Forces acting on bones and implants can cause fracture or implant failure. Bones experience compression, tension, bending, and torsional forces. Implants must resist these forces to provide stability for bone healing. Intramedullary nails share loading with bone to heal fractures. Nail properties like diameter, length, and material influence its bending stiffness and resistance to forces. Proper surgical technique including starting point, working length, and interlocking screws is needed for successful bone healing.
Measures of Dispersion and Variability: Range, QD, AD and SD
Biomechanics of Fracture and Fixation Justice 10.3.2005 (1).pptx
1.
2. ● Basic Concepts/Definitions
● Biomechanics of Intact/Healing Bone
● Biomechanics of Fracture
● Bone Healing
● Biomechanics of Implants: Avoiding
problems
3. Forces Acting on Long Bones
● Force is a vector
(magnitude with direction)
● Moment: Force acting on
a bone causing rotation
● Moment Arm: lever that
force acts on (some
distance away from center
of rotation)
6. Forces Acting on Construct
● Stress = Force/(Area
force is acting on)
= (normalized force)
● Strain = (Change in
Ht)/(Original Ht)
● Elastic Modulus =
Stress/Strain
= measure of stiffness
7. Deformation
● Elastic = if load is
removed material returns to
original shape
● Plastic = residual
deformation after load
removed
● Yield Point = load when
plastic deformation takes
place
● Work = Force x (distance
of bending)
● Toughness = Amt of work
req to Fx material
8. Implant Shape
● Moment of Inertia:
further away material
is spread in an object,
greater the stiffness
● Stiffness and strength
are proportional to
radius4
9. Fatigue
● Cyclic Loads below failure level progressive
cracks failure
● Stress Concentrator = radical change in shape
● Galvanic Corosion = Flow of electrons from (-) to
(+) in 2 dissimilar materials in conductive fluid
● Fretting = rubbing of 2 surfaces together
(removing oxidative layer)
● Crevice Corrosion = impurities in material
11. Viscoelasticity
● Increased resistance with
increased loading rate
● Creep = under constant load
soft tissue will continue to
gradually deform
● If compressive force is applied
slowly, syringe offers little
resistance
● Increased rate of force,
increased resistance to rate of
motion of syringe
12. Viscoelasticity
● Stress Relaxation: Applied
force with constant
displacement Decrease in
internal force as resistance
decreases
– resistance decreases as fluid is
forced from syringe
● Trabecular Bone: Trabecular
structure acts as elastic
component, Interstitial fluid
thru porous matrix is viscous
component
– Under higher loading rate there
is resistance to flow thus
increased internal pressure thus
increased stiffness of bone
13. Biomechanics Intact/Healing Bone
● Hierarchical structure
– Collagen embedded with
apatite
– Decreased modulus with
decreased apatite:collagen
ratio
● Fibrils organized to resist
force
– Fibers organized into
lamellae
– Concentric Lemellae make an
Osteon
14. Strength/Stiffness
● Strength proportional to
density2
● Modulus proportional to
density(2 to 3)
● Age: increased modulus,
bending strength from child
to adult, then decrease
● Holes/defects weaken bone
(round better than square)
● Strength proportional to
diameter4
15. Biomechanics of Bone Fx
● Weakest in Tension,
Strongest in
Compression
● Pure Bending
Transverse Fx
● Torsion Spiral
Fx
● Shear Oblique
Fx
● Butterfly due to Bend
+ Shear
16. ● Smaller cross section of
bone fails 1st (distal 1/3 of
tibia)
● Osteoperosis
– decreased density of
trebecular bone
– decreased endosteal
thickness of cortical bone
17. Bone Healing
● Direct
– Primary bone healing
– Cutting cones
– Seen with absolute stability
● Indirect
– Secondary bone healing
– Callus formation; resorption at fx site;
– Seen with relative stability
20. Relative Stability
● Motion between fracture fragments that is
compatible with fracture healing.
● Motion is below the critical strain level of tissue
repair.
● Promotes indirect bone healing!
● Examples:
– IM nails
– Bridge plate
– External Fixator
21. Absolute Stability
● Compression of two anatomically reduced
fracture fragments.
● No displacement of the fracture under
functional load.
● Promotes direct bone healing!
● Examples:
– Lag screw
– Plate => compression, buttress, neutralization
– Tension band
22. Biomechanics of Implants:
Avoiding Problems
● Cerclage Wire: strength proportional to
diameter
– Solid wire sensitive to scratch/notch (cable
better)
– Optimal # of turns 4-8 when twisted
23. Screw fixation
● Rotary forces compression between
objects (inclined plane on spiral pulls object
toward head)
● Four part construction: head, shaft, thread,
tip
● Thread defined by root diameter, thread
diameter, pitch
24. Screws
● Larger core diameter has
higher resistance to fatigue
& shear failure
– 4th power of the diameter
● Pullout strength (maximum
force screw can support along
its axis)
– outer diameter, length of
engagement, shear
strength/density of bone
25. Screws
● Tapping
– increase compressive forces,
decrease interface friction
● Cyclic Loading: If plate is
not tight enough to bone
– Force transferred to long axis
of screw
– Stress corrosion of plate
rubbing
26. Plates & Bending failure
● Leaving gap opposite plate
makes it a fulcrum
● increased stress at holes
● avoid holes over fracture sites
● greater the span between
screws
– less stiff
– more bending
28. Femoral Nail
● Contact Forces expand
femur (hoop stresses)
may cause it to split if
too large
● Starting hole: too
medial, too anterior
● Initial curve of IM rod,
rod stiffness
29. Femoral Nail
● Distal Fx:
– Longer moment arm of external force
thus greater bending moment in rod
– Greatest area of stress in rod (Fx site)
is near screw holes (stress riser)
– Locking screw supported only by
cortices
● Stiffness & strength to bend decrease with
length3
● Possible to nick border of rod hole
w/ screw accentuate fatigue
30. Ex-Fix
● Self-tapping pins local heat
thermal necrosis & microcracking
(thus corrosion/fatigue)
● Pin Micromotion bone
resorption at interface
– Undersize hole 0.1 mm decr
micromotion
– Undersize >0.3 mm incr
microcracking
31. Ex-Fix
● Deformation of Pin or Side Bar
– Stiffness & Strength proportional to diameter4
– Stiffness & Strength inversely proportional to lenght3
● To increase strength:
– Decrease sidebar to bone distance
– Increase pin diameter
– Put pins closer to fracture
– Increase # of sidebars
– Bury pin thread completely within cortex
● Add Sidebar at 90 degree plane also resist torsion
43. Intramedullary Nails
● “Internal Splint”, Load Sharing
● Nail itself should resist bending and torsion
● The bone should resist axial loading
● Strength => wall thickness, diameter, and
material
● stiffness => 4th power of the diameter
● Type of fracture –transverse, oblique, or
complex determines some stability
44. Intramedullary Nails
● Working length is area that spans fracture
between points of fixation.
● In bending, stiffness inversely proportional
to square of length
● Torsional rigidity is inversely proportional
to length
45. Intramedullary Nails
● Gripping strength is resistance to slipping at
bone-implant interface. Increased by
increasing cortical contact.
● Nail can twist or slip with torsional loading
which allows angulation
Stress removes shape/size
Strain measures deformation
Elastic modulus = stiffness higher modulus is stiffer (less flexible)
Structural properties = properties of fixation + bone
Material properties = properties of individual material
Elastic range is “working range” of device
2 most important factors of a device are Yield point and Stiffness (Elastic Modulus)
Material may have different stiffness or yield under forces in different directions
Work = Area under force displacement curve
May be flexible and tough or Stiff but brittle
Stress Concentrators = screw holes, where thread meets shank on a screw, scratches=Stress Riser
- Round hole less of change than sharp corner of square hole
A = crevice corrosion (impurity)
B = Stress Corrosion = fatigue + galvanic (b/w oxidative layer and underlying material)
C = Fretting = Rubbing of screw on hole
D = Galvanic in scratch/pit in plate
Metal materials under constant load deform immediately and then remain deformed until load is removed
Think of stretching soft tissue as stretching 2 components:
Spring – immediate elasticity of tissue (immediately compresses)
Syringe – syringe plunger displaces as it moves fluid thru orrifice (viscous creep)
Callus increases apatite as fracture heals
Initial callus disorganized becomes more organized
Fibers weakest when force is parallel with cement lines
As defect increases to 30% of diameter strength decreses to 50% of intact bone
As diameter increases in callus, strength increases with diameter4
As callus develops, mineralization, organization, density, and diatmeter all increase thus increased strength and stiffness
Tension Side fails 1st
Torsion: Progressive failure in elongation/tension of fibers on surface
Shear: compressive load in diagonal (bone is weaker in diagonal than pure compression)
Pure Compression: comminution of metaphysis (trebecular bone of metaphysis weaker than cortical bone of diaphysis(less dense))
Strength proportional to density squared
Decresed thickness decreased moment of inertia
Inflammation:
-hematoma/inflmmatory exudate from ruptured blood vessels
-bone necrosis at fracture ends
-vasodil/hyperemia surrounding soft tissue
-ingrowth of capillariescell prolif (PMN, macrophage, fibroblasts)
-fibrin/reticulin fibril network
-granulation replaces hematoma, osteoclasts remove necrotic bone
Soft:
-fragments no longer freely moving
-stability adequate to prevent shortening, angulation can still occur
-incr vascularity, capillary ingrowth, cells
-new bone starts subperiosteally
-chondroblasts appear in callus b/w bone fragments
Hard:
-soft callus is converted by enchondral ossification & intramembranous bone formation
-bony callus starts at areas remote from Fx (mechanically idle), progresses toward Fx
-Enchondral ossification periosteally & Intramembranous bone formation periosteally & endosteally
-Bony bridging at periphery of callus & endosteal bone
Remodelling:
-begins once Fx is solidly united
-lasts until completely returned to original morphology
-woven bone slowly replaced by lamellar bone
Large strain granulation tissue
Intermediate strain cartilage
Small strain direct bone formation with limitted callus
Tapped: 65% torque creates compression, Untapped: 5% compression
Not tapping cancellous bone improves pullout strength: tapping removes material (cancellous bone is already porous)
10-15% less force than max screw tightnessfails <1000 cycles (nl is 2.5 million cycles)
Place on tension side
Distal locking screw gets no support from trabecular bone 3 point bending of screw increased moment arm for longer screw