Dieter ScharnweberMaterials in Biomedicine 1
7. Cobalt based & shape memory alloys, biodegradable metals
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Groups of materials – CoCr based alloys
1.1. Classifications + Applications1.2. Chemical compositions1.3. Mechanical properties for cast/wrought materials
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The Co-Cr-phase diagram
austenite
hcp … hexagonal closed packed
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Classifications
Typically 60 – 70 % Co, 20 – 30 % Cr, (+ Ni, Mo, W, …)
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Alloy Application
CoCrMo (cast) Joint implants (hip, knee, elbow, shoulder, angle, finger)
Bone plates and screwsArtificial heart valves
CoCrMo (wrought) Joint implants
CoCrWNi (wrought) Joint implantsArtificial heart valvesWiresInstruments for surgery
CoNiCrMo (wrought) Hip stems (too soft for joint balls)
Start in 1929 with applications in dental surgery
Applications
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Chemical compositions
CoCr-MoCast alloy
CoCrWNiwrought alloyHS 25
CoNiCrMowrought alloyMP 35 N
Composition (mass%)
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alloy structure Tensile strenght Elongation at fracture [%]
Tensile Fatigue strenght
cast
wroughtsintered
Cold workedannealed
annealedCold worked
Cold worked and aged
Physical and mechanical properties
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Groups of materials – Shape memory alloys
1. Materials2. The basic effect
1. Shape memory2. Superelasticity
3. Properties4. Applications
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Binary phase diagram Ni-Ti
> 90 % of application with NiTi, NiTi-Cu, NiTi-Nb
Materials
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The basic effect - crystal structures
austenite austenite Twisted martensite
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Supereleastic behaviour - limited to a few tens of °C above Af (up to MD)
Transformation starts at critical stress p-m (p-m increases linearly with temperature with ~ 2 - 15 MPa K-1, with p-m = 0 for Ms) – reversible strains up to 8 %!!!
Superelasticity
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Transformation mechanism as f (T)
With increasing stressbelow As
elastic strain of (twinned) M / (plastic) detwinning of M / elastic strain of M / plastic strain of M / fracture
between As and Af
(plastic) detwinning of M + elastic strain of A / transformation of A fraction to detwinned M / elastic strain of M / plastic strain of M / fracture
between Af and MD
elastic strain of A / transformation of A to detwinned M / elastic strain of M / plastic strain of M / fracture
above MD
elastic strain of A / plastic strain of A / fracture
Superelasticity irreversible
MD
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Properties – comparison with other actuator principles
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Summary of physical parameters
Property Unit Value
Density g cm-3 6.5
Thermal conductivityof austeniteof martensite
W m-1 K-1
18 8.6
Transformation enthalpie J kg-1 15 000
Resistivityof austeniteof martensite
10-6 m1.00.8
Transformation temperature °C -150 to 100
Hysteresis °C 5 – 50
One way memory strain % 3 – 8
Superelastic strain % 6 – 8
Work output J g-1 4
Maximum recovery stress MPa 600 - 900
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Function and application categories
• free recovery applications• clamping and fixation devices• actuation applications• biomedical and other superelastic applications• damping applications (in cold shape up to 90 % not
yet used for biomedical applications)• https://www.youtube.com/watch?v=e2f29Sw7UVc• https://www.youtube.com/watch?v=XPrg8EZlD1E
17
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galvanic corrosion by electron-conducting connection of different materials
dental surgery - more craftsman-like techniques in dental laboratory additional disadvantageous changes in materials microstructure caused by heat treatment during welding or soldering
Short-circuit potentials and local current investigations of the combining of titanium with several other alloys in a 1 % NaCl solution (pH 6.3), in part with 10 % lactic acid (pH 1.81) showed:
1. Using Ti/gold-based alloys, Ti/palladium-based alloys and Ti/non-precious alloys, titanium was under either cathodic or anodic control.
2. In combination with noble metal alloys: titanium acts as local anode because of stability of the ion-conducting passive layer no increased corrosion takes place
3. In combination with nickel-based alloys: titanium acts as the local cathode because of the n-semiconducting properties of the titanium passive layer increased corrosion appears. Causes corrosion attack of nickel-based alloys + in case of unfavourable surface ratios damage to titanium due to hydrogen embrittlement.
An alloy is potentially useable for superstructures in galvanic coupling with titanium if:in a coupling titanium has a weak anodic polarisationthe galvanic cell current density is also weakthe crevice corrosion potential is markedly higher than the coupling potential.
Combinations of metallic biomaterials
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Goal: development of alloys being able to replace amalgams Gallium based alloys
(typical) composition (Galloy®):solid component: 60% Ag, 28% Sn, 12% Culiquid component: 62% Ga, 25% In, 13% Sn (Fp 10 °C, (Fp for Gallium 29.8 °C))
Investigations in deoxygenated Ringer’s solution at 37 °C showed:
For uncoupled gallium-based alloy at low overpotentials: selective dissolution of divalent tin ions, followed by a dissolution of GaFor uncoupled gallium-based alloys and gallium alloy coupled with amalgam: anodic current densities 103-104 times higher than that of an uncoupled amalgam very poor corrosion stability.
Comparison of the cytotoxicity of gallium and indium ions with that of mercuric ions in a concentration range of 1 µM to 1 mM using L-929 mouse fibroblasts:
mercuric ions: 50 % inhibition at concentration of 0.35 mM
gallium and indium ions:did not significantly inhibit dehydrogenase activity in either growing or the confluent phase
Special Materials
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Effects of metal ions used in dental materials on conversion of amorphous calcium phosphate to hydroxyapatite in vitro:
According to effects on both the rate of hydroxyapatite transformation and induction time:
inhibitory (in the order: Ni, Sn, Co, Mn, Cu, Ga, Th, Mo, Cd, Sb, Mg, Hg)
ineffective (Cs, Ti, Cr, Fe2+)
stimulatory (Fe3+, In)
Summary• similar or better mechanical properties than modern (Hg) amalgams• difficult manipulation• low corrosion resistance• lack of gallium’s biological impact• → restricted use
Results from in vitro experiments
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Magnesium Alloys for use as degradablemetallic implants in musculo-skeletal surgery
Why?
Mg?• Essential to human metabolism – co-factor for many enzymes & stabilizes DNA and RNA• Fourth most abundant cation in human body: 25 g in adult body, about 50 % in bone• Extracellular fluid level 0.7 to 1.05 mM• effectively excreted in urine
historyFirst use in human 1907 (Mg plate with gold plated steel nails to secure bone fracture in lower leg
failed by disintegration after 8 days + large amount of H2 gas
During WW II in Russia to secure fractures and to treat gun shot woundsno increased levels of serum Mg, no distinct inflammatory reactions, but gas cysts – treated by drawing gas with subcutaneous needle
from Staiger et al. Biomaterials 27(2006) 1728
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Magnesium Alloys for use as degradable metallic implants in musculo-skeletal surgery
Current status
New alloys to improve mechanical properties & corrosion resistancea) 2 – 10 wt% Al + traces of Zn + Mgb) 0.4 - 4 wt% mixture of rare earth elements + (traces) of Zn, Ag, Zr,
In vivo results
from Witte et al. Biomaterials 26(2005) 3567
ACP within corrosion product layerImproved mineralization of surrounding bone
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Magnesium Alloys for use as degradable metallic implants in musculo-skeletal surgery
Results:In vitro corrosion rates in artificial seawater four orders of magnitude higher than in vivo rateTendency of corrosion rates in vivo and in vitro was in the opposite direction
from Witte et al. Biomaterials 27(2006) 1013
AZ AlZn91 LAE LiAlRE442
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Magnesium Alloys for use as degradable metallic implants in musculo-skeletal surgery
Open questions
Behaviour / toxicity of alloying elementsFormation of H2 gasAdaptation of corrosion rate
summaryBiodegradable material with mechanical (+ biological) properties superior to most biodegradable polymeric materials
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Iron - hMSC on Fe(CPP) scaffolds
Fe13-Brushit Fe13-HAp2McCoys DMEM McCoys DMEM
3d
14d
7d
21d
Fe13 Fe13-HAp2 Fe13-Brushit3 Fe13-MgCPC
O2 ↓↓ ↓ ≈ control ≈ control
Fe ↑↑ ↑ - -
H2O2 ↑↑ ↑ - -
Ca ≥ control ↓ ≥ control
pH ≈ control ↑ ≈ control
Cytotoxicity f (concentration) f (concentration) no no
Adhesion already difficult with SaOs-2
Proliferation (static) ↓ +/- 0 ↑↑Differentiation (static)
Proliferation (dynamic) ↓ ↑ ↑↑Differentiation (dynamic) ↑
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Degradable cardiovascular iron stents
from Peuster et al. Heart 86(2001) 563
Material: > 99.8 % Fe (third most abundant cation in human body)Animal experiment in rabbits – native descending aorta – 6…18 month
Result:No thromboembolic complicationsNo adverse effectsNo significant neointimal proliferationNo pronounced inflammatory responseNo systemic toxicity