Lecture3-Bone Mechanics and Remodbhgelling
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Transcript of Lecture3-Bone Mechanics and Remodbhgelling
Lecture 3Bone Mechanics and Remodelling
http://www.aeromech.usyd.edu.au/people/academic/qingli/MECH4961.htmCourse Web
Imaging of Bone StructureImaging of Bone Structure
DEXA – Dual energy X-ray absorptiometry• Provide mineral content or density It is popular in examination of osteoporotic change but insensitive to structural changes. It is a means of measuring bone mineral density (BMD). Two X-ray beams with differing energy levels are aimed at the patient's bones. When soft tissue absorption is subtracted out, the BMD can be determined from the absorption of each beam by bone..
MRI – Magnetic Resonance Imaging• Soft tissues (bone marrow, fat, muscle) - give clear pictures of soft tissue structures near and around bones, it is usually the best choice for examination of the body's major joints, the spine for disk disease and soft tissues of the extremities. MRI is widely used to diagnose sports-related injuries, as well as work-related disorders caused by repeated strain, vibration or forceful impact.
CT – X-ray Computed Tomography - Nobel Prize device (1979).A medical imaging method employs tomography where digital geometry processing is used to generate a 3D image of the internals of an object from a large series of 2D X-ray images taken around a single axis of rotation. • Hard tissues and real 3D architecture on bone in a nondestructive way
Typical Nominal ResolutionsTypical Nominal Resolutions
Device Resolution (In-vivo)Medical CT 200×200×200μm
3D-pQCT 165×165×165 μm
Micro-CT 14×14×14 μm
3D-Micro-CT 28×28×28 μm
Synchroton-CT 2×2×2 μm
MRI 150×150×150 μm
Mirco-MRI 40×40×40 μm
(The data are keeping updating)
DEXA DEXA –– Dual Energy XDual Energy X--ray ray AbsorptiometryAbsorptiometry
GE Lunar DEXA
Medical MRIMedical MRI
MRI image of knee jointSample image: MR of the knee - side (lateral) view, showing distal or lowest part of femur, the patella (knee cap) and proximal (upper) tibia. The lateral meniscus is seen as a dark bow-tie like structure. The patellar tendon is also clearly seen at the front of the knee connecting the patella with the tibia.
MRI resolution <150μm)
MedicalMedical--CT ScanningCT Scanning
Medical CT Scanner (resolution <200μm)
MicroMicro--CT ScannerCT Scanner
MicroCT Scanner (SkyScan 1172, resolution <5μm)
Reconstruction: CT Scanning → sectional Image → Segmentation → 3D image (STL)
CT Reconstruction of Bone Microstructures CT Reconstruction of Bone Microstructures
32 years old man 59 years old man 89 years old man
37-year old man without bone disorder (lelf) and 73-year old osteoporotic woman (right)
Density and Density and EE--Modulus of Modulus of CancellousCancellous BoneBone
The best-established relationship is that between cancellous bone Young’s modulus and its structural apparent density (i.e. the weight per unit volume of a material including voids inherent ), as follows.
paE ρ=References Power Variance
Carter and Hayes (1977) J Bone Joint Surg, 59 :954 p=3.00 74%
Kabel et al (1999), Bone 24:115 p=1.93 94%
Rice et al (1988), J Biomech 21:155. p=2.00 78%
Hodgskinson and Currey (1992), J mater Sci Mater Med 3:377 p=1.96 94%
Density Density –– Elastic Constant Models Elastic Constant Models –– ContCont’’dd
931931
931 00042401800
813813 .tissue
.
tissue.
tissue .EEEE φρφ =⎟⎠⎞
⎜⎝⎛==
• Kabel model (1999) - isotropic
• Hodgskinson-Currey model (1992) 9610037150 .mean .E ρ=
( ) ( ) ( )92133
89122
8111 5298851240 .
tissue.
tissue.
tissue EE,EE,EE φφφ ===
( ) ( ) ( )98112
97113
04223 697236333533 .
tissue.
tissue.
tissue .EG,.EG,.EG φφφ ===
( ) ( ) ( )248012
191013
086023 176031602560 .
tissue.
tissue.
tissue .E,.E,.E −−− === φνφνφν
• Yang (1999) – orthotropic cancellous model
φ – volume fraction and ρ =1800φ, ρ =kg/m3
Etissue – isotropic tissue Young’s modulus (GPa)
Orthotropic Constitutive Model of Bone Orthotropic Constitutive Model of Bone
9 independent components to elasticity matrix (along 3 directions)
⎪⎪⎪⎪
⎭
⎪⎪⎪⎪
⎬
⎫
⎪⎪⎪⎪
⎩
⎪⎪⎪⎪
⎨
⎧
⎥⎥⎥⎥⎥⎥⎥⎥⎥⎥⎥⎥⎥⎥⎥
⎦
⎤
⎢⎢⎢⎢⎢⎢⎢⎢⎢⎢⎢⎢⎢⎢⎢
⎣
⎡
−−
−−
−−
=
⎪⎪⎪⎪
⎭
⎪⎪⎪⎪
⎬
⎫
⎪⎪⎪⎪
⎩
⎪⎪⎪⎪
⎨
⎧
12
13
23
33
22
11
12
31
23
33
23
3
132
32
22
121
31
1
21
1
12
13
23
33
22
11
100000
010000
001000
0001
0001
0001
σσσσσσ
νν
νν
νν
εεεεεε
G
G
G
EEE
EEE
EEE
,,,G,G,G
,E,E,E
311332232112
312312
321
:RatiossPoisson'3:ModuliShear3
:ModulisYoung'3
νννννν ===E3(Axial)
E2(circumferential)
E1 (radial)
e3(Axial)
e2(circumferential)
e1 (radial)
Orthotropic Constitutive Model of Bone Orthotropic Constitutive Model of Bone –– ContCont’’d d
Young’s modulus Poisson’s ratio Shear modulus
E1=6.9GPa ν12=0.49, ν21=0.62 G12=2.41GPa
E2=8.5GPa ν13=0.12, ν31=0.32 G13=3.56GPa
E3=18.4GPa ν23=0.14, ν32=0.31 G23=4.91GPa
Young’s modulus Poisson’s ratio Shear modulus
E1=12.0GPa ν12=0.376, ν21=0.422 G12=4.53GPa
E2=13.4GPa ν13=0.222, ν31=0.371 G13=5.61GPa
E3=22.0GPa ν23=0.235, ν32=0.350 G23=6.23GPa
Tibia
Femur
(Humpherey and Delange, An introduction to Biomechanics, 2004)
CTCT--Based FE Based FE ModellingModelling of Microstructuresof Microstructures
Voxel-based FE model(element size: 25μm )
Solid-based FE model(element size: 150μm )
• Directly transfer pixel/voxel image to elements• Large number of elements• Stress concentration
• Segmentation• Creation of a series of curves• Creation of Surface/solid• FEM discretisation
RemodelingRemodeling
Remodeling involves changes in biological material properties.
These changes, which often are adaptive, may be brought about by alterations in modulus, internal structure, strength, or density. For example, bones, and heart muscle may change their internal structures through reorientation of trabeculae and muscle fibers, respectively.
Wolff’s Law1892 Julius Wolff stated “every change in the function of bone is followed by certain definite changes in internal architecture and external conformation in accordance with mathematic laws.”
Cancellous Cortical
RemodellingRemodelling –– Biomechanical Causes Biomechanical Causes
Biological remodeling due to changes inBiological remodeling due to changes in•• Stress/strainStress/strain•• Strain energy densityStrain energy density•• Loading frequencyLoading frequency•• MicroMicro--crackscracks•• Temperature, environmentTemperature, environment
Remodeling (growth) of trees Remodeling (growth) of trees ((MattheckMattheck 1998)1998)
Bone remodeling in mice Bone remodeling in mice (Burr et al 2002)(Burr et al 2002)
RemodellingRemodelling –– Biomechanical Causes Biomechanical Causes
Step 1: stresses/strains cause a little crack, Step 2: cells turn into osteoclasts and dissolve (resorb) bone, Step 3: cells from the marrow space turn into osteoblasts and build new bone.
Remodeling mechanism due to microcracks
RemodellingRemodelling –– MicroMicro--cracks cracks
Mechanical Stimuli Mechanical Stimuli -- ψψStrain energy density
Energy stress – linearise the quadratic nature of U
Mechanical intensity scalar (volumetric shrinking/swelling)
von Mises stress (σ1, σ2, σ3 – principal stresses)
{ } { } [ ]23231313121233332222111121
21 εσεσεσεσεσεσψ +++++=== εσ TU
UEavgenergy 2== σψ
( ) Usign 332211 εεεϑψ ++==
( ) ( ) ( )[ ]213
232
2212
1 σσσσσσσψ −+−+−== vm
Daily stress (ni = number of cycles of load case i, N=number of different load cases, m=exponent weighting impact of load cycles)
( ) mNi
miid n
1
1∑ === σσψ
Mechanisms Mechanisms -- Transduction ofTransduction of Mechanical Mechanical SignalsSignals
Mechanism – bone tissue transduces the mechanical strain to adaptive response
• Piezoelectric properties of collagen
• Change in solubility of hydrozyapatite
• Fatigue microfracture damage-repair
• Hydrostatic presure of extracellular fluid influences on bone cell
• Hydrostatic pressure influences on solubility of mineral and collagenouscomponent
• Creation of steaming potential
• Direct response of cells to mechanical loading
Mechanical StimuliMechanical Stimuli -- ContCont’’dd
Site dependency• Different bones provide different mechanical functions (e.g. skull and femur)• Different sites have different biological environment (e.g. cell and nutrients)• Different remodelling equilibrium• Frost (Anat Rec, 1990) suggested: 4 bone envelops – trabecular, periosteal, endocortical and osteonal
Time dependency• High frequency (25Hz) vs low frequency• Large load + low frequency (e.g. 4 cycle per day) can prevent mass loss, and 36 cycles can generate substantial bone growth• Fading memory – more recent loading is more important (cells may gradually become accommodated to a old changed mechanical environment)
Model ClassificationModel Classification
Optimisation model – bone is optimised for minimum mass, maximum strength, minimum the notch stress (but no adaptation for physiological process)
Phenomenological model – seek to describe the stimulus and the response quantitatively – particularly useful in developing simulations and predictions of bone adaptation (no interplay of genetics, hormones, drug therapy)
Mechanistic Model – cause-and-effect-based phenomenological model
RemodellingRemodelling
Micro- or Tissue view of point considers that cell responsible for bone resorption and deposition are always on various surfaces. Thus net remodelling can be described as a free-boundary problem
Continuum view of point considers functional adaptation as a coupled “free-boundary-vale problem” – a time dependent description for
• Changes in bone materials properties – Internal Remodelling
Material property [C] will be a function of time:
• Change in external geometry of cortical surface – Surface Remodelling
Surface (control point) will be a function of time:
[ ] ( )[ ]tCC =
[ ] ( )[ ]tSS =
Stimulus error:
Surface Surface RemodellingRemodelling RuleRule
( ) ( )t*te ψψ −=( ) stimulusmechanical=tψ
Surface Remodelling rate is proportional to stimulus error:(cs = constant)
Surface Remodelling Rule
ws = half-width of dead zone (lazy zone)
( ) ( )[ ]t*tcs s ψψ −=&
( ) ( )[ ] ( ) ( )( ) ( )
( ) ( )[ ] ( ) ( )⎪⎩
⎪⎨
⎧
−<−+−<−<−>−−−
=
sss
ss
sss
wt*twt*tcwt*tw
wt*twt*tcs
ψψψψψψψψψψ
forfor0
for&
Surface Surface RemodellingRemodelling RuleRule
*ψ ψ
Dead zoneLazy zone
0
s& ( ) ( )[ ]t*tcs s ψψ −=& ( ) ( )[ ]
( ) ( )[ ]⎪⎩
⎪⎨
⎧
+−
−−=
ss
ss
wt*tc
wt*tcs
ψψ
ψψ0&
sw* −ψ sw* +ψ
( ) ( )( ) ⎥
⎦
⎤⎢⎣
⎡ −=
t*t*tcs s ψ
ψψ&Alternative Remodel Rule
Internal Internal RemodellingRemodelling RuleRule
*ψ ψ
Dead zoneLazy zone
0
Alternative Remodel Rule
( ) ( )[ ]t*tc ψψρ ρ −=&( ) ( )[ ]
( ) ( )[ ]⎪⎩
⎪⎨
⎧
+−
−−=
ρρ
ρρ
ψψ
ψψρ
wt*tc
wt*tc0&
ρψ w* − ρψ w* +
( ) ( )( ) ⎥
⎦
⎤⎢⎣
⎡ −=
t*t*tc
ψψψρ ρ&
Computational Computational RemodellingRemodelling
Modifysurface
orBone
density
FEATo computestress/strain
tensor σ
UpdateFEA
Model
UpdateGeometry or
MaterialProperty
Applyremodeling
ruleYes
Equilibrium No ( ) ( ) wt*te 2>−= ψψ
Example 1 Example 1 –– Bone Loss in SpaceBone Loss in Space
Human spaceflight to mars could become a reality within the next 25 years, but not until some physiological problems are resolved, including an alarming loss of bone mass, fitness and muscle strength. Gravity at Mars' surface is about 38% of that on the earth. With lower gravitational forces, bones decrease in mass and density.
The rate at which we lose bone in space is 10-15 times greater than that of a postmenopausal woman and there is no evidence that bone loss ever slows in space. NASA has collected data that humans in space lose bone mass at a rate of c =1.5%/month so far.
Further, it is not clear that space travelers will regain that boneon returning to gravity. During a trip to mars, lasting between 13 and 30 months, unchecked bone loss could make an astronaut's skeleton the equivalent of a 100-year-old person.
Example Example –– Bone Loss in Space Bone Loss in Space –– ContCont’’dd
( ) ( )( ) ⎥
⎦
⎤⎢⎣
⎡ −=
−=≈=
+
t*t*tc
ttdtd nn
ψψψ
Δρρ
ΔρΔρρ ρ
1&
( ) ( )( ) tt*
t*tcnn Δψ
ψψρρ ρ ⎥⎦
⎤⎢⎣
⎡ −+=+1
Remodelling rule
380
MarstheonlevelStressearththeonlevelStress
.*
*
=
==
ψψψψ n%.c ρρ 51=
( ) ( )t.t%.. nnnn ΔρΔρρρ 009301516201 −=−=+Thus:
Mechanics of Introductory Example Mechanics of Introductory Example –– ContCont’’dd
How long could an astronaut survive in a zero-gravity environment if we assume the critical bone density to be ρcrit=1.0g/cm3. You may assume that an initial density on the earth is ρ0=1.79g/cm3 (due to ground preparation)
FS
S
x
y
l l
zF
Section S-S
x
y
Cortical
CancellousR
r
Assignment Assignment –– Part IPart I
{ } { } [ ]zxzxyzyzxyxyzzzzyyyyxxxxTU εσεσεσεσεσεσψ +++++===
21
21 εσ
Surface remodeling rate equation
Strain energy density
( ) ( )[ ] ( ) ( )( ) ( )
( ) ( )[ ] ( ) ( )⎪⎩
⎪⎨
⎧
−<−+−<−<−>−−−
=
sss
ss
sss
wt*twt*tcwt*tw
wt*twt*tcs
ψψψψψψψψψψ
forfor0
for&
Example 2 Example 2 –– Femur Growth (Internal Femur Growth (Internal RemodellingRemodelling))
Download the Matlab remodelling program from http://www.aeromech.usyd.edu.au/people/academic/qingli/MECH4961.htm
This is Part II of Assignment #3Change different load cases, cycles etc to observe the different bone formation