applied human anatomy and...
TRANSCRIPT
Applied Human
Anatomy and
Biomechanics
Course Content
I. Introduction to the Course
II. Biomechanical Concepts Related to Human Movement
III. Anatomical Concepts & Principles Related to the Analysis of Human Movement
IV. Applications in Human Movement
V. Properties of Biological Materials
VI. Functional Anatomy of Selected Joint Complexes
Why study?
� Design structures that are safe against the
combined effects of applied forces and
moments
1. Selection of proper material
2. Determine safe & efficient loading conditions
Application
� Injury occurs when an imposed load exceeds the tolerance (load-carrying ability) of a tissue� Training effects
� Drug effects
� Equipment Design effects
Properties of Biological Materials
A. Basic Concepts
B. Properties of Selected Biological Materials
A. Bone
B. Articular Cartilage
C. Ligaments & Muscle-Tendon Units
Structural vs. Material
Properties
Structural Properties
� Load-deformation
relationships of like
tissues
Material Properties
� Stress-strain
relationships of
different tissues
Terminology
� load – the sum of all the external forces and
moments acting on the body or system
� deformation – local changes of shape within
a body
Load-deformation relationship
� Changes in shape (deformation) experienced
by a tissue or structure when it is subjected to
various loads
Extent of deformation
dependent on:
� Size and shape (geometry)
� Material� Structure
� Environmental factors (temperature, humidity)
� Nutrition
� Load application� Magnitude, direction, and duration of applied force
� Point of application (location)
� Rate of force application
� Frequency of load application
� Variability of magnitude of force
Types of Loads
Uniaxial Loads
� Axial
� Compression
� Tension
� Shear
Multiaxial Loads
� Biaxial loading
responses
� Triaxial loading
responses
� Bending
� Torsion
Types of Loads
Axial Loads
Whiting & Zernicke (1998)
Shear Loads
Whiting & Zernicke (1998)
Axial Loads
Create
shear
load as
well
Whiting & Zernicke (1998)
Biaxial & Triaxial Loads
Whiting & Zernicke (1998)
Structural vs. Material
Properties
Structural Properties
� Load-deformation
relationships of like
tissues
Material Properties
� Stress-strain
relationships of
different tissues
Terminology – Stress (σ)
σ = F/A (N/m2 or Pa)
� normalized load
� force applied per unit area, where area is measured in the plane that is perpendicular to force vector (CSA)
Terminology – Strain (εεεε)
ε = ∆dimension/original
dimension
� normalized
deformation
� change in shape of a
tissue relative to its
initial shape
How are Stress (σ) and Strain
(εεεε) related?
� “Stress is what is done to an object, strain is
how the object responds”.
� Stress and Strain are proportional to each
other.
Modulus of elasticity = stress/strain
Typical Stress-Strain Curve
kxFe====
Elastic region & Plastic region
Stiffness
Fig. 3.26a, Whiting & Zernicke, 1998
Stiffness (Elastic Modulus)
Load (N)
Deformation (cm)
1 5 10 15 20 25
A
B C
1 2 3 4 5 6 7
Strength stiffness ≠ strength
•Yield
•Ultimate
Strength
•Failure
Apparent vs. Actual Strain
1. Ultimate Strength
2. Yield Strength
3. Rupture
4. Strain hardening
region5. Necking region
A: Apparent stress
B: Actual stress
Tissue PropertiesLoad (N)
Deformation (cm)
1 5 10 15 20 25
A
B C
Extensibility & Elasticity
ExtensibilityLoad (N)
Deformation (cm)
1 5 10 15 20 25
A
B C
1 2 3 4 5 6 7
ligament tendon
Rate of Loading
� Bone is stiffer, sustains a higher load to failure, and
stores more energy when it is loaded with a high
strain rate.
Bulk mechanical properties
� Stiffness
� Strength
� Elasticity
� Ductility
� Brittleness
� Malleability
� Toughness
� Resilience
� Hardness
Ductility
� Characteristic of a material that undergoes
considerable plastic deformation under
tensile load before rupture
� Can you draw???
Brittleness
� Absence of any plastic
deformation prior to
failure
� Can you draw???
Malleability
� Characteristic of a material that undergoes
considerable plastic deformation under
compressive load before rupture
� Can you draw???
Resilience
Toughness
Hardness
� Resistance of a material to scratching, wear,
or penetration
Uniqueness of Biological
Materials
� Anisotropic
� Viscoelastic
� Time-dependent behavior
� Organic
� Self-repair
� Adaptation to changes in mechanical demands
General Structure ofConnective Tissue
Cellular Component Extracellular Matrix
Protein Fibers
collagen, elastin
Ground
Substance(Fluid)
Resident Cells
fibroblasts,
osteocytes,chondroblasts, etc.
Circulating Cells
lymphocytes,
macrophages, etc.
synthesis &maintenance
defense &clean up
determines the functional characteristics of the connective tissue
Distinguishes CT from other tissues
…blast – produce matrix…clast – resorb matrix…cyte – mature cell
Collagen vs. Elastin
Collagen
� Great tensile strength
� 1 mm2 cross-section →
withstand 980 N tension
� Cross-linked structure →↑ stiffness
� Tensile strain ~ 8-10%
� Weak in torsion and bending
Elastin
� Great extensibility
� Strain ~ 200%
� Lack of creep
Types of Connective Tissue
Ordinary Special
Irregular Ordinary Regular Ordinary Cartilage Bone
Regular Collagenous
Regular Elastic
Loose
Adipose
Irregular Collagenous
Irregular Elastic
•Number & type of cells•Proportion of collagen, elastin, & ground substance
•Arrangement of protein fibers
•Bind cells•Mechanical links•Resist tensile loads
Why study?
� Design structures that are safe against the
combined effects of applied forces and
moments
1. Selection of proper material
2. Determine safe & efficient loading conditions
Application
� Injury occurs when an imposed load exceeds the tolerance (load-carrying ability) of a tissue� Training effects
� Drug effects
� Equipment Design effects
Properties of Biological Materials
A. Basic Concepts
B. Properties of Selected Biological Materials
A. Bone
B. Articular Cartilage
C. Ligaments & Muscle-Tendon Units
Mechanical Properties of Bone
� General
� Nonhomogenous
� Anisotropic
� Strongest
� Stiffest
� Tough
� Little elasticity
Material Properties: Bone Tissue
� Cortical: Stiffer, stronger, less elastic (~2% vs.
50%), low energy storage
Mechanical Properties of Bone
� Ductile vs. Brittle
� Depends on age and rate at which it is loaded
� Younger bone is more ductile
� Bone is more brittle at high speeds
Glass
Bone
Metal
σ
ε
•Stiffest?
•Strongest?
•Brittle?
•Ductile?
old
young
Tensile Properties: Bone
Ultimate
stress (MPa)
Modulus of
elasticity (GPa)
Strain to
Fracture (%)
Collagen 50 1.2 -
Osteons 38.8-116.6 - -
Axial
Femur (slow)
(fast)
78.8-144 6.0-17.6 1.4-4.0
Tibia (slow) 140-174 18.4 1.5
Fibula (slow) 146-165.6 - -
Transverse
Femur (fast) 52 11.5 -
Stiffness
Compressive Properties: Bone
Ultimate
stress (MPa)
Modulus of
elasticity (GPa)
Strain to
Fracture (%)
Osteons 48-93 - -
Axial
Mixed 100-280 - 1-2.4
Femur 170-209 8.7-18.6 1.85
Tibia 213 15.2-35.3 -
Fibula 115 16.6 -
Transverse
Mixed 106-133 4.2 -
140-174
146-165.6
78.8-144 1.4-4.06.0-17.6
18.4
Other: Bone
Ultimate
stress
(MPa)
Modulus of
elasticity
(GPa)
Strain to
Fracture
(%)
Shear 50-100 3.58 -
Bending 132-181 10.6-15.8 -
Torsion 54.1 3.2-4.5 0.4-1.2
Tension 78.8-174 6.0-18.4 1.4-4.0
Compression 100-280 8.7-35.3 1-2.4
From LeVeau (1992). Biomechanics of human motion (3rd ed.). Philadelphia: W.B. Saunders.
Ultimate
stress (MPa)
Modulus of
elasticity (GPa)
Strain to
Fracture (%)
Polymers (bone
cement)
20 2.0 2-4
Ceramic (Alumina) 300 350 <2
Titanium 900 110 15
Metals (Co-Cr alloy)
Cast
Forged
Stainless steel
600
950
850
220
220
210
8
15
10
Cortical bone 100-150 10-15 1-3
Trabecular bone 8-50 - 2-4
Bones (mixed) 100-280 8.7-35.3 1-2.4
Mechanical Properties of Selected Biomaterials
Viscoelastic Properties :
Rate Dependency of Cortical Bone
Fig 2-34, Nordin & Frankel, (2001)
•With ↑ loading rate:
� ↑ brittleness
� Energy storage ↑ 2X
(↑ toughness)
� Rupture strength ↑ 3X
� Rupture strain ↓100%
� Stiffness ↑ 2X
Viscoelastic Properties :
Rate Dependency of Cortical Bone
Fig 2-34, Nordin & Frankel, (2001)
•With ↑ loading rate:
� More energy to be
absorbed, so fx
pattern changes &
amt of soft tissue
damage ↑
Effect of Structure
� Larger CSA distributes force over larger area,
� ↓ stress
� Tubular structure (vs. solid)
� More evenly distributes bending & torsional stresses
because the structural material is distributed away from
the central axis
� ↑ bending stiffness without adding large amounts of bone
mass
� Narrower middle section (long bones)
� ↓ bending stresses & minimizes chance of fracture
Effects of Acute Physical Activity
Fig 2-32a, Nordin & Frankel (2001)
Acute Physical Activity
Fig 2-32b, Nordin & Frankel (2001)
•Tensile strength: 140-174 MPa
•Comp strength: 213 MPa
•Shear strength: 50-100 MPa
Acute Physical Activity
Fig 2-32b, Nordin & Frankel (2001)
•As speed ↑↑↑↑, εεεε and σσσσ ↑↑↑↑
•5X↑↑↑↑ in εεεε with speed
•εεεεwalk= 0.001/s
•εεεεslow jog = 0.03/s
Acute Physical Activity
Fig 2-33, Nordin & Frankel (2001)
•In vivo, muscle
contraction can
exaggerate or
mitigate the effect
of external forces
Chronic Physical Activity
� ↑ bone density,
� ↑ compressive strength
� ↑ stiffness (to a certain threshold)
Chronic Disuse
� ↓ bone density (1%/wk for bed rest)
� ↓ strength
� ↓ stiffnessFig 2-47, Nordin & Frankel (2001)
Repetitive Physical Activity
Injury
cycle
Muscle Fatigue
↓↓↓↓ Ability to Neutralize Stresses on Bone
↑↑↑↑ Load on Bone
↓↓↓↓ Tolerance for Repetitions
Repetitive Physical Activity
Fig 2-38, Nordin & Frankel (2001)
Applications for Bone Injury
� Crack propagation occurs more easily in the
transverse than in the longitudinal direction
� Bending
� For adults, failure begins on tension side, since
tension strength < compression strength
� For youth, failure begins on compression side,
since immature bone more ductile
� Torsion
� Failure begins in shear, then tension direction
Effects of Age
� ↑ brittleness
� ↓ strength
� (↓ cancellous bone & thickness of cortical bone)
� ↓ ultimate strain
� ↓ energy storage
Effects of Age on Yield & Ultimate
Stresses (Tension)
100
110
120
130
140
150
160
170
180
20-29 30-39 40-49 50-59 60-69 70-79 80-89
Age (yrs)
Stress (MPa)
Femur - Yield Tibia - Yield Femur - Ultimate Tibia - Ultimate
Effects of Age on Eelastic (Tension)
10.0
15.0
20.0
25.0
30.0
35.0
20-29 30-39 40-49 50-59 60-69 70-79 80-89
Age (yrs)
Elastic Modulus (GPa)
Femur Tibia
0.000
0.005
0.010
0.015
0.020
0.025
0.030
0.035
0.040
0.045
20-29 30-39 40-49 50-59 60-69 70-79 80-89
Age (yrs)
Ultim
ate Strain
Femur Tibia
Effects of Age on Ultimate Strain (Tension)
2
2.5
3
3.5
4
4.5
5
5.5
6
20-29 30-39 40-49 50-59 60-69 70-79 80-89
Age (yrs)
Energy (MPa)
Femur Tibia
Effects of Age on Energy (Tension)
Properties of Biological Materials
A. Basic Concepts
B. Properties of Selected Biological Materials
A. Bone
B. Articular Cartilage
C. Ligaments & Muscle-Tendon Units
� Deforms more than bone since is 20X less stiff than bone� ↑ congruency
� High water content causes even distribution of stress
� High elasticity in the direction of joint motion and where joint pressure is greatest
� Compressibility is 50-60%
Tensile Properties: Cartilage
Ultimate
stress (MPa)
Modulus of
elasticity (GPa)
Strain to
Fracture (%)
Tension 4.41 - 10-100
Superficial 10-40 0.15-0.5 -
Deep 0-30 0-0.2 -
Costal 44 - 25.9
Disc 2.7 - -
Annulus 15.68 - -
Compressive Properties:
Cartilage
Ultimate
stress (MPa)
Modulus of
elasticity (GPa)
Strain to
Fracture (%)
Compression 7-23 0.012-0.047 3-17
Patella - 0.00228 -
Femoral head - 0.0084-0.0153 -
Costal - - 15.0
Disc 11 - -
Other Loading Properties:
Cartilage
Ultimate
stress(MPa)
Modulus of
elasticity (GPa)
Strain to
Fracture (%)
Shear
Normal - 0.00557-0.01022 -
Degenerated - 0.00137-0.00933 -
Torsion
Femoral - 0.01163 -
Disc 4.5-5.1 - -
Tension
From LeVeau (1992). Biomechanics of human motion (3rd ed.). Philadelphia: W.B. Saunders.
Properties of Biological Materials
A. Basic Concepts
B. Properties of Selected Biological Materials
A. Bone
B. Articular Cartilage
C. Ligaments & Muscle-Tendon Units
D. Skeletal Muscle
Structure and Function:
Architecture
� The arrangement
of collagen fibers
differs between
ligaments and
tendons. What is
the functional
significance?
Biomechanical Properties and
Behavior
� Tendons: withstand
unidirectional loads
� Ligaments: resist
tensile stress in one
direction and smaller
stresses in other
directions.
Viscoelastic Properties :
Rate Dependent Behavior
� Moderate strain-rate sensitivity
� With ↑ loading rate:
� Energy storage ↑ (↑ toughness)
� Rupture strength ↑
� Rupture strain ↑
� Stiffness ↑
Viscoelastic Properties:
Repetitive Loading Effects
Enoka (2002), Figure 5.3, p. 219, From Butler et al. (1978)
•↑ stiffness
Enoka (2002), Figure 5.3, p. 219, From Butler et al. (1978)
Idealized
Stress-Strain
for
Collagenous
Tissue
Very small
plastic
region
Ligamentum flavum
Nordin & Frankel (2001), Figure 4-10, p. 110, From Nachemson & Evans (1968)
Tensile Properties: Ligaments
Ultimate
stress (MPa)
Modulus of
elasticity (GPa)
Strain to
Fracture (%)
Nonelastic 60-100 0.111 5-14
ACL 37.8 - 23-35.8
Anterior
Longitudinal
.0123
Collagen 50 1.2 -
Viscoelastic Behavior of Bone-
Ligament-Bone Complex
� Fast loading rate:
� Ligament weakest
� Slow loading rate:
� Bony insertion of ligament weakest
� Load to failure ↓ 20%
� Energy storage ↓ 30%
� Stiffness similar
As loading rate ↑↑↑↑, bone strength ↑↑↑↑ more
than ligament strength.
Ligament-capsule injuries
� Sprains
� 1st degree – 25% tissue failure; no clinical instability
� 2nd degree – 50% tissue failure; 50%↓ in strength & stiffness
� 3rd degree – 75% tissue failure; easily detectable instabilty
� Bony avulsion failure (young people –more likely if tensile load applied slowly)
Tensile Properties:
Muscles & Tendons
Ultimate
stress (MPa)
Modulus of
elasticity (GPa)
Strain to
Fracture (%)
Muscle 0.147-3.50 - 58-65
Fascia 15 - -
Tendon
Various 45-125 0.8-2.0 8-10
Various 50-150 - 9.4-9.9
Various 19.1-88.5 - -
Mammalian 0.8-2
Achilles 34-55 - -
Enoka (2002), Figure 5.12, p. 227, From Noyes (1977); Noyes et al. (1984)
Enoka (2002), Figure 3.9, p. 134,
From Schechtman & Bader (1997)
EDL Tendon
ECRB Achilles
Max muscle force (N) 58.00 5000.0
Tendon length (mm) 204.00 350.0
Tendon thickness (mm2) 14.60 65.0
Elastic modulus (MPa) 726.00 1500.0
Stress (MPa) 4.06 76.9
Strain (%) 2.70 5.0
Stiffness (N/cm) 105.00 2875.0
Muscle-Tendon Interaction
� Stiffer tendon → more brisk, accurate movements
� Less stiff, ↓ muscle contraction velocity, ↑ efficiency
� ↑ tendon compliance, small ∆ muscle length (as
compared to ∆ M-T unit length
� High resilience
� Limited viscoelastic behavior, therefore, tendon in
major site of storage of elastic energy in M-T unit
� Tensile strength of tendon 2X that of its muscle
Role of Elasticity in Human
Movement
� Elasticity of tendon
� responsible for force transfer from muscle to
bone
� enables storage and release of energy, reducing
metabolic cost
� Material & structural properties of tendon
determine the amount of resistance to
stretch and, thus, amount of elastic force
transferred to bone
Muscle – Mechanical Stiffness
� Instantaneous rate of change of force with length
� Unstimulated muscles are very compliant
� Stiffness increases with tension
� High rates of change of force have high muscle
stiffness, particularly during eccentric actions
� Stiffness controlled by stretch and tendon reflexes
Effects of Disuse
Nordin & Frankel (2001), Figure 4-15a, p. 110, From Noyes (1977)
Effects of Disuse
Nordin & Frankel (2001), Figure 4-15b, p. 110, From Noyes (1977)
Effects of corticosteroids
� ↓ stiffness
� ↓ rupture strength
� ↓ energy absorption
� Time & dosage dependent
Effect of Structure
Whiting & Zernicke (1998), Figure 4.8a,b, p. 104, From Butler et al. (1978).
Miscellaneous Effects
� Age effects
� More compliant / less strong before maturity
� Insertion site becomes weak link in middle age
� ↓ stiffness & strength in pregnancy in rabbits
� Hormonal?
Summary
� Mechanical properties of biological materials vary across tissues and structures due to material and geometry differences.
� Understanding how age, physical activity, nutrition, and disease alter mechanical properties enables us to design appropriate interventions and rehabilitations.
� Understanding these mechanical properties allows us to design appropriate prosthetic devices to for joint replacement and repair.