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1
Theories of Bone Modeling and Remodeling
Stresses and Strains at the Organ Level (Example #1):
Numerical Modeling of the Femoral Head
University of Paderborn, Germany 1
Stresses and Strains at the Organ Level (Example #2):
Numerical Modeling of trabecular core of the L1 Vertebra
2Rutgers University, Dept. of Mechanical and Aerospace Engineering
2
The above animations display nonlinear finite element simulation of compressive loading of bovine tibial trabecular bone. The volume on the left represents the full specimen (5mm cube). The animation on the right represents a 1.5mm cubed subvolume of the specimen. Red indicates tensile strain failure, while blue represents compressive strain failure.
Stresses and Strains at the Trabecular Level:
Compression Simulation using Finite Element Analysis
3
4a
Osteogenesis Modeling
Remodeling
Three major methods of bone adaptation:
4b
3
5
6
7
4
oWolff was a German Anatomist who is credited with general theory of bone adaptation known as Wolff's Law: 1870-1894
oSuggested that bone obtained maximum mechanical efficiency with minimum mass -> optimal configuration
oBone structure could adapt in response to changing Mechanical Environment
Summary of Wolff's Observations:
8
Wolff's law:
"Every change in the form and the function of a bone or of their function alone is followed by certain definite changes in their internal architecture, and equally definite secondary alterations in their external confirmation, in accordance with mathematical laws"
9
o Roux, a German surgeon, suggests in 1881 that cell activity is modulated by mechanical stress
o Apposition and resorption by cells determines change in bone structure
o Cell based apposition and resorption regulated by value of local stress
Summary of Roux's Observations:
10
5
o Koch, American Anatomist Johns Hopkins 1917, performed strength of materials analysis for proximal femur
o Confirms trajectorial theory, trabeculae along principal stress
o Suggests that bone density should be highest in areas of highest shear stress
o Again suggests bone attains maximum strength with minimum material
Summary of Koch's Observations:
11
Ø Trabecular orientation aligned with principal stresses
Ø Density highest in areas of highest shear (bending)
stress
Ø Bone structure can be adapted to change in load
Ø Bone cells may be regulated by local stress
Ø Results show no direct relation of stress to cell
activity; Relationship of bone structure to mechanics
derived without regard to physiological mechanisms
Summary of Observations 1865 1920:
12
13
6
o Glucksman performed experiments on tissue undergoing intramembranous ossification in vitro, Cambridge, 1938-1941
o Arranged ossifying tissues so that as they grew different amounts of tensile stress developed
o Tensile stresses promoted increased ossification of fibrous tissue
o Histological structure of ossifying tissue aligned along principal tensile stresses
A summary of Glucksman's results:
14
o Determined in 1966 that bone could be adapted by either modeling or remodeling mechanisms
o Determined that osteoblast and osteoclast activity were coupled during remodeling, no net gain of bone
o Suggested that the relationship between strains and bone mass was different in growing (modeling) and mature (remodeling)
Frost s contributions:
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7
Chamay & Tschantz (1972)
performed osteotomy of radius in dogs
17
o At 9 weeks, significant hypertrophy with 60% to 100% increase in cortical thickness
o Noted several cases of fatigue fracture
o Carter estimated strains were between 5000 and 7000 mstrain; suggested hypertrophy due to damage
Carter & co-workers (1981)
performed osteotomy of ulna in dogs
oMeasured strains in control and experimental limbs cortex with strain gauge
oFound strain increased from 600 mstrain to 1500mstrain after osteotomy
oNo significant change in bone geometry or deposition of mineral after 8 weeks
18
Bone Activity Principal Strain (mstrain)
Horse radius Trotting - (-0.28%)
Dog radius Trotting -2400
Goose humerus Flying -2800
Sheep femur Trotting -2200
Pig radius Trotting -2400
Fish hypural Swimming -3000
Monkey mandible Biting -2200
Rubin and Lanyon (1982):
19
8
Rubin and Lanyon (1984) also performed a procedure to isolate the turkey ulna and impose controlled dynamic bending strains on the isolated ulna
o Found that dynamic strains are necessary to maintain bone; Static load led to bone resorption
o 4 cycles of load per day was sufficient to maintain bone; 36 to 1800 cycles per day produced no response
20
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Frost s description of the different adaptational responses for the adolescent and the adult skeleton.
22
9
o Cowin proposed idea of adaptive elasticity 1976;
Hart performed computational implementation in 1983
o Separates surface and external remodeling
o Rate of Change of bone volume fraction related to strain
o Tensors A,B must be determined by experiment
o Constants difficult to determine:
Qualitative results good,
but accurate validation was not done
23
Hart (1983) reached the following conclusions:
24
Fyhrie s predictions of bone density distributions in the femoral head
Rem
odel
ing
Vec
tor
gain
loss
2s
Un U
Huiskes et als description of the density change rate in respect to the mechanical stimulus of the Strain Energy Density (U)
25
10
Dynamic Simulations of
Cancellous Bone Resorption Around
Orthopaedic Fixative Implants
Illustrative Example of Using the Algorithm by Huiskes:
Dr. Amit Gefen
The Musculoskeletal Biomechanics Laboratory
Deptartment of Biomedical EngineeringFaculty of Engineering, Tel Aviv University
26
Bone screws are well-known and clinically accepted means for fracture fixation or for stabilizing bone transplants
Background
27
Background (cont.) Since the screws remain attached to the bone after healing, they may also diminish its strength
The stiffer metallic screws (E>100 GPa) carry most of the shared load, causing the adjacent bone (E=1-20 GPa) to be atrophied in response to the diminished load it is carrying
cancellous bone resorption around the threads due to stress shielding
micromotion and possible loosening
Internal loads will be mainly supported by the screws, which are shielding the bone from carrying the normal mechanical stresses
This stress shielding effect alters the normal stress stimuli for bone growth, and, according to Wolff s law, bone will adapt itself by reducing its mass around the implant
28
11
Objective
Characterize screw designs that provide optimal stress transfer to the surrounding bone, and, thereby, alleviate commonly observed conditions of loosening and failure of fixations due to stress shielding
29
Methods Two finite element (FE) model types of the screw-bone mechanical interaction were developed:
cortical bone layer
cancellous bone bulk
80 N
axis
ymm
etri
c co
nstr
aint
s
axis of symmetry
scre
w
fixed constraints between the screw s head and cortical surface
typical meshing around the screw s threads
screw cortical bone layer
gluteus maximus, 900 N
gluteus medius, 1165 N
fixed constraints
joint reaction, 3150 N
cancellous bone
idealized axisymmetrical femoral head30
Methods (cont.)
dead zone
ψref + ωψref − ω
gain
loss ψψ
dρρdt
ψref
calculate loading history
control finite element model
solve von Mises stresses for reference signal ψref
bone-screw finite element model
solve von Mises stresses for transient stress state ψ
+- Σ
actual mechanical stimulus for modeling/ remodeling element stress
within dead zone ?
no
compute local bone density change using remodeling rule
steady state
reached ?
no
yes
yes
construct bone/screw geometries
STOP
An iterative algorithm for simulating bone adaptation around the screw was coupled with the FE models
remodeling rule
remodeling algorithm31
12
Methods (cont.)
3αρ=Eα = 2875 MPa cm3/gr
(Carter and Hayes, 1977)
ρψ
U= σε ⋅=
2
1U
( )
( )
−−⋅
+−⋅
=
ωψψ
ωψψρ
cc
cc
dtd
ref
ref
0( )
( )ωψψ
ωψψω
ωψψ
+>−
+≥−≤−
−<−
ref
ref
ref
density-stiffness relation:
stress stimulus for bone remodeling:
remodeling rule:(van Reitbergen et al., 1993 )
c=0.02 (µm/day)/(MPa/day)(Beaupr et al. (1990)
Mat
hem
atic
al F
orm
ula
tio
n
32
Methods (cont.)
2low-stiffness titanium core
polymeric external layer and threads
following insertion of the screw, the steel sphere is pushed downward
the resulted opening of the screw s tip exerts controlled compression on adjacent bone
1
hollow canal
Newly Proposed ScrewsCommercial Designs
Graded-Stiffness Active-Compression
constant dimensions- shaft diameter- screw-head diameter- thread pitch- screw length
modified properties- material stiffness- thread profile shape- thread diameter- no. of threads
33
Methods (cont.)
cortical bone layer
cancellous bone bulk
σσ t
σσ fbσσ ft
j
σσb i
tf
bf
σ
σα =
∑
∑
∑
∑=
=
=
=
== N
jjt
N
iib
N
jjt
N
iib
N
N
2
2
2
2
1
1
σ
σ
σ
σβ
for the first thread:
for all other threads:
In order to quantify the screw-bone load sharing (and its evolution with bone adaptation) for the purpose of rating the different designs, two stress transfer parameters (STP) were defined,
34
13
Results
135100
65
35
25
2017
14
11
8
42
0
MPa
rectangular
wide profile
9 threads
* each time step represents 10 weeks of bone adaptation
triangular
wide profile
9 threads
trapezoidal
standard profile
9 threads
trapezoidal
wide profile
9 threads
Evolution of stresses around different screws idealized model
35
* each time step represents 10 weeks of bone adaptation
Results (cont.)
135100
65
35
25
2017
14
11
8
42
0
MPa
displacements(magnified ×× 30)
evolution of stresses
stresses around the threads
stresses around a graded-stiffness triangular screw
36
Results (cont.)Evolution of the STP for bone adaptation behavior around commercial screw designs
αα STP ββ STP
37
14
Results (cont.)Evolution of the STP for bone adaptation behavior around the newly proposed graded-stiffness and active-compression screws
0.5
0 .55
0.6
0 .65
0.7
0 .75
0.8
0 .85
0.9
0 .95
1
0 50 100 150 200Time [Weeks ]
αα
" A c t i v e - C o m p r e s s i o n " W i d e R e c t a n g u l a r
" A c t i v e - C o m p r e s s i o n " T r i a n g u l a r
" G r a d e d- S t i f f n e s s" W i d e R e c t a n g u l a r G r a d e d - S t i f f n e s s T r i a n g u l a r
0
0 .1
0 .2
0 .3
0 .4
0 .5
0 .6
0 5 0 1 0 0 1 5 0 2 0 0
T i m e [W e e k s ]
" A c t i v e - C o m p r e s s i o n " W i d e R e c t a n g u l a r
" A c t i v e - C o m p r e s s i o n " T r i a n g u l a r
" G r a d e d - S t i f f n e s s " W i d e R e c t a n g u l a r
" G r a d e d - S t i f f n e s s " T r i a n g u l a r
αα STP ββ STP
38
Conclusions
A method of evaluating and rating designs and expected biomechanical performances of orthopaedic fixative screws was presented.
Wide (6-mm thread diameter) rectangular and trapezoidal screw profiles have superior biomechanical compatibility with bone compared with other commercial designs
The promising computational STP results obtained for the graded-stiffness and active-compression screw designs will have to be validated with data from animal experiments
39
Conclusions (cont.)
Finally, it was demonstrated that bone remodeling computer simulations can be used as a highly effective tool for evaluation of several design parameters of the screws, such as geometry, material characteristics and even coating
40
15
41
üState of bone (growth, healing, mature) determines its ability to respond to mechanical strain
üMature bone may seek to exist within limited strain range
üResulting structure (from growth) shows attributes of efficient or optimized structure -> fully stressed / strained?
üComputational models have the ability to predict qualitatively correct bone structure distribution
üBone cells can respond directly to mechanical strain
Summary of State-of-the-Art Knowledge in Bone Adaptation Theory:
42
43
Future Work:
Ø Strain measured on cortical surface or computed by single level solid continuum models is not the same as that experienced by cells due to hierarchical bone structure
Ø Specific relationships between strain and adaptation for different states of bone response have not been clearly delineated
Ø Nature of loads on bone are difficult to determine, but are necessary to fully understand its mechanics and adaptation