第三天

Metals主题

K1: Do we needalloying elements for Mg implant materials?

Hort N, Mendis CL,Maier P

MagnesiumInnovation Centre, Helmholtz-Zentrum Geesthacht, Geesthacht, Germany

Application—property profile---materialsselection

Alloying elements

Any element besides matrix

Micro-alloying <1%

Macro-alloying >1 wt.%

Impurity=alloying element

Stable compound O F Cl

Technologically critic: Fe Co Ge As Se Te

Technologically critic but feasible Cd Ag Ga

Useable elements with known binary phasediagram: Li Ca Sr Ba Sc Y Zr Mn Cu Ag Au Ga Si Bi La Pr Nd Sm Eu Gd Tb Dy Ho ErTm Yb Lu

It is difficult to refine pure Mg (Zr, coldwork + recrystallization)

Mg2.4Zn0.1Ag0.1Ca0.1Zr script mater 64(2011) 335

Stiffness is not the strength

sspec=s/(r*g)(Kg)

Alloying elements, processing steps, requirementsneed to be synchronized.

Defined bench ( give me numbers) arenecessary

O1. Development of high-strengthbioabsorbable Mg alloys suitable for conventional cold-working processes

Griebel AJ, Schaffer JE

Fort Wayne MetalsResearch Products Corp., Fort Wayne, IN, USA

现在研究的医用镁合金没有ZM21 AZ31 AZ61的relative strength的，PLLA PGA的formability

Mg-6Li, Mg-6Li-Al-0.5RE(断裂强度495MPa),Mg-6Li-1Ca, Mg-6Li-0.25Ca

Commercially viable cold-forming, up to 98%reduction of area

O2. Porosity andYoung´s-modulus control und measurement on Mg alloy parts, produced by PM(Powder Metallurgy) and MIM (Metal Injection Moulding)

Wolff M, Ebel T,Kainer KU, Klassen T

Helmholtz-ZentrumGeesthacht, Germany

E-modulus

Characteristicphysical value of the materials or materials characterisatics of theproducts/specimen?

E-moduluscalculation via tensile testing

materials showssame E-properties after plastic deformation

Nonlinear elasticbehavior of Mg [Beck et al., 1940]

Mg does not havean E-modulus in the common way of understanding.

Hyperbolicfunction for E-modulus calculation

Dynamic methodsfor E-modulus calculation

Porositycalculation, via analysis software, photopshop software

Pure Mg+waxpolymer additive        MIM

O3. Characterizationof biodegradable magnesium single crystals with various crystallographicorientations

Shin KS, Jung HC,Bian MZ, Nam ND, Kin NJ

MagnesiumTechnology Innovation Center, Seoul National University, Seoul, South Korea

单晶沿着不同方向切，从(0001)到（1010）隔10度一切，腐蚀速度不同。不同的pitting corrosion rate

利用XPS测Cl2p说明不同表面被Cl离子attack的程度不同

O4. Preparation,mechanical and degradation properties of Mg-based microwire for self-assemblystents

Peng Q, Fu H, ZhangJ, Tian Y, Liu R

State KeyLaboratory of Metastable Materials Science and Technology, Yanshan University,China

Stent pipefabricated by the backward extrusion

Stent prepared bymicrowires with melt extraction method

It is still notstable to prepare the uniform tube due to the fluctuation of the bob.

O5. Amorphous alloys– processing, properties and applications

Laws KJ, Cao JD,Ferry M

School ofMaterials Science and Engineering, UNSW, Australia

Mg-Zn-Ca BMG

Mg-rich BMGs---poor thermoplastic forming

Ca-rich BMGs---disintergrate

Zn-richBMGs---poor GFA

Aim: ExploreCa-rich BMGs with high Zn content as potential restorable metals

O6. Fe-based alloyswith TWIP effect for biodegradable stents

Mouzou E, Purnama A,Mostavan A, Paternoster C, Tolouei R, Turgeon S, Mantovani D

Lab. forBiomaterials & Bioengineering (CRC-I), Dept. Min-Met-Materials Engineering& University Hospital Research Centre, Un iversité Laval, Québec City,Canada

For stent, the YS>250MPa UTS>600MPa, elongation >25%, corrosion rate 0.5-0.9mm/Year

High Mn TWIP steel,Fe-Mn-C, the corrosion rate is 0.29 mm/year, 由于强度高可以降低strut thickness从而达到整体降解提高的目的。

Current opinion insolid state and materials science 15(2011) 141-168

O7. Effect of phosphorus on the corrosionbehaviour of electroformed iron-based bilayer materials targeted forbiodegradable stent application

Mostavan A, Paternoster C, Tolouei R, DubéD, Mantovani D

Lab. forBiomaterials & Bioengineering (CRC-I), Dept. Min-Met-Materials Engineering& University Hospital Research Centre, Université Laval, Québec City,Canada

Tubeelectroforming---grinding---mini tube

To obtain bilayerby dual bath technique

Fe electrolyte andFeP electrolyte

Fe layer- FePlayer

E;Fe/FeP1.28mm/year

下午的报告比较短，实际上是墙报的简单介绍，不许提问，每个讲5分钟。

SOP1. Development ofPLGA-infiltrated porous iron for temporary medical implants

Yusop AH, Daud NM,Hermawan H

Faculty ofBiosciences and Medical Engineering, Universiti Teknologi Malaysia (UTM),Malaysia

Acceleratedegradation and enhanced biocompatibilty

SOP2. Degradationstudy of Fe-cermica biocomposites

Nordin JA, Daud NM,Prajitno DH, Nur H, Hermawan H

Faculty ofBiosciences and Medical Engineering, Universiti Teknologi Malaysia (UTM),Malaysia

HA TCP BCP, 75nm Fepowder 450 micrometer Press at 11.8MPa, pillet with 12 mm diameter, SinteringVacuum 1100 degree C

Immersion Weightloss Pure Fe<Fe-Ha<Fe-BCP<Fe-TCP

Electrochemicalmeasurement: Pure Fe<Fe-Ha<Fe-TCP<Fe-BCP

SOP3. Stentmaterials-dependent macrophage fusion and secretion of inflammatory cytokineand chemokine

Mao L, Kwak M, Xue Q,Lu Y, Niu J, Zhang J, Yuan G, Fan R

School of MaterialsScience and Engineering, Shanghai Jiao Tong University, Shanghai 200240, China

Primary macrophageson Mg

SOP4. Microstructure,mechanical properties and corrosion behaviour of Mg-3Al-1Zn alloy stent tubes

Hanada K, Huang X,Matsuzaki K

AdvancedManufacturing Research Institute, National Institute of Advanced IndustrialScience and Technology (AIST), Japan

Effect of grainsize on the mechanical properties and corrosion resistance

AZ31 stent tubswith various hcp orientation

The deformabilityin the wall thickness and

The tube withlargely tilted c axis of hcp to the circumferetial direction in an appropriatefor stent application

SOP5. SuLaser surfacestructuring of Mg stent

Demir AG, PrevitaliB, Furlan V

Department ofMechanical Engineering, Politecnico di Milano, Italy

Laser structuringof the stent surface in order to increase adhesion of polymer coating

Laser cutting withproductive nanosecond pulsed laser

Laser cutting with “cold”femtosecond pulsed laser

Surface remelting,with transition, worm, bud, …surface morphology

SOP6. Magnesiumand its alloys – an introduction to their metallurgy and deformation behaviour

Manuel MV

Department ofMaterials Science and Engineering, University of Florida, USA

SOP7. Mechanicalproperties and corrosion behaviour of ZK60 processed by ECAP for biomedicalapplication

Mostaed E, Ge Q,Vedani M, De Oliveira Botelho PA, Zanella C, Deflorian F

Department ofMechanical Engineering, Politecnico di Milano, Milan, Italy

4 passes at 3steps: 250, 200 and 150 degree C

Hot extrusion ofZK60 tube by using UFG billet

SOP8. Effect ofprocess on the properties of biodegradble Mg-2Zn-0.2Mn alloy

Huang N, Zhou SJ, GuoSJ, Wang J

Key Lab. ofAdvanced Materials Technology, Ministry of Education, Southwest JiaotongUniversity, China

Microstructure,degradation, blood compatibility

SOP9. Influence ofdifferent storage durations on the properties of degradable magnesium basedimplants

Bracht K, AngrisaniN, Seitx JM, Eifler R, Weizbauer A, Reifenrath J

Small AnimalClinic, Veterinary University of Hannover, Foundation, Hannover, Germany

Storage ofbiomedical device are invoidable.

Influence ofdifferent storage on Structural changes, biomechanical properties, in vitrodegradation

LAE442

0, 24, 48 weeks

Metallographic andcontrast analysis, three-point bending

No cleardifferences in grain size after 48 weeks

Percentageprecipitate tend to increase with time

In vitro corrosiondecrease 20%

Storage of Mg basedimplants hnas no appreciable effect on implant quality

SOP10. Degradation ofMg-Zn-Ca alloy processed by high pressure torsion for bone implant applicationin simulated body flood

Yue GC, Zhu SJ, WangLG, Ma X, Ji C, Guan SK

School of MaterialsScience and Engineering, Zhengzhou University, 100 Kexue Road 450001,Zhengzhou, China

5 rotations with apressure of 5GPa at room temperature

After HPT, grain sizefrom 80micrometer to 1 micrometer, second phase inside grain -40nm

Pitting corrosionchange into homogeneous corrosion

Higher content ofZn element

SOP11. Corrosion andwear behaviour of Mg-xZn-0.8Zr alloy in simulated body fluid

Liu D, Liu L, Liu Y,Song R, Chen M

School of MaterialsScience and Engineering, Tianjin University of Technology, Tianjin 300384,China

2,3,4,4.5 四个锌含量

3Zn UTS 290MPa,elongation 17.8%

Wear testing in SBFwith stainless steel pin

SOP12.Microstructures and corrosive properties in simulated body fluid of biologicalMg-Zn-Y-Nd alloy by friction stir processing

Guan SK, Zhu SJ, WangLG, Yue GC, Wang J, Jin J

School of MaterialsScience and Engineering, Zhengzhou University, 100 Kexue Road 450001,Zhengzhou, China

Complete uniformfine grain can be obtained

FSP sample showuniform corrosion

SOP13. Selectivelaser melting of biodegradable metals

Jauer L, Meiners W,Poprawe R

FraunhoferInstitute for Laser Technology ILT, Aachen, Germany

Major chanllenges

Small temperaturedifference between melting and evaporation

Reactiviity ofpowder materials

AZ91, WE43,AZ91/beta TCP(5 wt.%)

97..6% 93.8, 97.7density, respectively

Higher strength butless ductility than cast parts

Surface roughness<15 micrometer

Transfer to biodegradableFe-based alloy

SOP14: Effect ofnitrogen on microstructures in biomedical Co-Cr-Mo alloys

Alfirano

MetallurgyEngineering Department, University of Sultan Ageng Tirtayasa, Indonesia

(缺席)

SOP15. Fabrication and bioactivity ofNa2Ti6O13 nanofibers on micro-arc oxidized Ti

Lan Zhang, Yong Han

State KeyLaboratory for Mechanical Behavior of Materials, Xi'an Jiaotong University,China

Science 310(2005)1135

SOP16. Relationship between secondary phaseand corrosion properties of biodegradable Mg-based alloys

Idris MH,Bakhsheshi-Rad HR, Lotfabadi AF

Department ofMaterials, Manufacturing and Industrial Engineering, Universiti TeknologiMalaysia, Malaysia

To improve of thebiodegradation resistance Mg-5Ca through the addition of Zn

Mg 99.98, Zn, 99.99%, Mg-32Ca master alloy

Mg-5Ca-3Zn

Alfa-Mg+Mg2Ca+Ca2Mg6Zn3 eutectic