BACKGROUND
The synovial joints are the most common types of joints in mammals, provide free movement between the bones they join, and are typical of nearly all limb joints. They can be compared to mechanical bearings in a musculoskeletal machine. A synovial joint is the meeting point of two bones, movably arranged in relation to each other. The end surfaces of said bones are usually smooth and rounded, and covered by articular cartilage. A synovial membrane encapsulates the joint, forming a joint cavity, which contains synovial fluid. Outside the synovial membrane is a fibrous capsule and ligaments, forming an articular capsule.
A healthy joint is remarkably effective with coefficients of friction lower than those obtainable with man-made journal bearings (frictional bearings). Furthermore, the constant process of renewal and restoration of living tissue ensures that a synovial joint have a durability far superior to that of any artificial bearing. So far, no artificial joint can equal the performance of a normal human joint.
There are however both natural and pathological processes leading to deteriorated joint function. With age and wear, the articular cartilage becomes less effective as a shock absorber and a lubricated surface. Different degenerative joint diseases, such as arthritis, osteoartrithis, or osteoarthrosis, accelerate the deterioration.
Developments in material science, together with modern surgical techniques have made it possible to replace one or more of the contact surfaces, or the entire joint. Due to their weight-carrying function, hip and knee joints are most frequently addressed by surgical intervention and implantation of artificial components, or joint replacement surgery.
The lubrication of a healthy joint has been the focus of many researchers. Articular cartilage is elastic, fluid-filled, and backed by a relatively impervious layer of calcified cartilage and bone. This means that load-induced compression of cartilage will force interstitial fluid to flow laterally within the tissue and to surface through adjacent cartilage. As that area, in turn, becomes load bearing, it is partially protected by the newly expressed fluid above it. This is a special form of hydrodynamic lubrication, so-called because the dynamic motion of the bearing areas produces an aqueous layer that separates and protects the contact points.
Boundary layer lubrication is the second major low-friction characteristic of normal joints. Here, the critical factor is proposed to be a small glycoprotein called lubricin. The lubricating properties of this synovium-derived molecule are highly specific and depend on its ability to bind to articular cartilage where it retains a protective layer of water molecules. Lubricin is not effective in artificial systems and thus does not lubricate artificial joints.
Other lubricating mechanisms have been proposed; some remain under investigation. Interestingly, hyaluronic acid, the molecule that makes synovial fluid viscous (synovia means âlike egg whiteâ), has largely been excluded as a lubricant of the cartilage-on-cartilage bearing. Instead, hyaluronate lubricates a quite different site of surface contactâthat of synovium on cartilage. The well-vascularized, well-innervated synovium must alternately contract and then expand to cover non-loaded cartilage surfaces as each joint moves through its normal range of motion. This process must proceed freely. Were synovial tissue to be pinched, there would be immediate pain, intraarticular bleeding, and inevitable functional compromise. The rarity of these problems testifies to the effectiveness of hyaluronate-mediated synovial lubrication.
WO 01/85179 discloses fluid compositions and methods for lubrication of mammalian joints are disclosed, including both natural and artificial fluids. Synovial fluid acts to lubricate the bearing surfaces of bones and bone-like structures which are held in frictional contact within biological joints. Such fluids may be used to treat arthritic, injured, and diseased joints. Synovial fluid containing a dextran-based hydrogel with lipids provides enhanced rheological and tribological properties of such a fluid. Phospholipids are particularly useful in dextran-based compositions for synovial fluid. One phospholipid that can be used advantageously in synovial fluid is dipalmitoyl phosphatidylcholine (DPPC).
Su et al. (Design and Mechanics Simulation of Bionic Lubrication System of Artificial Joints, Journal of Bionic Engineering, Volume 3, Issue 3, 2006) describe a new structure for artificial joints with a joint capsule which is designed to overcome the drawback of current prostheses that omit many functions of the lubricant and the joint capsule. The new structure is composed of three components: lubricant, artificial joint and artificial joint capsule. The lubricant sealed in the capsule can not only reduce the wear of the artificial joint but also prevents the wear particles leaking into the body. Thus, unexpected reactions between the wear particles and body can be avoided completely.
Radin et al. (Joint Lubrication with Artificial Lubricants, Arthritis & Rheumatism, 2005, Vol. 14, 1, 126-129) studied the joint lubricating properties, in vitro, in bovine metatarsal-phalangeal joints, of silicone fluid, methyl cellulose and polyvinyl-pyrrolidone compared to buffer, serum and synovial fluid. As has been previously reported, synovial fluid was almost twice as good as serum and buffer, which are equivalent in their joint lubricating qualities. Among the three artificial lubricants tested, only polyvinyl-pyrrolidone was superior to buffer or serum as a joint lubricant at 37° C. At 55° C., both polyvinyl-pyrrolidone and methyl cellulose had the same effect. At no time was any of the artificial lubricants tested as effective at reducing joint friction as was synovial fluid. Silicone fluid was consistently an inferior joint lubricant compared with buffer or serum. It was concluded that effective joint lubrication with artificial lubricants depends on their boundary and hydrophilic properties, rather than directly on their flow characteristics
Lubricants can be divided into three groups; gaseous, liquid and solid. For the purposes of this description, a solid lubricant is defined as a lubricant being solid and substantially maintaining its shape at body temperature and at a pressure and mechanical stress encountered in the mammal body, including in the joints of a mammal body.
Most solid lubricants are produced as thin solid films on sliding surfaces. They are also used as fillers in self-lubricating metallic, ceramic, and polymeric composites. In most cases, a transfer film is found on the sliding surfaces. For solid lubricant films, strong adhesion is key for long service life.
Boric acid (H3 BO3) films, which provide the component surfaces with a self-replenishing solid lubricant, are formed from the reaction of the B2 O3 surface (deposited by various conventional methods) on the component surface with the water present in the body of the recipient-patient. Conventional methods that can be employed to deposit either a boron, H3 BO3, or B2 O3 film on the annuloplasty ring component surface include vacuum evaporation (with or without ion bombardment) and simple oven curing of a thin layer over the implant surface. The self-lubricating mechanism of H3 BO3 is governed by its unique layered, triclinic crystal structure which allows sheets of atoms to easily slide over each other during movement, thus minimizing component wear and friction.
When present at a sliding surface, solid lubricants function the same way as their liquid counterparts. Specifically, they shear easily to provide low friction and to prevent wear damage between the sliding surfaces. Several inorganic materials (e.g. molybdenum disulfide, graphite, hexagonal boron nitride, boric acid) can provide excellent lubrication. Most of these solids owe their lubricity to a lamellar or layered crystal structure. A few others (e.g. soft metals, polytetrafluoroethylene, polyimide, certain oxides and rare-earth fluorides, diamond and diamond-like carbons, fullerenes) can also provide lubrication although they do not have a layered crystal structure.
Certain polymers are also used as solid lubricants because the attractive properties they combine are unavailable in other solid lubricants. Polymers are particularly favored for applications where cost, weight, corrosion and biocompatibility are the major considerations. In short, solid lubricants have been around for a long time, and they have been meeting some very important and critical tribological needs.
UHMWPE is another polymer used widely in total joint replacements (Kurtz et al., 1999). Because of the very long molecules and highly entangled molecular chains, it provides better wear resistance than PTFE. However, wear of this polymer still poses a major obstacle for the longevity of the total joint replacements. Recent efforts to solve these problems have increased interest in the structure, morphology, and mechanical properties of the UHMWPE and in various surface ad structural treatment processes (such as crosslinking).
(Solid lubricants and self-lubricating films, Bharat Bhushan, Modern tribology handbook, Vol. 1, 2000)
Hyaluronan or hyaluronic acid is approved by the FDA for the treatment of osteoarthritis in a method called viscosupplementation. In this treatment, hyaluronan is injected through the articular capsule and the synovial membrane, into the joint cavity, supplementing the synovial fluid. While mechanically cushioning the joint, and providing a temporary analgesic effect, this treatment is nevertheless recommended only as a last alternative to surgery. The injection is difficult to perform, and painful.
The present inventor set out to develop an implantable device and method for the lubrication of joints, in particular synovial joints, including natural joints, joints comprising artificial components following partial joint replacement surgery, and complete artificial joints, following complete joint replacement surgery.
Preferably said solid lubricant comprises hyaluronan (hyaluronic acid) and optionally suitable additives. Hyaluronan is particularly preferred, as this is a nontoxic, noninflammatory biodegradable natural substance.
Hyaluronan is available in different qualities, such as relating to purity, molecular weight and degree of crosslinking. With regard to molecular weight, many different qualities are available, ranging from low molecular weight (LMW) or about 50,000 Da to high molecular weight (HMW) or about 4-6,000,000 Da. An increase in molecular weight results in corresponding increase in viscosity, from an oily liquid to a gel-like semisolid.
For example WO 01/60868 discloses single phase gels for preventing the formation of surgical adhesions. The gels are prepared by reacting an aqueous solution of a polyanionic polysaccharide, such as hyaluronic acid or carboxymethyl cellulose, with divinyl sulfone, to form a gel, the solution is neutralized, and a solid is precipitated from the solution. The solid can be redissolved in water to form a gel having properties which can be modified to suit a particular application. Using a similar approach, a hyaluronic acid containing solid can be produced, and inserted in contact with the articular surfaces in a joint, where the surrounding aqueous body fluids redissolve the solid, releasing hyaluronic acid to lubricate the joint.
US 2009181058 discloses an injectable or implantable rod-shaped formulation for delivery of osteogenic proteins to treat osteoporotic and/or osteopenic bone are disclosed. The formulation comprises hyaluronic acid derivatives and osteogenic proteins, and optional excipients and active ingredients such as a bone resorption inhibitor.
WO 2006/034383 discloses viscoelastic compounds encompassing any compound having viscoelastic properties including, but not limited to, cellulose polymers and their derivatives (for example hydroxypropyl methyl cellulose) and polysaccharides including, but not limited to, glucosaminoglycans such as hyaluronic acid and synthetic linear polymers. By way of example, the viscoelastic compound may be chondroitin sulphate, polyacrylamide, collagen, pectin, synthetic polymer-modified carbohydrate, hyaluronic acid or salts or esters thereof in essentially pure form and dry form, or mixtures of two or more of these compounds.
Suitable sodium hylauronates may in one aspect have a molecular mass of at least 5-6 million before sterilization which when dissolved to a 1% (w/w) solution will obtain similar characteristics as Healon® ophthalmic viscoelastic solution (OVD) (available from Abbot Medical Optics, Inc., Santa Ana, California), or when dissolved to 2.3% (w/w) will resemble Healon® 5ⲠOVD (available from Abbot Medical Optics, Inc., Santa Ana, California)). The preparation and purification of this type of sodium hyaluronate and to generate viscoelastic solutions are described in more detail in U.S. Pat. Nos. 4,141,973 and 6,086,697. Also high viscosity, high molecular mass sodium hyaluronates such as those described in U.S. Pat. No. 5,681,825 (marketed as viscoelastic under the trade name Healon® GV) can be used with the present invention. One of ordinary skill in the art will realize that, in other aspects of the
invention, suitable sodium hylauronates may have a lower molecular mass, as low as 100,000 Da. Clearly, the desired molecular weight is dependent on the class of polymer that is desired to be used in association with the present invention. By way of example, and not of limitation, suitable viscoelastic solutions may be formed using HPMC in the weight range of from about 30,000 to about several hundred thousand daltons. Similarly, suitable viscoelastic solutions may be formed using chondroitin sulphate in the weight range starting from about 20,000 to about 30,000. In general, the molecular weight of the chosen viscoelastic compound (whether it is sodium hyaluronate, HPMC or another viscoelastic) will be selected based on the desired viscoelastic properties of the final solution.
Hip joint Osteoarthritis is a syndrome in which low-grade inflammation results in pain in the hip joints, caused by abnormal wearing of the Cartilage that acts as a cushion inside if the hip joint. This abnormal wearing of the cartilage also results in a decrease of the joints lubricating fluid called Synovial fluid. Hip joint Osteoarthritis is estimated to affect 80% of all people over 65 years of age, in more or less serious forms.
The present treatment for hip osteoarthritis comprises NSAID drugs, local injections of Hyaluronic acid or Glucocorticoid to help lubricating the hip joint, and replacing parts of the hip joint with a prosthesis through hip joint surgery.
The replacing of parts of the hip joint is one of the most common surgeri
This application is a continuation of U.S. application Ser. No. 15/049,155, filed on 22 Feb. 2016, which is a continuation of U.S. application Ser. No. 13/382,853, filed on 6 Jan. 2012, which is the U.S. national phase of International Application No. PCT/SE2010/050801, filed 12 Jul. 2010, which designated the U.S. and claims the benefit of U.S. Provisional Nos. 61/229,755, filed 30 Jul. 2009; 61/229,738 filed 30 Jul. 2009; 61/229,739 filed 30 Jul. 2009; 61/229,743 filed 30 Jul. 2009; 61/229,745 filed 30 Jul. 2009; 61/229,746 filed 30 Jul. 2009; 61/229,747 filed 30 Jul. 2009; 61/229,748 filed 30 Jul. 2009; 61/229,751 filed 30 Jul. 2009; 61/229,752 filed 30 Jul. 2009; 61/229,761 filed 30 Jul. 2009; 61/229,767 filed 30 Jul. 2009; 61/229,778 filed 30 Jul. 2009; 61/229,786 filed 30 Jul. 2009; 61/229,789 filed 30 Jul. 2009; 61/229,796 filed 30 Jul. 2009; 61/229,735 filed 30 Jul. 2009; and which claims priority to Swedish Application Nos.: 0900981-2 filed 10 Jul. 2009; 0900957-2 filed 10 Jul. 2009; 0900958-0 filed 10 Jul. 2009; 0900959-8 filed 10 Jul. 2009; 0900960-6 filed 10 Jul. 2009; 0900962-2 filed 10 Jul. 2009; 0900963-0 filed 10 Jul. 2009; 0900965-5 filed 10 Jul. 2009; 0900966-3 filed 10 Jul. 2009; 0900968-9 filed 10 Jul. 2009; 0900969-7 filed 10 Jul. 2009; 0900970-5 filed 10 Jul. 2009; 0900972-1 filed 10 Jul. 2009; 0900973-9 filed 10 Jul. 2009; 090097 4-7 filed 10 Jul. 2009; 0900976-2 filed 10 Jul. 2009 and 0900978-8 filed 10 Jul. 2009, the entire contents of each of which are hereby incorporated by reference.
FIELD OF INVENTION
The present invention relates generally to a medical device for implantation in a joint, and a method of providing said medical device.
BACKGROUND
The synovial joints are the most common types of joints in mammals, provide free movement between the bones they join, and are typical of nearly all limb joints. They can be compared to mechanical bearings in a musculoskeletal machine. A synovial joint is the meeting point of two bones, movably arranged in relation to each other. The end surfaces of said bones are usually smooth and rounded, and covered by articular cartilage. A synovial membrane encapsulates the joint, forming a joint cavity, which contains synovial fluid. Outside the synovial membrane is a fibrous capsule and ligaments, forming an articular capsule.
A healthy joint is remarkably effective with coefficients of friction lower than those obtainable with man-made journal bearings (frictional bearings). Furthermore, the constant process of renewal and restoration of living tissue ensures that a synovial joint have a durability far superior to that of any artificial bearing. So far, no artificial joint can equal the performance of a normal human joint.
There are however both natural and pathological processes leading to deteriorated joint function. With age and wear, the articular cartilage becomes less effective as a shock absorber and a lubricated surface. Different degenerative joint diseases, such as arthritis, osteoartrithis, or osteoarthrosis, accelerate the deterioration.
Developments in material science, together with modern surgical techniques have made it possible to replace one or more of the contact surfaces, or the entire joint. Due to their weight-carrying function, hip and knee joints are most frequently addressed by surgical intervention and implantation of artificial components, or joint replacement surgery.
The lubrication of a healthy joint has been the focus of many researchers. Articular cartilage is elastic, fluid-filled, and backed by a relatively impervious layer of calcified cartilage and bone. This means that load-induced compression of cartilage will force interstitial fluid to flow laterally within the tissue and to surface through adjacent cartilage. As that area, in turn, becomes load bearing, it is partially protected by the newly expressed fluid above it. This is a special form of hydrodynamic lubrication, so-called because the dynamic motion of the bearing areas produces an aqueous layer that separates and protects the contact points.
Boundary layer lubrication is the second major low-friction characteristic of normal joints. Here, the critical factor is proposed to be a small glycoprotein called lubricin. The lubricating properties of this synovium-derived molecule are highly specific and depend on its ability to bind to articular cartilage where it retains a protective layer of water molecules. Lubricin is not effective in artificial systems and thus does not lubricate artificial joints.
Other lubricating mechanisms have been proposed; some remain under investigation. Interestingly, hyaluronic acid, the molecule that makes synovial fluid viscous (synovia means âlike egg whiteâ), has largely been excluded as a lubricant of the cartilage-on-cartilage bearing. Instead, hyaluronate lubricates a quite different site of surface contactâthat of synovium on cartilage. The well-vascularized, well-innervated synovium must alternately contract and then expand to cover non-loaded cartilage surfaces as each joint moves through its normal range of motion. This process must proceed freely. Were synovial tissue to be pinched, there would be immediate pain, intraarticular bleeding, and inevitable functional compromise. The rarity of these problems testifies to the effectiveness of hyaluronate-mediated synovial lubrication.
WO 01/85179 discloses fluid compositions and methods for lubrication of mammalian joints are disclosed, including both natural and artificial fluids. Synovial fluid acts to lubricate the bearing surfaces of bones and bone-like structures which are held in frictional contact within biological joints. Such fluids may be used to treat arthritic, injured, and diseased joints. Synovial fluid containing a dextran-based hydrogel with lipids provides enhanced rheological and tribological properties of such a fluid. Phospholipids are particularly useful in dextran-based compositions for synovial fluid. One phospholipid that can be used advantageously in synovial fluid is dipalmitoyl phosphatidylcholine (DPPC).
Su et al. (Design and Mechanics Simulation of Bionic Lubrication System of Artificial Joints, Journal of Bionic Engineering, Volume 3, Issue 3, 2006) describe a new structure for artificial joints with a joint capsule which is designed to overcome the drawback of current prostheses that omit many functions of the lubricant and the joint capsule. The new structure is composed of three components: lubricant, artificial joint and artificial joint capsule. The lubricant sealed in the capsule can not only reduce the wear of the artificial joint but also prevents the wear particles leaking into the body. Thus, unexpected reactions between the wear particles and body can be avoided completely.
Radin et al. (Joint Lubrication with Artificial Lubricants, Arthritis & Rheumatism, 2005, Vol. 14, 1, 126-129) studied the joint lubricating properties, in vitro, in bovine metatarsal-phalangeal joints, of silicone fluid, methyl cellulose and polyvinyl-pyrrolidone compared to buffer, serum and synovial fluid. As has been previously reported, synovial fluid was almost twice as good as serum and buffer, which are equivalent in their joint lubricating qualities. Among the three artificial lubricants tested, only polyvinyl-pyrrolidone was superior to buffer or serum as a joint lubricant at 37° C. At 55° C., both polyvinyl-pyrrolidone and methyl cellulose had the same effect. At no time was any of the artificial lubricants tested as effective at reducing joint friction as was synovial fluid. Silicone fluid was consistently an inferior joint lubricant compared with buffer or serum. It was concluded that effective joint lubrication with artificial lubricants depends on their boundary and hydrophilic properties, rather than directly on their flow characteristics
Lubricants can be divided into three groups; gaseous, liquid and solid. For the purposes of this description, a solid lubricant is defined as a lubricant being solid and substantially maintaining its shape at body temperature and at a pressure and mechanical stress encountered in the mammal body, including in the joints of a mammal body.
Most solid lubricants are produced as thin solid films on sliding surfaces. They are also used as fillers in self-lubricating metallic, ceramic, and polymeric composites. In most cases, a transfer film is found on the sliding surfaces. For solid lubricant films, strong adhesion is key for long service life.
Boric acid (H3 BO3) films, which provide the component surfaces with a self-replenishing solid lubricant, are formed from the reaction of the B2 O3 surface (deposited by various conventional methods) on the component surface with the water present in the body of the recipient-patient. Conventional methods that can be employed to deposit either a boron, H3 BO3, or B2 O3 film on the annuloplasty ring component surface include vacuum evaporation (with or without ion bombardment) and simple oven curing of a thin layer over the implant surface. The self-lubricating mechanism of H3 BO3 is governed by its unique layered, triclinic crystal structure which allows sheets of atoms to easily slide over each other during movement, thus minimizing component wear and friction.
When present at a sliding surface, solid lubricants function the same way as their liquid counterparts. Specifically, they shear easily to provide low friction and to prevent wear damage between the sliding surfaces. Several inorganic materials (e.g. molybdenum disulfide, graphite, hexagonal boron nitride, boric acid) can provide excellent lubrication. Most of these solids owe their lubricity to a lamellar or layered crystal structure. A few others (e.g. soft metals, polytetrafluoroethylene, polyimide, certain oxides and rare-earth fluorides, diamond and diamond-like carbons, fullerenes) can also provide lubrication although they do not have a layered crystal structure.
Certain polymers are also used as solid lubricants because the attractive properties they combine are unavailable in other solid lubricants. Polymers are particularly favored for applications where cost, weight, corrosion and biocompatibility are the major considerations. In short, solid lubricants have been around for a long time, and they have been meeting some very important and critical tribological needs.
UHMWPE is another polymer used widely in total joint replacements (Kurtz et al., 1999). Because of the very long molecules and highly entangled molecular chains, it provides better wear resistance than PTFE. However, wear of this polymer still poses a major obstacle for the longevity of the total joint replacements. Recent efforts to solve these problems have increased interest in the structure, morphology, and mechanical properties of the UHMWPE and in various surface ad structural treatment processes (such as crosslinking).
(Solid lubricants and self-lubricating films, Bharat Bhushan, Modern tribology handbook, Vol. 1, 2000)
Hyaluronan or hyaluronic acid is approved by the FDA for the treatment of osteoarthritis in a method called viscosupplementation. In this treatment, hyaluronan is injected through the articular capsule and the synovial membrane, into the joint cavity, supplementing the synovial fluid. While mechanically cushioning the joint, and providing a temporary analgesic effect, this treatment is nevertheless recommended only as a last alternative to surgery. The injection is difficult to perform, and painful.
The present inventor set out to develop an implantable device and method for the lubrication of joints, in particular synovial joints, including natural joints, joints comprising artificial components following partial joint replacement surgery, and complete artificial joints, following complete joint replacement surgery.
Preferably said solid lubricant comprises hyaluronan (hyaluronic acid) and optionally suitable additives. Hyaluronan is particularly preferred, as this is a nontoxic, noninflammatory biodegradable natural substance.
Hyaluronan is available in different qualities, such as relating to purity, molecular weight and degree of crosslinking. With regard to molecular weight, many different qualities are available, ranging from low molecular weight (LMW) or about 50,000 Da to high molecular weight (HMW) or about 4-6,000,000 Da. An increase in molecular weight results in corresponding increase in viscosity, from an oily liquid to a gel-like semisolid.
For example WO 01/60868 discloses single phase gels for preventing the formation of surgical adhesions. The gels are prepared by reacting an aqueous solution of a polyanionic polysaccharide, such as hyaluronic acid or carboxymethyl cellulose, with divinyl sulfone, to form a gel, the solution is neutralized, and a solid is precipitated from the solution. The solid can be redissolved in water to form a gel having properties which can be modified to suit a particular application. Using a similar approach, a hyaluronic acid containing solid can be produced, and inserted in contact with the articular surfaces in a joint, where the surrounding aqueous body fluids redissolve the solid, releasing hyaluronic acid to lubricate the joint.
US 2009181058 discloses an injectable or implantable rod-shaped formulation for delivery of osteogenic proteins to treat osteoporotic and/or osteopenic bone are disclosed. The formulation comprises hyaluronic acid derivatives and osteogenic proteins, and optional excipients and active ingredients such as a bone resorption inhibitor.
WO 2006/034383 discloses viscoelastic compounds encompassing any compound having viscoelastic properties including, but not limited to, cellulose polymers and their derivatives (for example hydroxypropyl methyl cellulose) and polysaccharides including, but not limited to, glucosaminoglycans such as hyaluronic acid and synthetic linear polymers. By way of example, the viscoelastic compound may be chondroitin sulphate, polyacrylamide, collagen, pectin, synthetic polymer-modified carbohydrate, hyaluronic acid or salts or esters thereof in essentially pure form and dry form, or mixtures of two or more of these compounds.
Suitable sodium hylauronates may in one aspect have a molecular mass of at least 5-6 million before sterilization which when dissolved to a 1% (w/w) solution will obtain similar characteristics as Healon® ophthalmic viscoelastic solution (OVD) (available from Abbot Medical Optics, Inc., Santa Ana, California), or when dissolved to 2.3% (w/w) will resemble Healon® 5ⲠOVD (available from Abbot Medical Optics, Inc., Santa Ana, California)). The preparation and purification of this type of sodium hyaluronate and to generate viscoelastic solutions are described in more detail in U.S. Pat. Nos. 4,141,973 and 6,086,697. Also high viscosity, high molecular mass sodium hyaluronates such as those described in U.S. Pat. No. 5,681,825 (marketed as viscoelastic under the trade name Healon® GV) can be used with the present invention. One of ordinary skill in the art will realize that, in other aspects of the
invention, suitable sodium hylauronates may have a lower molecular mass, as low as 100,000 Da. Clearly, the desired molecular weight is dependent on the class of polymer that is desired to be used in association with the present invention. By way of example, and not of limitation, suitable viscoelastic solutions may be formed using HPMC in the weight range of from about 30,000 to about several hundred thousand daltons. Similarly, suitable viscoelastic solutions may be formed using chondroitin sulphate in the weight range starting from about 20,000 to about 30,000. In general, the molecular weight of the chosen viscoelastic compound (whether it is sodium hyaluronate, HPMC or another viscoelastic) will be selected based on the desired viscoelastic properties of the final solution.
Hip joint Osteoarthritis is a syndrome in which low-grade inflammation results in pain in the hip joints, caused by abnormal wearing of the Cartilage that acts as a cushion inside if the hip joint. This abnormal wearing of the cartilage also results in a decrease of the joints lubricating fluid called Synovial fluid. Hip joint Osteoarthritis is estimated to affect 80% of all people over 65 years of age, in more or less serious forms.
The present treatment for hip osteoarthritis comprises NSAID drugs, local injections of Hyaluronic acid or Glucocorticoid to help lubricating the hip joint, and replacing parts of the hip joint with a prosthesis through hip joint surgery.
The replacing of parts of the hip joint is one of the most common surgeries to date performed at hundreds of thousand of patients in the world every year. The most common method comprises placing a metal prosthesis in Femur and a plastic bowl in Acetabulum. This operation is usually done through a lateral incision in the hip and upper thigh and through, Fascia Lata and the lateral muscles of the thigh. To get access to the hip joint, the supporting hip joint capsule attached to Femur and Ilium of Pelvis needs to be penetrated, making it difficult to get a fully functional joint after the surgery. Femur is then cut at the neck with a bone saw and the prosthesis is placed in femur either with bone cement or without. Acetabulum is slightly enlarged using an Acetabular reamer, and the plastic bowl is positioned using screws or bone cement.
The surgery typically requires one week of hospitalization due to the increased risk of infection. The recovery process is on average about 6 weeks, but even after this period the patient should not perform any physical activates that places large strain on the joint.
SUMMARY
An implantable medical device for lubrication of a synovial joint having a joint cavity is provided. The implantable device comprises a solid lubricant and a feeding device, wherein said feeding device is adapted to feed said solid lubricant into the joint cavity for lubricating the synovial joint.
According to one embodiment, the solid lubricant is adapted to be placed within an implantable cartridge having an opening into the joint cavity. An inner diameter of the opening could have substantially the same diameter as the inner diameter of said cartridge.
In some embodiments, the solid lubricant could have thixotropic or shear thinning properties, such that the viscosity of said solid lubricant is reduced when said solid lubricant is exposed to strain in the joint cavity.
According to other embodiments, the solid lubricant comprises high-molecular weight hyaluronic acid, which could be crosslinked high-molecular weight hyaluronic acid or hyaluronic acids of at least two different high-molecular weights, crosslinked to form a semisolid or solid gel.
According to another embodiments, the solid lubricant comprises a crosslinking agent chosen from 1, 2, 3, 4-diepoxybutane, divinyl sulfone.
The solid lubricant could be a hydrophilic polymer chosen from synthetic and natural polysaccharides, which could be selected from a group consisting of: hydroxyethyl cellulose, carboxymethyl cellulose, xanthan gum, chondroitin sulfate, heparin, protein, sulfated protein, synthetic water-soluble polymers.
According to one embodiment, the protein comprises a protein selected from a group consisting of: collagen, elastin, albumin, and globulin.
According to one embodiment, the sulfated protein could comprise a sulfated protein selected from a group consisting of: keratin sulfate, and sulfated aminoglycosaminoglycans.
According to one embodiment, the synthetic water-soluble polymer is a synthetic water-soluble polymer selected from a group consisting of: polyvinyl alcohol, co-polymers of polyvinyl alcohol, and co-polymers of poly-(hydroxethyl) methacrylate.
According to yet another embodiment, the medical device is adapted to be implanted in the area of the hip joint, such that said solid lubricant can be inserted into the joint cavity of the hip joint.
The medical device could be adapted to at least partially be implanted in the caput femur, such that the feeding device can feed the solid lubricant into the hip joint cavity, towards the acetabulum.
According to yet another embodiment, the implantable device is adapted to be inserted into a bore in the femoral bone, which could be a bore from the lateral side of the femoral bone, in the region of the major trochanter, or a bore in the pelvis, such that the feeding device can feed the solid lubricant into the hip joint cavity, towards the caput femur. The medical device could for example be adapted to be inserted into the bore in the pelvis, from the acetabulum side of the pelvic bone or from the abdominal side of the pelvic bone.
According to yet another embodiment, the implantable medical device is adapted to be implanted in the area of the knee joint, such that said solid lubricant can be inserted into the joint cavity of the knee joint.
According to yet another embodiment, the medical device is adapted to at least partially be implanted distally in the femoral bone, such that the feeding device can feed the solid lubricant into the knee joint cavity, towards the tibia bone.
According to yet another embodiment, the implantable device is adapted to be inserted into a bore in the distal portion of the femoral bone.
According to yet another embodiment, the medical device is adapted to at least partially be implanted proximally in the tibia bone, such that the feeding device can feed the solid lubricant into the knee joint cavity, towards the femoral bone.
According to yet another embodiment, the implantable device is adapted to be inserted into a bore in the proximal portion of the tibia bone.
According to yet another embodiment, the medical device is adapted to be implanted in the area of the shoulder joint, such that the solid lubricant can be inserted into the joint cavity of the shoulder joint.
According to yet another embodiment, the medical device is adapted to at least partially be implanted in the scapula bone, such that the feeding device can feed the solid lubricant into the shoulder joint cavity, towards the humerus bone, or implanted in the humerus bone, such that the feeding device can feed the solid lubricant into the shoulder joint cavity, towards the scapula bone.
According to yet another embodiment, the medical device further comprises a retention member for retaining the medical device inside of the bore, the retention member comprises at least one bone contacting portion adapted to press on the bone of the inside of the bore for retaining said medical device in the bore. The retention member could be comprises at least one spring member adapted to exert force on said at least one bone contacting portion.
The feeding device could according to one embodiment comprises an energized feeding device, which could comprise a motor.
In other embodiments, the feeding device comprises an elastic member, which could be a spring member or a member of elastic material.
According to yet another embodiment, the feeding is adapted to be powered by a pressurized gaseous fluid.
According to yet another embodiment, the medical device is adapted to, at least partially, be placed in a prosthesis comprising at least one joint surface being adapted for implantation.
The medical device could comprise a cartridge being adapted to be exchanged when said solid lubrication housed inside said cartridge has ended.
In yet another embodiment, the medical device further comprises an implantable sleeve adapted to be placed within a bone of the patient, and further adapted to receive said implantable medical device.
A method for improving the lubrication of a synovial joint of a patient is further provided. The method comprises the steps of drilling or punching a chamber in a bone of the patient, such that an opening of the chamber is located in the joint cavity, and implanting a medical device into the chamber comprising a solid lubricant.
In one embodiment, the method further comprises the step of implanting a feeding device adapted to feed said solid lubricant into the joint cavity for lubricating the synovial joint.
According to some embodiments the solid lubricant is housed within a cartridge, and the step of implanting the medical device could comprise the step of implanting said cartridge into the chamber.
In some embodiments, the step of drilling or punching a chamber in a bone of the patient could comprise the step of drilling or punching a chamber in a bone in the area of the hip joint, such that said solid lubricant can be inserted into the joint cavity of the hip joint. The area of the hip joint could be in the caput femur or in pelvis.
According to one embodiment, the step of implanting said cartridge into the chamber could comprise the step of implanting the cartridge into a bore created in the caput femur, such that the feeding device can feed the solid lubricant into the hip joint cavity, towards the acetabulum.
According to yet another embodiment, the step of implanting the cartridge into a bore could comprise the step of implanting the medical device into the bore from the lateral side of the femoral bone, in the region of the major trochanter.
The step of implanting the cartridge into the chamber could comprise the step of implanting the cartridge into pelvis from the abdominal side of the pelvis, such that the feeding device can feed the solid lubricant into the hip joint cavity, towards the caput femur.
In yet another embodiment, the step of drilling or punching a chamber in a bone of the patient could comprise the step of drilling or punching a chamber in a bone in the area of the knee joint, such that said solid lubricant can be inserted into the joint cavity of the knee joint.
The step drilling or punching a chamber in a bone of the patient comprises the step of drilling or punching a chamber in the femoral bone or the tibia bone.
In yet another embodiment, the step of implanting the cartridge into the chamber could comprise the step of implanting the cartridge into a bore created in the femoral bone, such that the feeding device can feed the solid lubricant into the knee joint cavity.
The step of implanting the cartridge into the chamber could comprise the step of implanting the cartridge into a bore created in the tibia bone, such that the feeding device can feed the solid lubricant into the knee joint cavity.
The step of drilling or punching a chamber in a bone of the patient could comprise the step of drilling or punching a chamber in a bone in the area of the shoulder joint, such that said solid lubricant can be inserted into the joint cavity of the shoulder joint, and the step of drilling or punching a chamber in a bone of the patient could comprise the step of drilling or punching a chamber in the humerus bone or in the scapula bone.
In yet other embodiments, the step of implanting the cartridge into the chamber could comprise the step of implanting said cartridge into a bore created in the humerus bone, such that the feeding device can feed the solid lubricant into the shoulder joint cavity.
The step of implanting the cartridge into the chamber could comprise the step of implanting the cartridge into a bore created in the scapula bone, such that the feeding device can feed the solid lubricant into the shoulder joint cavity.
According to yet another embodiment, the method further comprises the step of implanting a retention member for retaining the medical device inside of said chamber. The step of implanting the retention member could comprise the step of implanting the retention member such that the retention member presses on the bone of the inside of the bore for retaining said medical device in the bore.
The step of implanting a feeding device could comprise the step of implanting an energized feeding device, which in a further step could be connected.
The method could further comprise the step of implanting a prosthesis comprising at least one joint surface being adapted for implantation.
In yet another embodiment, the method could comprise the steps of: creating an incision in the patient, removing the implanted medical device from the patient, and inserting a new medical device, and suturing or stapling the incision.
Please note that any embodiment or part of embodiment, feature, method, associated system, part of system described herein may be combined in any way.
BRIEF DESCRIPTION OF DRAWINGS
The embodiments are now described, by way of example, with reference to the accompanying drawings, in which:
FIG. 1 a is a sectional view of a hip joint;
FIG. 1 b is a sectional view of a collum femur;
FIG. 2 is a sectional view of the femoral bone and the hip joint when a bore is created in the femoral bone 5 ;
FIG. 3 is a sectional view of the femoral bone and the hip joint when a medical device is inserted into the bore in the femoral bone;
FIG. 4 is a sectional view of the femoral bone and the hip joint when the solid lubricant has been pressed into the cavity of the hip joint;
FIG. 5 a is a sectional view of the femoral bone and the hip joint when the medical device/cartridge is being removed from the bore in the femoral bone;
FIG. 5 b is a sectional view of the femoral bone and the hip joint when a replacement cartridge is placed in the bore;
FIG. 6 shows the creation of a bore in the distal part of the femoral bone;
FIG. 7 shows the placing of a cartridge in the distal part of the femoral bone;
FIG. 8 shows the removal of a cartridge in the distal part of the femoral bone;
FIG. 9 a shows the placing of a replacement cartridge in the distal part of the femoral bone;
FIG. 9 b shows a prosthetic part having a bore in which the medical device is adapted to be placed;
FIG. 10 shows bore locations in the femoral and tibia bone;
FIG. 11 shows the medical device when placed in a bore in the humerus bone;
FIG. 12 shows the creation of a bore in the pelvic bone from the abdominal side of the pelvic bone;
FIG. 13 shows the placing of a medical device in the bore created in the pelvic bone;
FIG. 14 shows the hip joint in section when the solid lubricant has been pressed into the hip joint cavity;
FIG. 15 shows the removal of the medical device in the direction of the abdominal cavity;
FIG. 16 shows the placing of a replacement cartridge in the bore in the pelvis, from the abdominal side of the pelvic bone;
FIG. 17 a shows a sectional view of the medical device/cartridge according to one embodiment;
FIG. 17 b shows an alternative embodiment of the retention members;
FIG. 17 c shows a sectional view of the medical device/cartridge according to another embodiment;
FIG. 17 d shows a sectional view of the medical device/cartridge according to an energized embodiment;
FIG. 17 e shows a sectional view of a prosthetic part adapted to replace a portion of the femoral bone;
FIG. 18 is an overall view of a human patient's body showing the position of an implanted assembly according to the invention;
FIG. 19 is a side view of a first embodiment of an implanted assembly according to the invention mounted to a body tissue;
FIG. 20 a is a top view of the assembly shown in FIG. 19 having elliptical shape;
FIG. 20 b is a top view of the assembly shown in FIG. 19 having circular shape;
FIG. 20 c is a sectional view of the assembly shown in FIG. 20
b;
FIG. 21 is an overall view of a human patient's body showing an implanted assembly according to the invention connected to an implanted medical device;
FIG. 22 is a block diagram of a control system comprising a control assembly according to the invention;
FIG. 23 is a sectional view of the control assembly shown in FIG. 19 ;
FIG. 24 is a block diagram showing the different parts of a control assembly according to the invention;
FIG. 25 is a side view of an alternative embodiment of an implanted assembly according to the invention comprising an injection port; and
FIG. 26 is a side view of yet an alternative embodiment of an implanted assembly according to the invention comprising a pump.
FIG. 27 illustrates a system for treating a disease, wherein the system includes an implanted assembly of the invention implanted in a patient.
FIGS. 28 - 42 schematically show various embodiments of the system for wirelessly powering the implanted assembly shown in FIG. 1 .
FIG. 43 is a schematic block diagram illustrating an arrangement for supplying an accurate amount of energy used for the operation of the implanted assembly shown in FIG. 1 .
FIG. 44 schematically shows an energy balance measuring circuit of one of the proposed designs of the system for controlling transmission of wireless energy.
FIG. 45 is a more detailed block diagram of an arrangement for controlling the transmission of wireless energy used for the operation of the implanted assembly shown in FIG. 18 .
FIG. 46 is a circuit for the arrangement shown in FIG. 36 , according to a possible implementation example.
FIG. 47 shows the apparatus, a two way pump and the regulation reservoir.
FIG. 48 shows a block diagram of a reversed seivo system.
FIG. 49 a - 49 c shows a system with a regulation reservoir placed subcutaneous.
FIG. 50 shows an embodiment of the system with hydraulic or pneumatic operation.
FIG. 51 a - 51 c shows a system with a regulation reservoir placed subcutaneous.
DETAILED DESCRIPTION
Biocompatible material is to be understood as being a material with low level of immune response. Biocompatible materials are sometimes also referred to as biomaterials. Analogous is biocompatible metals a metal with low immune response such as titanium or tantalum. The biocompatible metal could also be a biocompatible alloy comprising at least one biocompatible metal.
Form fitting is to be understood as an element having a part or section which is adapted to enable a mechanical connection of said element to at least one other element using said part or section. Form fitted structure is a structure of an element which enables form fitting.
Elasticity is to be understood as a materials ability to deform in an elastic way.
Elastic deformation is when a material deforms under stress (e.g. external forces), but returns to its original shape when the stress is removed. A more elastic material is to be understood as a material having a lower modulus of elasticity. The elastic modulus of an object is defined as the slope of its stress-strain curve in the elastic deformation region. The elastic modulus is calculated as stress/strain, where stress is the force causing the deformation, divided by the area to which the force is applied; and strain is the ratio of the change caused by the stress.
Stiffness is to be understood as the resistance of an elastic body to deformation by an applied force.
Functional hip movements are to be understood as movements of the hip that at least partly correspond to the natural movements of the hip. On some occasions the natural movements of the hip joint might be somewhat limited or altered after hip joint surgery, which makes the functional hip movements of a hip joint with artificial surfaces somewhat different than the functional hip movements of a natural hip joint.
The functional position of an implantable medical device or prosthesis is the position in which the hip joint can perform functional hip movements.
Functional hip joint is a hip joint that can perform functional hip movements either with or without an implanted medical device or prosthesis.
In the following a detailed description of embodiments will be given. In the drawing figures, like reference numerals designate identical or corresponding elements throughout the several figures. It will be appreciated that these figures are for illustration only and are not in any way restricting the scope. Thus, any references to direction, such as âupâ or âdownâ, are only referring to the directions shown in the figures. Also, any dimensions etc. shown in the figures are for illustration purposes.
The functional position or normal functional position, of an implantable medical device or prosthesis is the position in which the hip joint can perform functional hip movements. The final position is to be understood as a functional position in which the medical device needs no further position change.
The medical device according to any of the embodiments could comprise at least one material selected from a group consisting of: polytetrafluoroethylene (PTFE), perfluoroalkoxy (PFA) and fluorinated ethylene propylene (FEP). It is furthermore conceivable that the material comprises a metal alloy, such as cobalt-chromium-molybdenum or titanium or stainless steel, or polyethylene, such as cross-linked polyethylene or gas sterilized polyethylene. The use of ceramic material is also conceivable, either solely in the contacting surfaces, or in the entire medical device, suitable ceramic materials could be zirconium or zirconium dioxide ceramics or alumina ceramics. The part of the medical device in contact with human bone for fixation of the medical device to human bone could comprise a poorhouse structure which could be a porous micro or nano-structure adapted to promote the growth-in of human bone in the medical device for fixation thereof. The porous structure could be achieved by applying a hydroxy-apatite (HA) coating, or a rough open-pored titanium coating, which could be produced by air plasma spraying, in further embodiments a combination of a rough open-pored titanium coating and a HA top layer is also conceivable. The contacting parts could according to some embodiments be made of a self lubricated material such as a waxy polymer, such as PTFE, PFA, FEP, PE and UHNWPE, or a powder metallurgy material which could be infused with a lubricant, which is preferably a biocompatible lubricant, such as a Hyaluronic acid derivate. It is also conceivable that the material of contacting parts or surfaces of the medical device herein is adapted to be constantly or intermittently lubricated in accordance with several of the embodiments disclosed herein. In yet other embodiments parts or portions of the medical device could comprise a combination of metal materials and/or carbon fibers and/or boron, a combination of metal and plastic materials, a combination of metal and carbon based material, a combination of carbon and plastic based material, a combination of flexible and stiff materials, a combination of elastic and less elastic materials, Corian or acrylic polymers.
FIG. 1 shows the hip joint of a human patient in section. The hip joint comprises a caput femur 5 placed at the very top of collum femur 6 which is the top part of the femoral bone 7 . The caput femur is in connection with the acetabulum 8 which is a bowl shaped part of the pelvic bone 9 . Both the caput femur surface 10 and the acetabulum surface 11 is covered with articular cartilage 13 which acts as a cushion in the hip joint. In patients with hip joint osteoarthritis, this articular cartilage 13 is abnormally worn down due to a low grade inflammation. The hip joint is surrounded by the hip joint capsule 12 which provides support for the joint and hinders luxation. After conventional hip joint surgery, penetrating the hip joint capsule 12 , the capsule 12 is dramatically weakened due to the limited healing possibilities of its ligament tissue. By not having to perform a total hip joint replacement the hip joint capsule 12 can remain intact.
The femoral bone, as well as most other bones in the human body comprises cortical bone, the outer dense, sclerotic bone, and cancellous bone comprised of a less dense cell structure comprising the bone marrow.
FIG. 1 b shows a cross-section of the collum femur ( 6 in FIG. 1 a ) displaying the cortical bone 601 and the cancellous bone 602 , the cortical bone 601 thus enclosing the cancellous bone 602 .
FIG. 2 shows the step of creating a bore in the femoral bone from the lateral side of the thigh using an orthopedic drill 2301 . The bore penetrates the most proximal part of the femoral bone, being the caput femur 5 and thus reaches the synovial area of the hip joint comprising the contacting surfaces of caput femur 5 and acetabulum 8 , the synovial area being the area in which the synovial fluid is present.
FIG. 3 shows the step of inserting an implantable device being a cartridge 2302 comprising a solid lubricant 2303 housed within the walls 2304 of the cartridge 2302 . The solid lubricant being adapted to lubricate the contacting surfaces of the acetabulum 8 and the caput femur 5 . The bottom portion of the cartridge 2302 comprises a feeding device adapted to feed the solid lubricant, here comprising a spring member 2306 which presses on a bottom plate 2310 disposed within the cartridge 2302 , further pressing the solid lubricant 2303 through the cartridge 2302 and in the synovial area for lubricating said contacting surfaces. The spring member 2306 is in contact with the dividing wall 2307 of the cartridge, on the other side of the dividing wall 2307 of the cartridge 2302 a retention member 2308 for retaining the cartridge 2302 in the femoral bone is disposed. The retention member comprises two spring loaded <figure-callout id="2311" label="bone engaging members" filenames="US12226316-20250218-D00002.png,US12226316-20250218-D00010.png" state="{{state}}"
CLAIMS
Claims ( 5 )
The invention claimed is:
1. A method for lubricating a synovial joint in a patient, the method comprising feeding a solid lubricant into a joint cavity of the synovial joint of the patient,
wherein the solid lubricant comprises hyaluronic acid, and
controlling the feeding of the solid lubricant in response to one of a pre-programmed time-schedule or to a sensor sensing a physical parameter of the patient.
2. The method according to claim 1 , wherein the hyaluronic acid is a high-molecular weight hyaluronic acid.
3. The method according to claim 2 , wherein the high-molecular weight hyaluronic acid has a molecular weight in the range of 4-6 MDa.
4. The method according to claim 1 , wherein the solid lubricant comprises a hydrophilic polymer comprising a natural polysaccharide.
5. The method according to claim 4 , wherein the solid lubricant comprises a hydrophilic polymer comprising a protein.
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Implantable medical device for lubrication of a synovial joint
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An Implantable medical device for lubrication of a synovial joint
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CA
CA2804973A
patent/CA2804973A1/en
not_active
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2010-07-12
BR
BR112012000639A
patent/BR112012000639B8/en
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IP Right Cessation
2010-07-12
US
US13/382,853
patent/US9265610B2/en
active
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2010-07-12
JP
JP2012519508A
patent/JP5923444B2/en
active
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2010-07-12
EP
EP10797392.7A
patent/EP2451381B1/en
active
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2010-07-12
AU
AU2010269150A
patent/AU2010269150B2/en
not_active
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2010-07-12
MX
MX2012000521A
patent/MX2012000521A/en
active
IP Right Grant
2010-07-12
WO
PCT/SE2010/050801
patent/WO2011005185A1/en
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2016
2016-02-22
US
US15/049,155
patent/US11224516B2/en
active
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2017
2017-02-03
AU
AU2017200767A
patent/AU2017200767B2/en
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2019
2019-11-08
AU
AU2019261818A
patent/AU2019261818B2/en
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active
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2024
2024-01-25
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AU2024200485A
patent/AU2024200485A1/en
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JP5923444B2
( en )
2016-05-24
US20170021153A1
( en )
2017-01-26
WO2011005185A1
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( en )
2021-03-02
AU2019261818B2
( en )
2021-06-17
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( en )
2024-02-15
US11224516B2
( en )
2022-01-18
JP2012532658A
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2012-12-20
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( en )
2019-12-05
CA2804973A1
( en )
2011-01-13
EP2451381A4
( en )
2013-01-09
US20120101456A1
( en )
2012-04-26
EP2451381B1
( en )
2016-04-06
US9265610B2
( en )
2016-02-23
BR112012000639A2
( en )
2016-11-16
MX2012000521A
( en )
2012-07-17
AU2021232799B2
( en )
2023-10-26
AU2017200767B2
( en )
2019-08-08
EP2451381A1
( en )
2012-05-16
AU2010269150B2
( en )
2016-11-03
BR112012000639B8
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2021-06-22
BR112012000639A8
( en )
2018-06-19
US20220202577A1
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2022-06-30
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2021-10-14
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