Ch 5 - Biomaterial Degradation Flashcards

1
Q

Metallic degradation

A

• “Corrosion” = leaching of ions from metallic surface into surroundings
* Metals more suscep. (in vivo) than ceramics

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2
Q

Redox reactions

A
  • OIL (of e-) → dissolution at \anode

* RIG (of e-) → deposition at \cathode

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3
Q

Nernst equation

A

ΔE=( E_2 - E_1 ) − (RT/nF) ∗ ln⁡( [M_1^n] / [M_2^] )

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4
Q

Galvanic corrosion

A

• 2 metals electrically coupled in the body, connected by physiological fluid (\salt bridge)
• More active/anodic metal will dissolve at accelerated pace (dissolution), generates e-
* Redox rates must equal s.t. overall corrosion is rate-limited by slower one
** Mitigated by non-reactive/cathodic metals OR w/ passive oxide coatings

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5
Q

Pourbaix diagram

A

• Potential (V) v. pH
1 . \corrosion = +10^-6 M ions in sol’n (at equil.)
2. \immunity = “cathodic protection”
3. \passivation = stable solid film
* dashed lines = stability of water (WANT B/W LINES)
** CANNOT predict rate of rxns

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6
Q

Cathodic protection

A

Not energetically favorable to corrode/dissolve

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7
Q

Passivation

A
  • Surface oxidation leads to formation of stable solid film that coats surface of metal
  • Can slow or stop corrosion (e- transfer), even if energetically favorable
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8
Q

Corrosion by processing parameters

A
  • ANY change in microstructure (processing, mech loading, proteins/bacteria) → change localized ion conc ∴ corrosion ↑
    • Mech stress → higher energy state, # microcracks ↑
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9
Q

Crevice corrosion

A
  • Depletion of O_2 in crevice (neces. for OH passive layer) → anodic rxn → pH ↓
  • Frees H+ ∴ corrosion
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10
Q

Pitting corrosion

A

• Flaw disrupts passivation film
• Small anode, large cathode (signif. dissolution of anode)
* Dangerous b/c may be undetected until sudden device failure

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11
Q

Intergranular corrosion

A

• GB = heightened energy state
∴ more active/anodic susc.
* can lead to intergranular attack (corrosion of passivating layer)
** Mitigated by heat treating

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12
Q

Mech corrosion: stress corrosion cracking

A

• Metal under tension AND subjected to corrosive envir.
• Small cracks form ⊥ to direction of applied stress
• \crack propag, brittle fracture
* Dangerous b/c can occur at low loads and normally tolerated sol’ns
** Mitigated by design w/ min. stress raisers

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13
Q

Fatigue corrosion

A
  • Con’t bending, loading or motion around implant may disrupt passivating film on surface → corrosion of local area
  • ↓ max stress at failure as N cycles ↑ (fatigue life ↓)
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14
Q

Fretting corrosion

A

Removal of passivating layer by mechanical motion near implant

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15
Q

Corrosion by biological envir

A
  • Inflam. cells: strong oxidizing agents, ↓ pH
  • Proteins: scavenge metals (alter equil → further dissolution)
  • Bacteria: infect device (affect passive layer by consuming H+ from cathode) → equil change, anodic dissolution
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16
Q

Ceramic degradation

A

• Breakdown of ceramic mat’ls
• Ceramics = passive layer (on metals) b/c more stable in physio. envir. (ionic bonds stronger)
* e.g. porosity/stress raisers → elev. energy → cracks → SA for rxn → water penetration → degradation

17
Q

Polymer degradation

A
  • \swelling/dissolution (breaking 2 ° chains)

* \chain scission (breaking 1 ° chains)

18
Q

Swelling/dissolution

A
  • Polymers w/ hydrophilic domains swell in physiologic envir. → water penetrates hydrophilic polymers (reduces 2 ° bonds, more ductile)
  • Not enough interchain bonding ∴ eventually falls apart
19
Q

Chain scission

A
  • Separation in chain segments at point of bond rupture ∴ overall ↓ MW
  • \hydrolysis or \oxidation
20
Q

Hydrolysis

A
  • Cleavage of crosslinks/hydrophobic side chains b/w chains via water molec’s → low MW, water-soluble products (to be cleared by body’s natural processes)

• PROMOTED by:
1 . ↑ Reactivity/# of groups in polymer backbone
2. ↓ Interchain bonding (MW, 1 ° bonds)
3. ↑ Amount media(water)/SA to penetrate polymer
• REDUCED by:
– Physical prop’s e.g. X-talinity (2 ° bonds) ↑ ∴ slows water
– Chem prop’s e.g. hydrophobicity ↑ ∴ slows water
– Water penetration ↓ ∝ degradation ↓

21
Q

Oxidation

A

• Highly reactive species (i.e. free radicals) attack and break covalent bonds in suscep. chem. groups within polymer backbone
• Radicals can either cause crosslinking or attack polymer chain (good/bad)
• Can reduce oxidation by: heating to allow radicals to recombine or adding radical scavengers e.g. vitamin E
* \initiation (homo-/heterolysis), \propagation and \termination
* Most often due to active agents released by inflam.

22
Q

Metal-catalyzed oxidation

A

Caused by corrosion of metal (interior) → formation of strong oxidizing agent/free radicals → attack polymer coating (from inside) → brittle fracture

23
Q

Environmental stress cracking

A

Polymer under sufficient tensile stresses in biological envir → exterior of implant develops deep cracks ⊥ to primary loading axis

24
Q

Enzyme-catalyzed degradation

A

Catalysts w/ affinity for polymer chemical groups → cleavage of crosslinks/hydrophobic side chains b/w chains → low MW, water-soluble products (to be cleared by body’s natural processes)
* Differs person to person (hard to predict extent)
** Rate depends on:
1 . amount of enzyme at implant site
2. # cleavable moieties

25
Q

Biodegradation

A
  • Chem breakdown of mat’l mediated by any compon. of physiological envir. e.g. water, ions, cells, proteins, bacteria
  • \Synthetic: typ. by hydrolysis (b/c more consistent patient to patient, v. enzymes)
  • \Natural: typ. by enzymes (allows more localized delivery)
26
Q

Biodegradable ceramics

A

• Typ. composed of CaPO_4 (orthopedics/bone tissue)
• Dissolution/disintegration influenced by:
1 . Chem suscep. (hydrated = faster erosion)
2. ↑ % crystalinity (less suscep. b/c tight packing)
3. Amount media/water
4. SA/vol ratio (porous = ↑ SA for dissolution)

27
Q

Biodegradable polymers

A
  • \bulk degrad: water in > rate of cleavage

* \surface degrad: water in < polymer hydrolysis

28
Q

Bulk degradation

A
  • Rate of water ingress > rate at which polymer is cleaved/converted into water-soluble degrad. products e.g. sutures
  • Often implant develops cracks and fissures before complete degrad.
  • Disadv: rapid ↓ mech prop’s/MW → collapse of implant (limited potential app., esp. in load-bearing app)
29
Q

Surface degradation

A
  • Rate of water penetr. into mat’l < rate of polymer hydrolysis e.g. implantable birth control
  • Implant ↓ thickness, but maintains mech prop’s/MW
  • Must possess highly hydrolytically labile (alterable) bonds and hydrophobic moieties (groups) to prevent signif. water penetr. into interior of device
  • Disadv: con’t turnover of implant surface → harder to est. good integr. w/ surrounding tissue
  • Often used for constant drug release (b/c rate of degrad. determined by geometry)
30
Q

Passive layer

A

Insulating layer made of hydroxides that form spontaneously on the surface of some metals