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WO2004022118A1 - Élément de matière biologique - Google Patents

Élément de matière biologique Download PDF

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Publication number
WO2004022118A1
WO2004022118A1 PCT/JP2003/011263 JP0311263W WO2004022118A1 WO 2004022118 A1 WO2004022118 A1 WO 2004022118A1 JP 0311263 W JP0311263 W JP 0311263W WO 2004022118 A1 WO2004022118 A1 WO 2004022118A1
Authority
WO
WIPO (PCT)
Prior art keywords
bone
amorphous alloy
biomaterial
modulus
potential
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Ceased
Application number
PCT/JP2003/011263
Other languages
English (en)
Japanese (ja)
Inventor
Kozo Nakamua
Isao Ohnishi
Takao Hanawa
Sachiko Hiromoto
Norio Maruyama
Toshio Arai
Hitoshi Ofune
Mamoru Ishida
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.)
National Institute for Materials Science
YKK Corp
Original Assignee
National Institute for Materials Science
YKK Corp
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 National Institute for Materials Science, YKK Corp filed Critical National Institute for Materials Science
Priority to AU2003261912A priority Critical patent/AU2003261912A1/en
Publication of WO2004022118A1 publication Critical patent/WO2004022118A1/fr
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

Links

Classifications

    • 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
    • A61L31/00—Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
    • A61L31/02—Inorganic materials
    • A61L31/022—Metals or alloys
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods
    • A61B17/56—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor
    • A61B17/58—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor for osteosynthesis, e.g. bone plates, screws or setting implements
    • A61B17/68—Internal fixation devices, including fasteners and spinal fixators, even if a part thereof projects from the skin
    • A61B17/84—Fasteners therefor or fasteners being internal fixation devices
    • A61B17/86—Pins or screws or threaded wires; nuts therefor
    • A61B17/866—Material or manufacture
    • 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
    • A61L31/00—Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
    • A61L31/14—Materials characterised by their function or physical properties, e.g. injectable or lubricating compositions, shape-memory materials, surface modified materials
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods
    • A61B17/56—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor
    • A61B17/58—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor for osteosynthesis, e.g. bone plates, screws or setting implements
    • A61B17/68—Internal fixation devices, including fasteners and spinal fixators, even if a part thereof projects from the skin
    • A61B17/72—Intramedullary devices, e.g. pins or nails
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods
    • A61B17/56—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor
    • A61B17/58—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor for osteosynthesis, e.g. bone plates, screws or setting implements
    • A61B17/68—Internal fixation devices, including fasteners and spinal fixators, even if a part thereof projects from the skin
    • A61B17/74—Devices for the head or neck or trochanter of the femur
    • A61B17/742—Devices for the head or neck or trochanter of the femur having one or more longitudinal elements oriented along or parallel to the axis of the neck
    • A61B17/744—Devices for the head or neck or trochanter of the femur having one or more longitudinal elements oriented along or parallel to the axis of the neck the longitudinal elements coupled to an intramedullary nail
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B17/00—Surgical instruments, devices or methods
    • A61B17/56—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor
    • A61B17/58—Surgical instruments or methods for treatment of bones or joints; Devices specially adapted therefor for osteosynthesis, e.g. bone plates, screws or setting implements
    • A61B17/68—Internal fixation devices, including fasteners and spinal fixators, even if a part thereof projects from the skin
    • A61B17/80—Cortical plates, i.e. bone plates; Instruments for holding or positioning cortical plates, or for compressing bones attached to cortical plates
    • 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 invention relates to a biomaterial made of an amorphous alloy (metallic glass), and more particularly, to an orthopedic spinal fixation material such as an intramedullary nail or an osteosynthesis plate, a fracture fixation material, an artificial joint, or an intervertebral joint.
  • the present invention relates to a biological material member useful for dental crowns, inlays, crowns, artificial beds, artificial dental roots, orthodontic wires, etc., and surgical instruments for general surgery. Background art
  • the requirements for medical materials include non-toxicity, non-carcinogenicity, non-allergenicity, suitability for living tissues, and biocompatibility for safety, as well as medical functionality for enhancing medical effects. And the like.
  • Medical functionality includes mechanical properties (mechanical strength, fatigue resistance, wear resistance) and chemical properties (corrosion resistance, biofluid corrosion resistance).
  • a Co_Cr-based alloy, stainless steel, or a titanium alloy has been conventionally used, and various titanium alloys have been proposed. (See, for example, JP-A-58-124244).
  • stainless steel SUS316L and Ni-Ti alloys contain Ni and are a source of allergy.
  • titanium alloys have also caused allergies, and the use of stainless steel or titanium alloys is not always optimal for living organisms.
  • titanium alloy is used for intramedullary nails, etc.
  • stress shield problem problem of load cut-off
  • the present invention has been made in view of the above-mentioned circumstances, and has as its object the purpose of not including Ni as an allergic source, having excellent corrosion resistance to biological fluids, high strength, and low elastic modulus.
  • Another object of the present invention is to provide a biomaterial member that is difficult to react with a living body, is easy to remove after treatment, and hardly causes problems such as stress shield and pulmonary infarction when used as an intramedullary nail or the like. Disclosure of the invention
  • a polarization resistance in a degassed Hanks solution is 4 ⁇ 10 6 ⁇ cm 2 or more, and an immersion potential-pitting potential window is 0.25 V or more.
  • a biomaterial member comprising an amorphous alloy of the above is provided.
  • the biomaterial is made of an amorphous alloy having a Young's modulus of 10 OGPa or less.
  • the biomaterial member of the present invention does not contain Ni as an allergic source, has excellent corrosion resistance to biological fluids, has high strength and a low elastic modulus, is difficult to react with a living body, and is removed after the treatment. When used as an intramedullary nail or the like, problems such as so-called stress shielding and pulmonary infarction are unlikely to occur.
  • the biomaterial member may be an amorphous alloy having a polarization resistance in a degassed Hanks solution of 4 ⁇ 10 6 ⁇ cm 2 or more, and an immersion potential-pitting potential window of 0.25 V or more. Since it is preferably made of an amorphous alloy having a Young's modulus of 100 GPa or less, it has excellent in vivo corrosion resistance, excellent specific strength, low Young's modulus, and physical properties closer to bone. . For this reason, a smaller osteosynthesis material with the same strength can be manufactured, and it is less susceptible to stress shields, which is advantageous for bone fusion, and a conventional thick intramedullary nail is inserted into the bone marrow.
  • the fat that overflows from the bone marrow mixes into the blood, thereby forming a blood clot in the lungs, which makes it easier to cause pulmonary infarction.
  • the effect of reducing the increase in intramedullary pressure can be obtained.
  • the space occupation in the bone marrow can be minimized, blood vessels in the bone marrow can be preserved to a maximum extent, and bone formation in the bone marrow is hardly inhibited.
  • the most preferable application mode of the biomaterial member of the present invention is at least one of an intramedullary nail for orthopedic surgery, a osteosynthesis plate, a locking nail, and a bone fixing screw.
  • Figure 1 is a schematic diagram of order to explain the method for obtaining the polarization resistance R p from the polarization curve of the corrosion potential neighbors.
  • FIG. 3 is a schematic partial cross-sectional front view showing an embodiment in which the biomaterial made of the amorphous alloy of the present invention is applied to an intramedullary nail.
  • FIG. 4 shows the application of the biomaterial made of the amorphous alloy of the present invention to an osteosynthesis plate. It is a schematic front view showing an embodiment.
  • biomaterials used as intramedullary nails, osteosynthesis plates, etc. are not only non-toxic, non-allergic, but also suitable for blood, such as biocompatibility for safety, as well as mechanical properties ( Mechanical strength, fatigue resistance, and abrasion resistance) and chemical properties (corrosion resistance, corrosion resistance to biological fluids) are required.
  • polarization resistance is 4 x 1 0 6 ⁇ cm 2 or more, immersion potential - from the pitting potential window 0 2 5 V or more amorphous alloy, preferably a Young's modulus of 1 0 0 GP a less amorphous alloy.
  • the first feature of the biomaterial member of the present invention is that it is an amorphous alloy having a polarization resistance of 4 ⁇ 10 6 ⁇ cm 2 or more in a degassed Hanks solution.
  • metal material corrodes in a living body, metal ions are eluted and a corrosion product is formed.
  • the metallic material does not show toxicity such as allergy or carcinogenesis as it is, but in order to exhibit toxicity, it is eluted as metal ions by corrosion and binds to biomolecules in the form of ions or metal salts, or is similar to abrasion powder. It must be in a proper form.
  • the destruction of metallic materials in vivo is attributed to fatigue and fretting fatigue.However, these are not singly occurring, but are phenomena related to corrosion such as corrosion fatigue and fretting corrosion. .
  • the corrosion phenomena of metallic materials in the living environment is important from the viewpoint of the toxicity and durability of the material, and measurement for clarifying the corrosion phenomena in the living environment in vitro is required.
  • a degassed Hanks solution is used as a test solution, and an amorphous alloy having a polarization resistance of 4 ⁇ 10 6 ⁇ cm 2 or more is used.
  • the polarization resistance used for evaluating the corrosion reaction : p is the ratio of the current or voltage change obtained when a small voltage variation ⁇ ? 7 or a current variation ⁇ i is given. / ⁇ ; ⁇ ), and the corrosion potential E c of the polarization curve as shown in FIG.
  • the polarization resistance in the degassed Hanks solution is 4 ⁇ 10 6 ⁇ cm 2 or less.
  • the corrosion current density I increases as the polarization resistance Rp increases.
  • a second feature of the biomaterial member of the present invention is that the biomaterial member is an amorphous alloy having an immersion potential-pitting corrosion potential window of 0.25 V or more.
  • the immersion potential-pitting potential window is simply the potential difference between the pitting potential and the immersion potential on the anodic polarization curve, and indicates the allowable range of an environmental change that causes pitting.
  • the immersion potential is the potential of a metal when the metal is immersed in a solution and no action is applied from the outside.
  • an environmental change such as pH change of the solution
  • the immersion potential of the metal changes, and if the immersion potential after the environmental change becomes higher than the pitting potential, pitting occurs. Therefore, the larger the difference between the pitting potential and the immersion potential, the wider the allowable range for metal potential changes due to environmental changes.
  • the pitting corrosion resistance of the metal with respect to the environmental change is defined by an immersion potential-porosity potential window by a polarization test. Things.
  • the immersion potential-pitting potential window is specified to be 0.25 V or more for the following reason.
  • the immersion potential-pitting potential window is 0.25 V or more, preferably 0.3 V or more, it is determined that pitting does not occur even by environmental changes in the living body.
  • an amorphous alloy having an immersion potential-pitting potential window of 0.25 V or more is used. Since it is determined that pitting does not occur due to environmental changes, there is no point in setting the upper limit of the immersion potential-pitting potential window, and only the condition of 0.25 V or more has to be satisfied.
  • the biomaterial for orthopedic surgery of the present invention is made of an amorphous alloy satisfying a specific corrosion resistance condition. It also has the advantage of the above.
  • the characteristics of an amorphous alloy (metallic glass) vary depending on the combination of its constituent elements.
  • the structure has super fine transferability
  • the Young's modulus is important in the properties required for biomaterials for orthopedic surgery, especially for intramedullary nails, osteosynthesis materials, interlocking nails, and screws for bone fixation. Below, preferably 90 GPa or less is desirable. However, it is desirable to have a Young's modulus of about 20 GPa or more, which is close to that of bone.
  • the Young's modulus at the densest bone part in the living body is at most about 20 GPa, which is about 1/10 that of stainless steel.
  • the Young's modulus at the densest bone part in the living body is at most about 20 GPa, which is about 1/10 that of stainless steel.
  • calcium phosphate was observed on the surface of the titanium alloy after extraction and sulfide was observed on stainless steel, whereas no product was observed on the amorphous alloy.
  • calcium phosphate is formed, as in titanium alloys, it strengthens the bond between bone and the material, making it difficult to remove after bone fusion.However, in the case of amorphous alloys, such products are not generated. However, it becomes easy to remove after bone fusion, and it is most suitable as an intramedullary nail or osteosynthesis material.
  • Young's modulus and tensile strength are shown in Table 2 below for some examples of amorphous alloys.
  • amorphous alloys have excellent specific strength, low Young's modulus, and have physical properties closer to bone. For this reason, it is possible to produce an osteosynthesis material having the same strength and a smaller size (for example, the diameter of a hole having the same strength as a titanium alloy rod having a diameter of about 20 mm is about 15 to 16 mm) It is considered that it is hardly affected by load shedding and is advantageous for bone union. Therefore, when a thick intramedullary nail is inserted into the bone marrow as in the past, fat overflowing from the bone marrow enters the blood.
  • the amorphous state without grain boundaries is often higher in corrosion resistance than the crystalline metal, and is extremely advantageous as a material for medical use, particularly as an osteosynthesis material. is there.
  • amorphous alloys have lower Young's modulus and higher strength than crystalline metals, but these are very valuable properties for biomaterials.
  • the biomaterial member of the present invention is most suitable as an artificial bone material because of its low Young's modulus.
  • a fracture fixing material for shaping a spinal column fixing material, a fracture fixing material, an artificial joint, an intervertebral spacer, etc. It is useful as a material for various medical uses, such as surgical materials, dental materials such as crowns, inlays, crowns, prostheses, artificial roots, orthodontic wires, and general surgical materials such as surgical instruments.
  • the biomaterial member of the present invention has a polarization resistance in the degassed Hanks solution of 4 ⁇ 10 6 ⁇ cm 2 or more, and an immersion potential-pitting potential window of 0.25 V or more, preferably
  • any substantially amorphous alloy material containing an amorphous phase having a Young's modulus of 100 GPa or less and at least a volume fraction of 50% or more can be applied without particular limitation.
  • the present invention can be suitably applied to an amorphous alloy having a composition represented by any one of the formulas (1) and (2). If the volume ratio is less than 50%, the invention can be applied to an amorphous alloy containing nanocrystals or quasicrystals.
  • M 1 is one, two or three elements selected from Zr, Hf and Ti; M 2 is Cu, Fe, Co, Mn, Nb, V, Cr, Zn, At least one element selected from the group consisting of Al, Sn and Ga; M 3 is at least one element selected from the group consisting of B, C, N, P, Si and 0; and M 4 is Ta , W And at least one element selected from the group consisting of Mo, M 5 is Au, P t, at least one element selected from the group consisting of Pd and Ag, a, b, c, d, and e it It is in atomic%, 25 ⁇ a ⁇ 85, 15 ⁇ b ⁇ 75, 0 ⁇ c30, 0 ⁇ d ⁇ 15, 0 ⁇ e ⁇ 15. )
  • M 1 is an essential-based metal element order to form an amorphous
  • M 2 decreases the melting point by combining the M 1, eutectic This has the effect of easily causing supercooling during solidification, and can facilitate the formation of amorphous.
  • M 4 promotes passivation of the surface of the amorphous phase and improves corrosion resistance.
  • M 5 is improves the corrosion resistance, is suppressed oxidation of the molten metal by the flux effect, the degree of supercooling for reducing heteronuclear production formation site increases, improving the amorphous formation capability.
  • an amorphous alloy having a glass transition region having a temperature width of 30 K or more is preferable.
  • FIG. 3 shows an embodiment in which the biomaterial made of the amorphous alloy of the present invention is applied to an intramedullary nail.
  • the intramedullary nail 1 After being implanted in bone A, the intramedullary nail 1 is fixed with an interlocking nail (side stop screw) 2.
  • the intramedullary nail 1 and the inner rocking nail 2 are made from the amorphous alloy of the present invention.
  • Fig. 4 shows the application of a biomaterial made of the amorphous alloy of the present invention to an osteosynthesis plate.
  • 2 shows an embodiment according to the invention.
  • the joint plate 3 is applied to the bone A fractured at the fracture site X, and is fixed by the osteosynthesis plate fixing screw (screw) 4.
  • the joint plate 3 and the screw 4 for fixing the osteosynthesis plate are made of the amorphous alloy of the present invention.
  • the surface polished with # 600 SiC abrasive paper was used for measurement.
  • the surface polished with # 600 SiC abrasive paper was used for measurement.
  • Figure 5 shows the measured polarization curves.
  • Table 3 shows the corrosion characteristic values obtained from the polarization curves.
  • R p of the amorphous alloy an order of magnitude higher than SUS 3 16 L steel, since was several times higher than the pure T i, the corrosion resistance of the amorphous alloys than S US 3 1 6 L Steel It was found to be very high and equal to or higher than pure i.
  • the passivation current density of this amorphous alloy was as low as that of pure Ti. From this, it was found that the passivation film of the present amorphous alloy had a protective property equal to or higher than that of pure Ti.
  • pitting was observed on the polarization curve of the amorphous alloy. It was evaluated by the potential difference between the p en and pitting power position (E pit). Since the potential difference of the amorphous alloy was almost the same as that of SUS316L steel, it is considered that the pitting corrosion resistance of this amorphous alloy is equivalent to that of SSUS316L steel.
  • an amorphous alloy rod with a diameter of 2 mm and a length of 35 mm was inserted into the bone marrow, and for biosafety, blood metal concentration (Cu) and metal content in tissues were included. Evaluation was based on the amount (Cu).
  • a group in which Ti-6A1-4V alloy and SUS316L steel were inserted intramedullary and a control group in which no metal was introduced were used as comparison controls.
  • the corrosion and wear of the amorphous alloy removed after implantation were evaluated using a scanning electron microscope (SEM) and energy dispersive X-ray spectroscopy (EDS).
  • the metal materials for comparison were Ti-16A1-4V alloy and SUS316L.
  • Test Example 2 The results of Test Example 2 are summarized below.
  • the amorphous alloy ribbon was implanted for 6 weeks, but no effect on the living body was observed in the optical microscope image of the surrounding tissue.
  • the concentration of CU in the blood which could adversely affect the living body, did not increase. From the above, there was no adverse effect on living tissues when the amorphous alloy was implanted into the bone surface for 6 weeks.
  • the amorphous alloy alloy was inserted for 6 weeks and 12 weeks, but neither the blood concentration of Cu nor the metal content in the tissue increased compared to the Ti-6A1-4V alloy group and the control group.
  • the amorphous alloy alloy was inserted for 6 weeks and 12 weeks, but neither the blood concentration of Cu nor the metal content in the tissue increased compared to the Ti-6A1-4V alloy group and the control group.
  • the average bone mass ratio compared to the contralateral side (non-operative side) tended to be higher than that of the group using the SUS316L rod and T1-6A1-4V rod for the amorphous alloy.
  • the amorphous alloy is safe as an osteosynthesis material, and is advantageous for bone fusion at a fracture.
  • the biomaterial member of the present invention does not contain Ni as an allergic source, has excellent corrosion resistance to biological fluids, has high strength, has a low elastic modulus, does not easily react with the living body, and has completed the treatment. It is easy to remove later, and when used as an intramedullary nail etc., it is unlikely to cause so-called stress shield ⁇ pulmonary infarction.
  • dental crowns, inlays, crowns, prostheses, and human roots such as orthopedic spinal fixation materials such as intramedullary nails and osteosynthesis plates, fracture fixation materials, human joints, and intervertebral spacers It can be suitably used as a biomaterial member useful for an orthodontic wire, a surgical instrument for general surgery, and the like.

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  • Health & Medical Sciences (AREA)
  • Surgery (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • General Health & Medical Sciences (AREA)
  • Orthopedic Medicine & Surgery (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Veterinary Medicine (AREA)
  • Public Health (AREA)
  • Animal Behavior & Ethology (AREA)
  • Vascular Medicine (AREA)
  • Epidemiology (AREA)
  • Chemical & Material Sciences (AREA)
  • Neurology (AREA)
  • Inorganic Chemistry (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Medical Informatics (AREA)
  • Molecular Biology (AREA)
  • Materials For Medical Uses (AREA)
  • Prostheses (AREA)

Abstract

L'invention concerne un élément de matière biologique constituée d'un alliage amorphe qui présente une résistance de polarisation dans une solution de Hank dégazée de 4x106 Φcm2 ou plus et une fenêtre de potentiel d'immersion/potentiel de corrosion par piqûres de 0,25V ou plus. Dans un mode de réalisation approprié, cette matière biologique est constituée d'un alliage amorphe qui présente un module de Young de 100 GPa ou moins. Cette matière biologique présente les caractéristiques suivantes : elle est dépourvue de Ni comme source d'allergie potentielle, elle est hautement résistante à la corrosion grâce aux fluides biologiques, elle est hautement résistante, elle présente un faible module d'élasticité, elle réagit difficilement à un corps vivant et elle peut être facilement enlevée, une fois le traitement achevé. En cas d'utilisation d'un clou centro-médullaire ou d'un instrument analogue, la matière biologique selon l'invention ne pose pas de problèmes, tels que le 'stress shielding' ou l'infarctus pulmonaire. En raison de ces caractéristiques, la matière biologique selon l'invention constitue la matière osseuse artificielle la plus indiquée pour une utilisation, par exemple, avec un clou centro-médullaire (1) qui est intégré dans un os A, puis fixé avec un clou de verrouillage (une vis horizontale) (2), une plaque de connexion osseuse ou une vise de fixation osseuse.
PCT/JP2003/011263 2002-09-03 2003-09-03 Élément de matière biologique Ceased WO2004022118A1 (fr)

Priority Applications (1)

Application Number Priority Date Filing Date Title
AU2003261912A AU2003261912A1 (en) 2002-09-03 2003-09-03 Biomaterial member

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
JP2002258120A JP2004089580A (ja) 2002-09-03 2002-09-03 生体材料部材
JP2002-258120 2002-09-03

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WO2004022118A1 true WO2004022118A1 (fr) 2004-03-18

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CN104587532A (zh) * 2014-03-19 2015-05-06 西安爱德万思医疗科技有限公司 一种人体可吸收的耐蚀高强韧锌镁合金植入材料
CN104328312A (zh) * 2014-10-20 2015-02-04 东北大学 一种医用生物可降解锌合金及其制备方法
EP3128035A1 (fr) 2015-08-03 2017-02-08 The Swatch Group Research and Development Ltd. Alliage amorphe massif à base de zirconium sans nickel

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