WO2015082023A1 - Procédé pour fabriquer une augmentation osseuse implantable - Google Patents

Procédé pour fabriquer une augmentation osseuse implantable Download PDF

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Publication number
WO2015082023A1
WO2015082023A1 PCT/EP2013/075857 EP2013075857W WO2015082023A1 WO 2015082023 A1 WO2015082023 A1 WO 2015082023A1 EP 2013075857 W EP2013075857 W EP 2013075857W WO 2015082023 A1 WO2015082023 A1 WO 2015082023A1
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WO
WIPO (PCT)
Prior art keywords
bone
model
augment
interconnection points
beams
Prior art date
Application number
PCT/EP2013/075857
Other languages
English (en)
Inventor
Jan DEMOL
Bram LENAERTS
Jan Schrooten
Ana SOARES
Hans Pol Sus VAN OOSTERWYCK
Original Assignee
Mobelife N.V.
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Mobelife N.V. filed Critical Mobelife N.V.
Priority to PCT/EP2013/075857 priority Critical patent/WO2015082023A1/fr
Publication of WO2015082023A1 publication Critical patent/WO2015082023A1/fr

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Classifications

    • 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
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/28—Bones
    • 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
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/30—Joints
    • A61F2/3094—Designing or manufacturing processes
    • A61F2/30942—Designing or manufacturing processes for designing or making customized prostheses, e.g. using templates, CT or NMR scans, finite-element analysis or CAD-CAM techniques
    • 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
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/28—Bones
    • A61F2002/2835—Bone graft implants for filling a bony defect or an endoprosthesis cavity, e.g. by synthetic material or biological material
    • 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
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/30—Joints
    • A61F2/30767—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth
    • A61F2002/3092—Special external or bone-contacting surface, e.g. coating for improving bone ingrowth having an open-celled or open-pored structure
    • 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
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/30—Joints
    • A61F2/3094—Designing or manufacturing processes
    • A61F2/30942—Designing or manufacturing processes for designing or making customized prostheses, e.g. using templates, CT or NMR scans, finite-element analysis or CAD-CAM techniques
    • A61F2002/30952—Designing or manufacturing processes for designing or making customized prostheses, e.g. using templates, CT or NMR scans, finite-element analysis or CAD-CAM techniques using CAD-CAM techniques or NC-techniques
    • 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
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/30—Joints
    • A61F2/3094—Designing or manufacturing processes
    • A61F2/30942—Designing or manufacturing processes for designing or making customized prostheses, e.g. using templates, CT or NMR scans, finite-element analysis or CAD-CAM techniques
    • A61F2002/30955—Designing or manufacturing processes for designing or making customized prostheses, e.g. using templates, CT or NMR scans, finite-element analysis or CAD-CAM techniques using finite-element analysis
    • 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
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/30—Joints
    • A61F2/3094—Designing or manufacturing processes
    • A61F2/30942—Designing or manufacturing processes for designing or making customized prostheses, e.g. using templates, CT or NMR scans, finite-element analysis or CAD-CAM techniques
    • A61F2002/30962—Designing or manufacturing processes for designing or making customized prostheses, e.g. using templates, CT or NMR scans, finite-element analysis or CAD-CAM techniques using stereolithography

Definitions

  • the present invention relates to a method for manufacturing an implantable bone augment.
  • the invention further relates to an augment obtainable by the method according to the invention.
  • the present invention relates to support structures and methods for making support structures or components which can be used to fill defects in bone. These methods are based on imaging information of the bone defect and its mechanical environment.
  • the support structures can then be tailored such that they have optimal biological and mechanical properties that may enhance bone ingrowth and have the desired shape to repair the defective object.
  • alloplastic (e.g. metal) bone augments typically have a standardized shape and are designed as an assembly of unit cells resulting in a porous homogeneous structure.
  • these unit cells are typically cut off to form a bone contacting surface which is as complementary as possible to a corresponding surface of the bone, in particular a surface of the bone defect.
  • cut-off elements i.e. the partial unit cells
  • the boundary of the augment form an irregular surface which may compromise the augment structural integration in the surrounding bone. This is due to geometrical irregularities, for instance resulting in a pore size at the boundary which is less optimal for bone ingrowth, and mechanical irregularities, for instance leading to loading conditions less optimal for bone ingrowth. It is therefore a goal, among other goals, of the present invention to provide an improved, efficient and/or reliable method for manufacturing an implantable bone augment.
  • This goal is met by a method for manufacturing an implantable bone augment according to appended claims 1. More specifically, this goal, among other goals, is met by a method for manufacturing an implantable bone augment arranged to at least partially fit in a bone defect in a bone of a patient, wherein the method comprises the steps of:
  • said augment model is a beam network model formed by a plurality of beams interconnected at interconnection points, wherein a plurality of interconnection points on an outer surface of the beam network model define a bone contacting surface arranged for contacting a corresponding outer surface of the bone, in particular a surface of the bone defect, and wherein the interconnection points on said bone contacting surface are positioned such that the bone contacting surface is formed complementary to the corresponding outer surface of the bone;
  • the implant augment is designed as a beam network and is at least at the bone contacting surface formed of interconnected beams.
  • the bone contact surface therefore does not contain any cut-off elements, i.e. partial lengths of beams which are not interconnected at an interconnection point or node at the bone contacting surface.
  • the beam network at least at the bone contacting surface, follows the defect boundary. In other words, a plurality of interconnection points on the outside of said network define the bone contacting surface.
  • the formation of the beam network according to the invention is preferably done using meshing techniques, for instance using mesh elements having a predetermined size.
  • a meshing technique then creates a network of beams within the outer surfaces, at least a part of which is based on the bone model for forming the bone contacting surface.
  • the bone contacting surface of the augment is arranged to be in contact with a corresponding surface of the bone, in particular a surface of the defect.
  • the bone contacting surface is hereto formed complementary to the corresponding surface. Complementary in this respect means that the two surfaces in inserted state extend adjacently without any substantial play, or at least with minimal play.
  • a model based on a beam network is advantageously since such a model allows relatively easy analysis of the mechanical conditions in use, for instance using the Finite Elements Method.
  • the beam theory is applied to numerically analyze the mechanical characteristics.
  • Modelling for instance by numerical analysis, of the mechanical environment with a bone contacting surface having cut-off elements is difficult, such that it is hard to predict the mechanical conditions in implanted state.
  • the numerical analysis of the beam network model according to the invention is therefore more accurate, such that the mechanical environment of the augment according to the invention and the surrounding bone can be reliably predicted.
  • the combined model of the augment and the bone is therefore numerically analyzed to characterize and optimize the structure by adjusting the beam network to achieve a mechanical environment with as little as possible peaks, for instance in terms of local peaks of stresses and strains throughout the beam network. Local peaks in the loading conditions may result in poor bone ingrowth or even in bone resorption due to stress shielding. It is to be understood that a variation in stresses and strains throughout the augment in use cannot be prevented.
  • the optimization process is preferably arranged to optimize the beam network to achieve an as natural distribution of the loading conditions throughout the beam network as possible.
  • the step of providing the three-dimensional model of the bone comprises the step of obtaining an image of the bone and defect therein.
  • Digital patient- specific image information can be provided by any suitable means known in the art, such as for example a computer tomography (CT) scanner, a magnetic resonance imaging (MRI) scanner, an ultrasound scanner, or a combination of Roentgenograms.
  • CT computer tomography
  • MRI magnetic resonance imaging
  • ultrasound scanner or a combination of Roentgenograms.
  • the step of obtaining an image of the bone and the defect therein may for example comprise the steps of obtaining 2D datasets of the bone and reconstructing a 3D virtual bone model from said 2D datasets.
  • the first step in a planning is the construction of a 3D virtual model of the bone.
  • This reconstruction starts with sending a patient to a radiologist for scanning, e.g. for a scan that generates medical volumetric data, such as a CT, MRI scan or the like.
  • the output of the scan can be a stack of two-dimensional (2D) slices forming a 3D data set.
  • the output of the scan can be digitally imported into a computer program and may be converted using algorithms known in the field of image processing technology to produce a 3D computer model of a relevant bone.
  • a virtual 3D model is constructed from the dataset using a computer program such as Mimics(TM) as supplied by Materialise N.V., Leuven, Belgium.
  • Computer algorithm parameters are based on accuracy studies, as for instance described by Gelaude at al. (2008; Accuracy assessment of CT-based outer surface femur meshes Comput. Aided Surg. 13(4): 188- 199).
  • a more detailed description for making a perfected model is disclosed in U.S. Patent No. 5,768, 134 entitled 'Method for making a perfected medical model on the basis of digital image information of a part of the body'.
  • the size and the shape of the augment can be designed based thereon as described above. Based on this bone model, at least the contours of the bone contacting surface of the augment is preferably determined. This surface is formed complementarily to the corresponding surface in the bone model.
  • each of the beams has a substantially equal predetermined length. This results in a regular geometry and ensures that an optimal pore size for bone ingrowth can be achieved at the bone contacting surface.
  • the interconnection points on said bone contacting surface are positioned at substantially equal mutual distances. As the pore size of the porous beam network model is particularly important at the bone-augment interface, it is preferred if these interconnection points are placed at predetermined optimal mutual distances for ensuring an optimal bone ingrowth.
  • each of the beams has a substantially equal predetermined initial diameter and wherein the step of optimizing the mechanical properties comprises adapting the diameters of the beams forming the beam network model. This results in a regular geometry and ensures that an optimal pore size for bone ingrowth can be achieved at the bone contacting surface.
  • the step of optimizing comprises optimizing the mechanical properties of said beam network model for minimizing the strains in the outer surface of the bone in contact with the bone contacting surface of the augment model. Peak strains at the bone-augment interface compromise the bone ingrowth at this interface.
  • the stresses and strains in the augment-bone interface are calculated and the geometry of the beam network is optimized, for instance by varying the diameter of the beams as mentioned above, for obtaining as little strains as possible in the bone contacting surface.
  • the bone contacting surface is defined by said interconnection points and the beams interconnecting said interconnecting points.
  • interconnection points or nodes on the bone contacting surface hereby extend substantially parallel to said surface and therefore form a smooth surface. This further reduces any peaks in local loading conditions, such that the bone ingrowth is even further enhanced.
  • the beams defining the bone contacting surface further improves the optimization process. Also the beams are hereby taken into account in the optimization process, such that an implantable augment can be designed and manufactured with as little strains in the bone-augment boundary as possible.
  • the interconnection points on the outer surface of the beam network model define the complete outer surface of the model. Cut-off elements at these outer surfaces are then also prevented, which further allows easier numerically analyzing the model. It is again preferred if the outer surface is further defined by the beams interconnecting said interconnecting points on the outer surface.
  • the step of generating the three-dimensional augment model comprises:
  • the bone contacting surface is first defined by the plurality of interconnection points or nodes of the beam model to be able to form a surface being as complementary to the bone surface as possible.
  • this surface has been defined by these points, which are preferably arranged at substantially equal mutual distances for enhancing bone ingrowth as mentioned above
  • the remainder of the model is formed using a meshing technique. Forming the remainder of the model hereby means that the a three-dimensional beam network is formed having an outer contour corresponding to the earlier generated outer surface of the three- dimensional augment model.
  • the remainder of the interconnection points are hereto provided at preferably substantially equal distances for creating a beam network having a regular geometry. This beam network can then subsequently be optimized as described above.
  • the beam network consists of a plurality of polyhedrons, such as tetrahedrons and/or hexahedrons. Meshing techniques using for instance tetrahedrons as such are known and allow an efficient formation of a model with a predetermined outer shape, in particular the formation of a bone contacting surface which is accurately formed in
  • the beam network model contains only whole polyhedrons, such as tetrahedrons or hexahedrons to prevent the formation of cut-off elements.
  • the invention comprises the following steps:
  • the step of manufacturing preferably comprises using a three-dimensional printing technique, also referred to as rapid manufacturing technique, layered manufacturing technique, additive manufacturing technique or material deposition manufacturing technique.
  • Rapid manufacturing includes all techniques whereby an object is built layer by layer or point per point by adding or hardening material (also called free-form manufacturing).
  • the best known techniques of this type are stereolithography and related techniques, whereby for example a basin with liquid synthetic material is selectively cured layer by layer by means of a computer-controlled electromagnetic beam; selective laser sintering, whereby powder particles are sintered by means of an electromagnetic beam or are welded together according to a specific pattern; fused deposition modelling, whereby a synthetic material is fused and is stacked according to a line pattern;
  • Rapid Prototyping and Manufacturing techniques, are used for manufacturing the augment of the invention. Rapid Prototyping and Manufacturing (RP&M) can be defined as a group of techniques used to quickly fabricate a physical model of an object typically using three-dimensional (3-D) computer aided design (CAD) data of the object.
  • CAD computer aided design
  • Rapid Prototyping techniques including stereo lithography (SLA), Selective Laser Sintering (SLS), Fused Deposition Modeling (FDM), foil-based techniques, etc.
  • SLA stereo lithography
  • SLS Selective Laser Sintering
  • FDM Fused Deposition Modeling
  • foil-based techniques etc.
  • SLA stereo lithography
  • SLS Selective Laser Sintering
  • FDM Fused Deposition Modeling
  • foil-based techniques etc.
  • objects are typically built layer by layer.
  • Stereo lithography utilizes a vat of liquid photopolymer "resin" to build an object a layer at a time.
  • an electromagnetic ray e.g. one or several laser beams which are computer-controlled, traces a specific pattern on the surface of the liquid resin that is defined by the two- dimensional cross-sections of the object to be formed. Exposure to the electromagnetic ray cures, or, solidifies the pattern traced on the resin and adheres it to the layer below. After a coat had been polymerized, the platform descends by a single layer thickness and a subsequent layer pattern is traced, adhering to the previous layer. A complete 3-D object is formed by this process.
  • Selective laser sintering uses a high power laser or another focused heat source to sinter or weld small particles of plastic, metal, or ceramic powders into a mass representing the 3- dimensional object to be formed.
  • FDM Fused deposition modeling
  • Foil-based techniques fix coats to one another by means of gluing or photo polymerization or other techniques and cut the object from these coats or polymerize the object.
  • a technique is described in U.S. Pat. No. 5.192.539.
  • RP&M techniques start from a digital representation of the 3-D object to be formed, in this case the design of the augment.
  • the digital representation is sliced into a series of cross-sectional layers which can be overlaid to form the object as a whole.
  • the RP&M apparatus uses this data for building the object on a layer-by-layer basis.
  • the cross-sectional data representing the layer data of the 3-D object may be generated using a computer system and computer aided design and manufacturing (CAD/CAM) software.
  • CAD/CAM computer aided design and manufacturing
  • the implantable augment of the invention may be manufactured in different materials. Typically, only materials that are biocompatible (e.g. USP class VI compatible) with the human body are taken into account.
  • the augment is formed from a heat-tolerable material allowing it to tolerate high-temperature sterilization.
  • the surgical template may be fabricated from a polyamide such as PA 2200 as supplied by EOS, Kunststoff, Germany or any other material known by those skilled in the art may also be used.
  • the invention further relates to an implantable bone augment arranged to at least partially fit in a bone defect in a bone of a patient, wherein the augment comprises a body formed of a beam network which is formed by a plurality of beams interconnected at interconnection points, wherein a plurality of interconnection points on an outer surface of the beam network define a bone contacting surface arranged for contacting a corresponding outer surface of the bone, in particular a surface of the bone defect, and wherein the interconnection points on said bone contacting surface are positioned at substantially equal mutual distances and such that the bone contacting surface is formed complementary to the corresponding outer surface of the bone, wherein the diameters of said beams in the network are adapted for minimizing the strains in the bone contacting surface of the augment model.
  • each of the beams has a substantially equal length and the beam network preferably consists of a plurality of polyhedrons, such as tetrahedrons and/or hexahedrons.
  • Figure la schematically shows a boundary of an augment according to the prior art
  • Figure lb schematically shows a boundary of an augment according to the invention
  • Figure 2 schematically shows the process of creating the initial beam network model of the augment
  • FIG 3 schematically shows the result of the optimization process.
  • an augment 1 according to the prior art is shown.
  • the body of the augment 2 comprises a porous structure having beams 10 which are interconnected at interconnection points 11.
  • the outer surface 2, which is arranged to be in contact with the bone, is either defined by the cut off beams 10a extending at thus outer surface or by interconnection points 11a which happen to be at the outer surface 2.
  • the surface 2 is formed by simply cutting through the structure to create an outer surface which corresponds to the surface of the bone for which the augment 1 is intended. This cutting results in the cut-off elements 10a which compromise bone ingrowth.
  • an outer surface 2 of the augment 1 is defined by outer interconnection points 11a which are interconnected with outer beams 10a.
  • the inner structure of the augment is formed by corresponding beams 10 connected at interconnection points 11 to form a beam network.
  • the outer surface 2 is therefore smooth and does not contain cut-off elements such as in the augment according to the prior art.
  • the beams 10, 10a and interconnection points 11, 11a form tetrahedrons.
  • interconnection points 11a are subsequently placed on this outer surface 2, wherein the mutual distances between the points 11a are substantially the same. This ensures an optimal pore size at the boundary for bone ingrowth.
  • the remainder of the model for instance the inner structure thereof, can be defined using a meshing technique.
  • the resulting beam network is shown in the middle figure of figure 2.
  • the design of the model can then be manufactured using a three-dimensional printing, as shown in the right.
  • the structure of the beam network is however optimized to minimize peak loads in the structure, in particular at the surface 2 intended to contact the bone.
  • a combined Finite Element Method model of the augment, as seen in the middle of figure 2, in combination with the surrounding bone is made.
  • boundary conditions which mimic typical loading conditions of the bone, the mechanical environment in the augment in implanted state can be calculated.

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  • Health & Medical Sciences (AREA)
  • Engineering & Computer Science (AREA)
  • Vascular Medicine (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Transplantation (AREA)
  • Cardiology (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Orthopedic Medicine & Surgery (AREA)
  • Oral & Maxillofacial Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Physics & Mathematics (AREA)
  • Geometry (AREA)
  • Manufacturing & Machinery (AREA)
  • Prostheses (AREA)

Abstract

L'invention concerne un procédé pour fabriquer une augmentation osseuse implantable disposée au moins partiellement dans un défaut osseux d'un os d'un patient, le procédé comprenant les étapes consistant à : – fournir un modèle d'os tridimensionnel d'au moins une partie de l'os du patient comprenant le défaut osseux ; – générer un modèle d'augmentation tridimensionnel basé sur le modèle d'os de telle sorte que le modèle d'augmentation correspond au moins partiellement audit défaut, ledit modèle d'augmentation étant un modèle de réseau de faisceaux formé par une pluralité de faisceaux reliés entre eux au niveau de points de liaison, une pluralité de points de liaison sur une surface extérieure du modèle de réseau de faisceaux définissant une surface de contact d'os conçue pour entrer en contact avec une surface extérieure correspondante de l'os, en particulier une surface du défaut osseux, et les points de liaison sur ladite surface de contact d'os étant positionnés de telle sorte que la surface de contact d'os est formée de façon complémentaire à la surface extérieure correspondante de l'os ; – générer un modèle numérique combiné du modèle d'os et du modèle d'augmentation pour analyser numériquement les conditions de chargement dans ledit modèle combiné ; – analyser de façon itérative et numérique ledit modèle combiné, et optimiser les propriétés mécaniques dudit modèle de réseau de faisceaux pour réduire à un minimum des pics locaux dans les conditions de chargement ; et – fabriquer le modèle d'augmentation optimisé.
PCT/EP2013/075857 2013-12-06 2013-12-06 Procédé pour fabriquer une augmentation osseuse implantable WO2015082023A1 (fr)

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Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
ITUA20164134A1 (it) * 2016-05-18 2017-11-18 Francesco Naddeo Metodologia per la realizzazione ottimizzata rispetto ai carichi di scaffold tissutali
EP3422220A1 (fr) * 2017-06-27 2019-01-02 Ceské vysoké ucení technické v Praze Procede d'optimisation de l'arrangement et de l'orientation des fibres dans le beton a ultra-hautes performances
CN109172049A (zh) * 2018-09-13 2019-01-11 浙江工业大学 一种基于分层片状杆连接的多孔网状结构骨科修复植入体的设计制作方法及植入体
WO2020181296A3 (fr) * 2019-03-07 2020-10-22 Nexus Spine, LLC Procédés de développement d'implants poreux de propriétés optimales

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WO2020181296A3 (fr) * 2019-03-07 2020-10-22 Nexus Spine, LLC Procédés de développement d'implants poreux de propriétés optimales

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