US20120172997A1 - Self-Detaching Layer for Easy Implant Removal - Google Patents

Self-Detaching Layer for Easy Implant Removal Download PDF

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Publication number
US20120172997A1
US20120172997A1 US13/177,179 US201113177179A US2012172997A1 US 20120172997 A1 US20120172997 A1 US 20120172997A1 US 201113177179 A US201113177179 A US 201113177179A US 2012172997 A1 US2012172997 A1 US 2012172997A1
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United States
Prior art keywords
layer
implant
thickness
implant according
bone
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Abandoned
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US13/177,179
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English (en)
Inventor
Goetz Thorwarth
Cyril Voisard
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
DePuy Spine LLC
DePuy Synthes Products Inc
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Synthes USA LLC
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Application filed by Synthes USA LLC filed Critical Synthes USA LLC
Priority to US13/177,179 priority Critical patent/US20120172997A1/en
Assigned to SYNTHES USA, LLC reassignment SYNTHES USA, LLC ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: SYNTHES GMBH
Assigned to SYNTHES GMBH reassignment SYNTHES GMBH ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: THORWARTH, GOETZ, VOISARD, CYRIL
Publication of US20120172997A1 publication Critical patent/US20120172997A1/en
Assigned to DePuy Synthes Products, LLC reassignment DePuy Synthes Products, LLC CHANGE OF NAME (SEE DOCUMENT FOR DETAILS). Assignors: HAND INNOVATIONS LLC
Assigned to DEPUY SPINE, LLC reassignment DEPUY SPINE, LLC ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: SYNTHES USA, LLC
Assigned to HAND INNOVATIONS LLC reassignment HAND INNOVATIONS LLC ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: DEPUY SPINE, LLC
Assigned to DePuy Synthes Products, Inc. reassignment DePuy Synthes Products, Inc. CHANGE OF NAME (SEE DOCUMENT FOR DETAILS). Assignors: DePuy Synthes Products, LLC
Priority to US15/243,548 priority patent/US10166105B2/en
Assigned to HAND INNOVATIONS LLC reassignment HAND INNOVATIONS LLC CORRECTIVE ASSIGNMENT TO CORRECT THE INCORRECT APPL. NO. 13/486,591 PREVIOUSLY RECORDED AT REEL: 030359 FRAME: 0001. ASSIGNOR(S) HEREBY CONFIRMS THE ASSIGNMENT. Assignors: DEPUY SPINE, LLC
Assigned to DEPUY SPINE, LLC reassignment DEPUY SPINE, LLC CORRECTIVE ASSIGNMENT TO CORRECT THE INCORRECT APPLICATION NO. US 13/486,591 PREVIOUSLY RECORDED ON REEL 030358 FRAME 0945. ASSIGNOR(S) HEREBY CONFIRMS THE ASSIGNMENT. Assignors: SYNTHES USA, LLC
Abandoned legal-status Critical Current

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    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L2420/00—Materials or methods for coatings medical devices
    • A61L2420/02—Methods for coating medical devices
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L2420/00—Materials or methods for coatings medical devices
    • A61L2420/08—Coatings comprising two or more layers
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61L—METHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L2430/00—Materials or treatment for tissue regeneration
    • A61L2430/02—Materials or treatment for tissue regeneration for reconstruction of bones; weight-bearing implants

Definitions

  • the present application generally relates to a device for removing a bone implant from a bone.
  • the present invention relates to a system and method for coating a bone implant with soluble or biodegradable layers and biocompatible layers that prevent direct tissue contact with a tissue facing surface of the bone implant.
  • An exemplary coating according to the present invention may be carried out by a variety of techniques, including dip or spray coating and physical or chemical vapor deposition (PVD/CVD). This results in a biocompatible “shield” formed directly over the tissue contacting surface providing favorable healing around the implant but which is more easily detached after a predefined time in vivo, liberating the implant from surrounding tissue and allowing for a less invasive and damaging removal process.
  • An outer biocompatible layer formed over the first shield is subsequently resorbed on a longer timescale, its total volume and material properties being selected to render insignificant any adverse effect when implanted in vivo.
  • the present invention relates to an implant with a substrate material comprising a metal or metal alloy coated with a first layer having a thickness D comprising a material which is water-soluble or degradable in body fluids and a second layer having a thickness d ⁇ D placed over the first layer comprising a biocompatible material.
  • This implant provides a self-detaching coating on a metallic implant substrate, shielding the implant from bone on-growth or ingrowth without hindering the healing process. This allows for an easy removal of the implant after it has fulfilled its temporary function in the body.
  • the second layer comprises a bioresorbable or bio-dissolving material.
  • the second layer has a minimum thickness d of 1 nm, preferably of 10 nm. With a thickness of 10 nm the second layer acts as effective barrier to cell through-growth to reduce or block the relevant diffusion mechanism.
  • the second layer has a maximum thickness d of 100 nm.
  • the second layer has a resorption/dissolution rate which is smaller than that of the first layer.
  • the time required for the resorption/dissolution of the second layer is in the range of 2 weeks to 3 months.
  • the first layer is made of a resorbable material.
  • Preferred materials are polylactides (PLA) and Calciumphosphates (CaP). This configuration allows a cell through-growth which might lead to a weakened “cell-second layer-cell” structure that easily breaks upon removal of the bulk implant. After the first layer has dissolved/been resorbed, the second layer will be resorbed on a longer timescale.
  • the thickness D of the first layer is at least 10 ⁇ m, preferably at least 100 ⁇ m.
  • the thickness D of the first layer is at most 1000 ⁇ m, preferably at most 500 ⁇ m.
  • the ratio of D/d is in the range of 10,000:1 and 1,000:1.
  • the first layer comprises polyvinyl alcohol (PVA) or a polylactide.
  • the second layer comprises a non-resorbable metal, preferably titanium or a titanium alloy and has a thickness d of maximum 100 nm.
  • the second layer comprises hydroxyapatite and has a thickness d of maximum 10 ⁇ m.
  • a third layer comprising a mixture of the materials of the first and second layers is interposed between the first layer and the second layer.
  • a further layer is applied on the second layer and on this further layer another layer comprising a biocompatible material is applied.
  • the further layer comprises a material which is water-soluble or degradable in body fluids.
  • the number of alternating layers comprising a material which is water-soluble or degradable in body fluids and a biocompatible material is 2 x, wherein x is 3 or larger.
  • the material of the first layer is different from the material of the second layer.
  • a method for manufacturing of the implant comprises the steps of applying a material which is water-soluble or degradable in body fluids to a substrate comprising a metal or metal alloy to form a first layer on the substrate and applying a biocompatible material on the first layer.
  • a mixture of the materials used in steps A and B is applied to the first layer before performing step B.
  • the application of the layers is made by dip coating or spray coating.
  • FIG. 1 illustrates a cross-section of a first exemplary embodiment of the implant according to the present invention
  • FIG. 2 illustrates a cross-section of another exemplary embodiment of the implant according to the present invention.
  • FIG. 3 illustrates a cross-section of a further exemplary embodiment of the implant according to the present invention.
  • the present invention relates to a coated bone implant for the fixation of a fractured or otherwise damaged or weakened bone and a method of producing such a bone implant.
  • Embodiments of the present invention may be used for orthopaedic fixation, cranio-maxillofacial fixation or for the fixation of any other bone in a living body requiring short or long-term implantation of a bone implant.
  • a bone plate according to an exemplary embodiment of the invention is coated with one or more layers of materials selected to prevent the bone plate from becoming integrated with tissue surrounding the bone implant during short or long-term implantation in vivo.
  • One of more of the layers of material in the exemplary bone plate may be formed of resorbable materials exhibiting desired characteristics (e.g., resorption rate, biocompatibility, etc.). It is noted that although embodiments of the present invention are described with particular layer thickness and configurations and described in regard to the fixation of specific bones, any other thickness or configurations may be employed in the fixation of any bone without deviating from the spirit and scope of the invention. Furthermore, although embodiments of the present invention depict the deposition of layers on only one surface of a bone implant, any or all surfaces of the bone implant may be coated with the exemplary layers without deviating from the spirit and scope of the invention.
  • an implant 10 includes an implant body 12 (e.g., a bone plate or intramedullary nail) including a substrate material 1 .
  • a first surface 14 of the implant body 12 is coated with a first layer 2 with a second layer 3 extending over the first layer 2 so that the second layer 3 forms an outer surface of the implant 10 which, when implanted, forms a contact layer with the surrounding tissue.
  • the substrate material 1 of the implant 10 may be any suitable metal, metal alloy, or polymer.
  • the substrate material 1 is titanium (Ti), a Ti alloy such as TiAl 6 Nb 7 (“TAN”), steel or PEEK, as those skilled in the art will understand.
  • the first layer 2 has a thickness D and includes a resorbable material comprising polyvinyl alcohol (PVA) or a polylactide.
  • the thickness D of the first layer 2 can range from approximately 10 ⁇ m to 1000 ⁇ m, and in an exemplary embodiment may be between approximately 100 ⁇ m and 500 ⁇ m.
  • the second layer 3 has a thickness d and includes a biocompatible material which can be one of a bioresorbable or bio-dissolving material as well a non-resorbable or a non-dissolving material.
  • the second layer 3 comprises a non-resorbable metal, e.g. titanium or a titanium alloy and/or a hydroxyapatite.
  • the thickness d of the second layer 3 is smaller than the thickness D of the first layer 2 and can range from 1 nm to 100 nm and, in a preferred embodiment, has a maximum thickness d of 10 ⁇ m. Further, the resorption/dissolution time for the second layer 3 is longer than that of the first layer 2 and ranges from 2 weeks to 3 months.
  • the biocompatible layer system formed by the first and second layers 2 , 3 allows a favorable healing around the implant 10 as well as a less invasive and damaging procedure for removing the implant 10 due to the fact that at least the first layer 2 detaches from the implant body 12 after a predetermined time in vivo.
  • FIG. 2 another embodiment of the implant is illustrated which differs from the embodiment of FIG. 1 only in that an intermediate layer 4 is formed between the first and second layers 2 , 3 of an implant 10 ′.
  • the third layer 4 comprises a mixture of the materials of the first and second layer 2 , 3 .
  • an implant body 12 ′ consisting of the substrate material 1 and having the form of a bone plate or an intramedullary nail is coated with the first layer 2 having a thickness D.
  • the intermediate layer 4 is placed on the first layer 2 and has, for example, a thickness ⁇ I smaller than the thickness D of the first layer 2 and larger than the thickness d of the second layer 3 forming the contact layer with surrounding tissue.
  • FIG. 3 Another embodiment of the implant is illustrated in FIG. 3 which differs from the embodiment of FIG. 1 only in that a third layer 21 is formed over the second layer 3 .
  • the third layer 21 includes a material that is water-soluble or degradable in body fluids.
  • a fourth layer 31 formed over the third layer 21 includes a biocompatible material.
  • an implant 10 ′′ having an implant body 12 ′′ consisting of the substrate material 1 formed as a bone plate or intramedullary nail is coated with the first layer 2 having the thickness D and the second layer 3 having the thickness d is placed on the first layer 2 .
  • the third layer 21 is placed on the second layer 3 and has a thickness ⁇ F which may, for example, have a thickness equal to the thickness D of the first layer 2 while the fourth and outermost layer 31 has a thickness ⁇ A which may be, for example, equal to the thickness d of the second layer 3 .
  • the fourth layer 31 forms the contact layer with surrounding tissue.
  • a bone plate commonly used for fracture fixation in combination with bone screws is used.
  • the typical duration of in-vivo use of such bone plates ranges from a few weeks to a few months, after which they are often removed.
  • the bone plates are typically fabricated from a TAN alloy or steel, but also can be made from plastics like PEEK.
  • exemplary bone plates according to the present invention may also be implanted indefinitely if so desired without deviating from the spirit and scope of the present invention.
  • a TAN bone plate is first cleaned by immersion in a 50/50 percentage by volume mixture of ethanol and acetone and subsequently placed into an ultrasonic bath for approximately five minutes.
  • the implant is cleaned in a dry CO 2 gas jet.
  • the implant is then coated with a water-soluble first layer 2 of polyvinyl alcohol (PVA) by dip coating in a PVA/water solution with a removal speed of XX mm/s, resulting in a PVA layer XX micrometers strong after drying, wherein, as those skilled in the art will understand, the removal speed is directly related to the resulting PVA layer strength.
  • PVA polyvinyl alcohol
  • the removal speed may be 1 mm/s, resulting in a PVA layer of approximately 50 micrometers.
  • the bone plate is then inserted into a vacuum system applying a pressure smaller than 1e-4 mbar.
  • a 10 nm titanium oxide film is then deposited over the PVA layer by, for example, reactive magnetron sputtering with a working pressure of 5e-3 mbar in a mixture of 90% Ar and 10% O 2 .
  • the resulting second layer 3 is biocompatible and delays the water dissolution of the previously deposited PVA layer.
  • the coated bone implant 10 is then removed from the vacuum chamber and packed in dry air or a vacuum.
  • the first PVA layer 2 will detach in vivo after approximately one month, thus freeing the bone implant for removal following the removal of bone screws therefrom.
  • the exemplary layering according to the present invention may also be carried out on Kirschner wires or intramedullary nails without deviating from the spirit and scope of the present invention.
  • the Kirchner wire may be coated in substantially the same manner as discussed above, with a dip coating followed by a thermal evaporation process. If an intramedullary nail is used, the nail may be spray coated with a 100 ⁇ m thick biodegradable layer.
  • the biodegradable layer may then be coated with a hydroxyapatite layer.
  • a hydroxyapatite layer Upon dissolution of the biodegradable layer (i.e., after implantation in vivo for a predetermined period of time), sufficient space remains between the intramedullary nail and the hydroxyapatite layer to permit removal of the intramedullary nail while still preventing an ingrowth of weak tissue therearound.
  • any of the biodegradable layers of the present invention may be replaced by a melting interlayer, which may, for example, dissolve into surrounding tissue after reaching a predetermined temperature in the body (e.g. resting body temperature).
  • a predetermined temperature in the body e.g. resting body temperature
  • bone implants requiring only short-term implantation may be provided with lubrication to prevent or reduce tissue growth thereover.
  • the scope of the present application is not intended to be limited to the particular embodiments of the process, machine, manufacture, composition of matter, means, methods and steps described in the specification.

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  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Orthopedic Medicine & Surgery (AREA)
  • Veterinary Medicine (AREA)
  • Public Health (AREA)
  • General Health & Medical Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • Surgery (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Transplantation (AREA)
  • Chemical & Material Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Biomedical Technology (AREA)
  • Dermatology (AREA)
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  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Neurology (AREA)
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  • Molecular Biology (AREA)
  • Cardiology (AREA)
  • Vascular Medicine (AREA)
  • Inorganic Chemistry (AREA)
  • Manufacturing & Machinery (AREA)
  • Materials For Medical Uses (AREA)
  • Prostheses (AREA)
  • Surgical Instruments (AREA)
US13/177,179 2010-07-09 2011-07-06 Self-Detaching Layer for Easy Implant Removal Abandoned US20120172997A1 (en)

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US11998192B2 (en) 2022-04-12 2024-06-04 Cilag Gmbh International Adaptive control of surgical stapling instrument based on staple cartridge type

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WO2016159493A1 (ko) * 2015-03-31 2016-10-06 (주)웹스 생분해성 임플란트 구조체

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US10166105B2 (en) 2019-01-01
BR112012033415A2 (pt) 2016-11-29
US20160354208A1 (en) 2016-12-08
JP2013535239A (ja) 2013-09-12
EP2590596A1 (en) 2013-05-15
TWI519326B (zh) 2016-02-01
WO2012006334A1 (en) 2012-01-12
EP2590596B1 (en) 2015-08-26
JP5873490B2 (ja) 2016-03-01
CN105749345B (zh) 2019-10-25
CN105749345A (zh) 2016-07-13
KR20180008937A (ko) 2018-01-24
CA2803262C (en) 2018-09-11
JP6199419B2 (ja) 2017-09-20
KR101882667B1 (ko) 2018-07-30
KR20130139831A (ko) 2013-12-23
EP2982343A1 (en) 2016-02-10
JP2016105789A (ja) 2016-06-16
CA2803262A1 (en) 2012-01-12
KR101826590B1 (ko) 2018-02-07
TW201206509A (en) 2012-02-16

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