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The Science of Biomechanics and It’s Practical Application
Primerus – 2016 PPII Winter ConferenceFebruary 24-27, 2016
Delray Beach, FL
Mariusz Ziejewski, Ph.D., InżProfessor
Director of Impact Biomechanics Laboratory, College of Engineering
Director of Automotive Systems Laboratory, College of Engineering
Mechanical Engineering Department
North Dakota State University
and
Adjunct Associate Professor
Department of Neuroscience, School of Medicine
University of North Dakota
Who We Are
Founded in 2003
Mission
The mission of the NABISis to move brain injury science into practice.
VisionNABIS is the pre-eminent society for professionals involved in
state-of-the-art brain injury research, education and treatment.
A Society of Multidisciplinary Brain Injury Professionals
WHO WE ARE
Founded in 2003
MissionThe mission of the NABIS
is to move brain injury science into practice.
VisionNABIS is the pre-eminent society for professionals involved in
state-of-the-art brain injury research, education and treatment.
A Society of Multidisciplinary Brain Injury Professionals
Who We Are
Founded in 2003
MISSION
The mission of the NABISis to move brain injury science into practice.
VisionNABIS is the pre-eminent society for professionals involved in
state-of-the-art brain injury research, education and treatment.
A Society of Multidisciplinary Brain Injury Professionals
Who We Are
Founded in 2003
Mission
The mission of the NABISis to move brain injury science into practice.
VISIONNABIS is the pre-eminent society for
professionals involved in state-of-the-art brain injury research, education and treatment.
A Society of Multidisciplinary Brain Injury Professionals
A Society of Multidisciplinary Brain Injury Professionals
WHAT WE BRING TO THE TABLE
Continuing EducationThe largest annual conference for multidisciplinary brain injury
professionals in North America (avg. over 400 attendees)
Information ResourcesBrain Injury Professional, the largest circulation of any professional
publication on brain injury (over 6000 copies distributed per issue)
ExpertiseTransdisciplinary expertise across the lifespan to promote life quality through research, treatment, service delivery and advocacy efforts
(over 350 active members)
A Society of Multidisciplinary Brain Injury Professionals
WHAT WE BRING TO THE TABLE
CONTINUING EDUCATIONThe largest annual conference for
multidisciplinary brain injury professionals in North America
(avg. over 400 attendees)
Information ResourcesBrain Injury Professional, the largest circulation of any professional publication on
brain injury (over 6000 copies distributed per issue)
ExpertiseTransdisciplinary expertise across the lifespan to promote life quality through
research, treatment, service delivery and advocacy efforts(over 350 active members)
A Society of Multidisciplinary Brain Injury Professionals
WHAT WE BRING TO THE TABLE
Continuing EducationThe largest annual conference for multidisciplinary brain injury professionals in
North America (avg. over 400 attendees)
INFORMATION RESOURCESBrain Injury Professional, the largest circulation of
any professional publication on brain injury (over 6000 copies distributed per issue)
ExpertiseTransdisciplinary expertise across the lifespan to promote life quality through
research, treatment, service delivery and advocacy efforts(over 350 active members)
A Society of Multidisciplinary Brain Injury Professionals
WHAT WE BRING TO THE TABLE
Continuing EducationThe largest annual conference for multidisciplinary brain injury professionals in North America
(avg. over 400 attendees)
Information ResourcesBrain Injury Professional, the largest circulation of any professional publication on brain injury
(over 6000 copies distributed per issue)
EXPERTISETransdisciplinary expertise across the
lifespan to promote life quality through research, treatment, service delivery and
advocacy efforts(over 350 active members)
Chairman
Mariusz Ziejewski, PhD
Vice Chairman
Debra Braunling-McMorrow, PhD
Secretary
Brian Greenwald, MD
Treasurer
Bruce Stern, Esq.
Family Liason
Skye MacQueen
A Society of Multidisciplinary Brain Injury Professionals
Board of Directors
Michael Davis, CBIST
Sharon Grandinette, M.S., Ed. CBIST
Harvey E. Jacobs, PhD, CLCP
Brent Masel, MD
Jonathan Silver, MD
Louis Siracusano, Esq.
Tina Trudel, PhD
Barry Willer, PhD
Alan Weintraub, MD
THE 2015-2017 NABIS BOARD OF DIRECTORS
To learn more or to join NABIS, visit: www.nabis.org
Involvement with Department of Defense
Researcher:
1. Current, $600,000 grant, “Blast Pressure Gradients and Fragments on Ballistic Helmets and the Head and Brain Injury – Simultaneous MultiscaleModeling with Experimental Validation,” Department of the Army, US Army Research, Development and Engineering Command (2010-2013)
2. Current, $500,000 grant, “Blast and the Consequences on Traumatic Brain Injury – Mulitscale Mechanical Modeling of Brain” Air Force Office of Scientific Research, (2007-2010)
Chair:
1. Chairman, Scientific Peer Review Panel, “Physics of Blast as it relates to Brain Injury”, Intramural proposals, DoD PTSD/TBI Research Program, Congressionally Directed Medical Research Program (CDMRP). (Nov. 2007)
2. Chairman, Scientific Peer Review Panel, “Physics of Blast as it relates to Brain Injury”, Extramural proposals, DoD PTSD/TBI Research Program, CDMRP. (Dec. 2007)
Reviewer:
1. Reviewer, Proposals for the Military Operational Medical Research Program, US Army Materiel Research Command (USAMRMC) (May 2010)
2. Reviewer, Proposals for the Military Operational Medical Research Program, US Army Materiel Research Command (USAMRMC) (April, 2010)
3. Reviewer, Intramural Proposals for the Department of Defense (DoD) Defense Medical Research and Development Program, Intramural Applied Research and Advanced Technology Development Award (Nov. 2009)
4. Reviewer, Proposals for the Military Operational Medical Research Program, US Army Materiel Research Command (USAMRMC).(Oct., 2008)
5. Reviewer, Intramural Proposals for the Department of Defense (DoD) Intramural War Supplement Program.(Nov.,2008)
6. Reviewer, Scientific Peer Review Panels, Concept Proposals related to brain injuries caused by blasts for the DoD (PTSD/TBI) Research Program, CDMRP. (Oct., 2007)
7. Reviewer, Scientific Peer Review Panels, Intramural Proposals on Clinical Diagnosis related to brain injuries caused by blasts for the DoD(PTSD/TBI) Research Program, CDMRP. (Nov., 2007)
Invited Faculty:
1. Invited Faculty, Invited by former US Air Force Surgeon General P.K. Carlton to make a presentation on the Physics of Blast Injury to a specialconference/think tank session on allocation of Department of Defense (DoD) funding for TBI/blast injuries.
2. Invited Faculty, National Veteran’s Health Administration/Department of Defense (VHA/DoD) Conference: “Visual Consequences of Traumatic Brain Injury.”
3. Invited Faculty, National Veteran’s Health Administration/Department of Defense (VHA/DoD) Conference: “Sensory Impairment Issues in Traumatic Brain Injury.”
~ 7000 Human TestsMaximum Acceleration: 80 G
Maximum Velocity: 17 m/s
Pulse Duration: 40-180 ms
AFRL/HEPA Vertical Deceleration Tower
~ 900 Tests Analyzed with Humans
Six (6) Research Contracts, 1996-2010
Biofidelity of Hybrid II head/neck research
AFRL/HEPA Vertical Deceleration Tower
Direction of Our Research (Sponsored by DoD)
Multiscale modeling method proposed for brain cell adhesion modeling:
(a) MD (molecular dynamics)Simulation of Cell-ECM (extracellular matrix)interaction
(b) Average traction-separation data from MD simulation
(c) Axon- ECM continuum modeling of the interface
(d) Undulated RUC (repeating cell unit) of brain material and fiber reinforced composite modeling of the tissue
(e) Micromechanics modeling of RUC under different load cases for material characterization
BIOMECHANICS
“… the application of the principles and techniques of mechanics to the structure, functions and capabilities of
living organisms.”
Webster’s New World Dictionary of the American Language Ed. David B. Guralnik. 2nd College Ed. New York: World Pub. Co., 1970
“…evaluation based on
mechanism (cause) of injury.
Such an approach relies on
knowledge of the typical
physical and psychological
sequelae associated with a
particular mechanism of injury
to guide patient assessment
and treatment.”
Scott S., H. Belanger, R. Vanderploeg, J. Massengale, J. Scholten “Mechanism-of-Injury Approach to Evaluating Patients With Blast-Related Polytrauma”,
Journal of American Osteopathic Association Vol. 106, No.5, May 2006 pp. 265-270
Injury Exceeds Juror Expectations
Some people get hurt in a collision and
others do not get hurt in the same collision.
?
Each collision for each individual has its own
unique set of parameters that
control the outcomeof the impact.
We must incorporate all the significant
parameters cumulatively in a case
specific analysis.
PROVING THE CASE THROUGH
SCIENCEThe CSI Effect
Biomechanical Evaluation
ADVANTAGES:• Event specific• Unlimited resolution• Time History
DISADVANTAGES:• Accuracy of information• Accuracy of the software
To compliment the medical diagnosis of TBI
Biomechanical Engineer and
Nuclear Medicine
Top-Horizontal View
Ziejewski, M., G. Karami, W. Orrison, E. Hanson, “Dynamic Response of Head Under Vehicle Crash Loading,” 21st International Technical Conference on Enhanced Safety of Vehicles, Sponsored by Mercedes Benz and the National Highway Traffic Safety Admiistration (NHTSA), Stuttgart, Germany June 15-18th, www.nrd.nhtsa.dot.gov, SAE International, Head Injury Biomechanics, Vol. 1 P 144-187, 2011
Biomechanical MRI
Mid-Sagittal View
Biomechanical MRI
Ziejewski, M., G. Karami, W. Orrison, E. Hanson, “Dynamic Response of Head Under Vehicle Crash Loading,” 21st International Technical Conference on Enhanced Safety of Vehicles, Sponsored by Mercedes Benz and the National Highway Traffic Safety Admiistration (NHTSA), Stuttgart, Germany June 15-18th, www.nrd.nhtsa.dot.gov, SAE International, Head Injury Biomechanics, Vol. 1 P 144-187, 2011
What Biomechanics Can Do in Your Case
1. Explain what happened in the accident
2. Connect the collision to the injuries
3. Determine whether or not the collision was sufficient to cause traumatic brain injury (probability over 50%)
4. Case specific probability of TBI (95%???)
5. Identify the risk factors
Biomechanical EvaluationIdentify and Quantify Risk Factors
• Impact Force (Magnitude, direction, time duration)
• Gender
• Body Position
• Pre-existing Conditions
• Etc..
28
• Impact Force (Magnitude, direction, time duration)
• Gender
• Body Position
• Pre-existing Conditions
• Etc..
29
Biomechanical EvaluationIdentify and Quantify Risk Factors
• Impact Force (Magnitude, direction, time duration)
• Gender
• Body Position
• Pre-existing Conditions
• Etc..
30
Biomechanical EvaluationIdentify and Quantify Risk Factors
• Impact Force (Magnitude, direction, time duration)
• Gender
• Body Position
• Pre-existing Conditions
• Etc.
31
Biomechanical EvaluationIdentify and Quantify Risk Factors
Demonstrate the vulnerability
of the human brain
Relative Motion of the Brain
Relative Motion of the Brain
Because:
3D Dynamic Response Micro Damage
Relative Motion of the Brain
Because:
3D Dynamic Response Micro Damage
36
(Panjabi et al., 2001)
Relative Motion of the Brain
Because:
3D Dynamic Response Micro Damage
(a)(b)
Countercoup
(C, D)
Coup
(A, B)
Extremely Dynamic Oscillation of the Brain Tissue
.0002s
Ziejewski, M. and Karami, G. , “Biomechanical Perspective on Blast Injury,” in Concussive Brain Trauma: Neurobehavioral Impairment and Maladaptation by Dr. Rolland Parker, Taylor & Francis Group, Boca Raton, FL, 2012
Brain Oscillation
Relative Motion of the Brain
Because:
3D Dynamic Response Micro Damage
VEHICLEDYNAMICS ANALYSIS
HUMAN BODYDYNAMICS ANALYSIS
HUMAN TOLERANCEANALYSIS
The significant parameters of the collision include, but are not limited to:
A. Severity of Vehicle Dynamics
• Δv (Change in velocity)
• PDOF (Direction of impact)
• Δt (Duration of impact)
B. Severity of Human Body Dynamics
• Gender
• Height
• Weight
• Body position
• Vehicle interior characteristics
• Individual tolerances
VEHICLEDYNAMICS ANALYSIS
HUMAN BODYDYNAMICS ANALYSIS
INJURY MECHANISMS
Newton’s 2ND Law
(acceleration)
F = m . a(Force) (mass)
(acceleration)
F = m .(Force) (mass)
V t
What is Delta-V (V)?
TIME
VEL
OC
ITY
Pre-Impact
Post-Impact
Severity of Collision for Specific Δt
Impact (Delta V, ΔV)
Linder, A., et al. “Change of Velocity and Pulse Characteristics in Rear Impacts: Real World and Vehicle
Tests Data.” 18th ESV Conference, Paper #285, 2003.
100 – 120 ms
Heinrichs, B., J. Lawrence, B. Allin, J. Bowler, C. Wilkinson, K. Ising and D. King. Low-Speed Impact Testing of Pickup Truck
Bumpers Society of Automotive Engineers, Inc. 2001.
7.5 mph
60 ms
100 ms
A
t = 2.5 ms
Simulation Test
Dynamic Progressive Buckling
•Ziejewski, M., B. Anderson, M. Rao and M. Hussain, “Energy Absorption for Short Duration Impacts,” SAE Paper #961851, Indianapolis, IN, 1996•Ziejewski, M., B. Anderson, “The Effect of Structural Stiffness on Occupant Response For A -Gx Acceleration Impact,” SAE Paper #962374, São Paulo, SP, Brazil, 1996•Ziejewski, M., H. Goettler, “Effect of Structural Stiffness and Kinetic Energy on Impact Force,” SAE Paper #961852, Indianapolis, IN, 1996•Anderson, B., M. Ziejewski, H. Goettler, “Method to Predict the Energy Absorption Rate Characteristics for a Structural Member,” Society of Automotive Engineers (SAE) Paper #982388, Detroit, MI, 1998•Pan, X., M. Ziejewski, H. Goettler, “Force Response Characteristics of Square Columns for Selected Materials at Impact Loading Combinations Based on FEA,” SAE Paper #982418, Detroit, MI., 1998
Uniqueness of the Loading Conditions
μs
(kPa
)
• Supersonic overpressurization shockwave• Timescale in μs (microseconds) • 1atm ≈ 100 kPa
Uniqueness of the Loading Conditions
(kP
a)
μs
(kP
a)
• Supersonic overpressurization shockwave• Timescale in μs (microseconds) • 1atm ≈ 100 kPa
Time Matters
∆V = 7.5 mph
∆t = 120 ms aaverage= 2.8 g apeak= 5.7 g
∆t = 60 ms aaverage= 5.7 g apeak= 11.4 g
∆t = 2.5 ms aaverage= 136.6 g apeak= 273.2 g
VEHICLEDYNAMICS ANALYSIS
HUMAN BODYDYNAMICS ANALYSIS
INJURY MECHANISMS
RAPID HEAD VELOCITY CHANGE
BRAIN DEFORMATION
BRAIN DAMAGE
→LINEAR→ANGULAR
→LINEAR→ANGULAR
→CHANGE IN SHAPE→CHANGE IN VOLUME
→STRESS→STRAIN→INTERCRANIAL PRESSURE
APPLICATION OF FORCE
54
ENGINEERING PARAMETERS
INJURY QUANTIFICATION
YESYES
YESYES
--
--YES
Mechanical Properties of Brain Tissue
• Incompressible (High resistance to change in size, high bulk modulus)
• Deformable (Low resistance to change in shape, low shear modulus)
• Heterogeneous (Different properties within the brain)
• Anisotropic (Different properties in different directions)
• Viscoelastic (Time dependent properties: magnitude, duration, rate of change)
Mechanical Properties of Brain Tissue
• Incompressible (High resistance to change in size, high bulk modulus)
• Deformable (Low resistance to change in shape, low shear modulus)
• Heterogeneous (Different properties within the brain)
• Anisotropic (Different properties in different directions)
• Viscoelastic (Time dependent properties: magnitude, duration, rate of change)
B.R. Donnelly and J. Medige, “Shear Properties of Human Brain Tissue,” Journal of Biomechanical Engineering, Nov. 1997, Vol. 119, 423-432. Shames, I.H. and Cozzarelli, F.A., 1992, Elastic and Inelastic Stress Analysis, New Jersey: Prentice Hall, Englewood Cliffs, NJ
Incompressible/Deformable
• Bulk modulus is approximately 105 (100,000) times larger than shear modulus.
• Deformation of brain tissue can be assumed to depend on shear modulus only.
• This behavior is common with viscoelasticmaterials (Shames and Cozzarelli, 1992)
Mechanical Properties of Brain Tissue
• Incompressible (High resistance to change in size, high bulk modulus)
• Deformable (Low resistance to change in shape, low shear modulus)
• Heterogeneous (Different properties within the brain)
• Anisotropic (Different properties in different directions)
• Viscoelastic (Time dependent properties: magnitude, duration, rate of change)
Mechanical Properties of Brain Tissue
• Incompressible (High resistance to change in size, high bulk modulus)
• Deformable (Low resistance to change in shape, low shear modulus)
• Heterogeneous (Different properties within the brain)
• Anisotropic (Different properties in different directions)
• Viscoelastic (Time dependent properties: magnitude, duration, rate of change)
Demonstration
Slow Application of Force
Rapid Application of Force
• macro scale (mm) (10-3 m) – MRI detection limit – Fig. A, B, C• Diffusion Tensor Imaging (DTI) – 1x1x5 mm3
• Susceptibility Weighted Imaging (SWI) – 0.2x0.2x0.2 mm3
• micro scale (μm) (10-6 m) – the cell – Fig. D• MR Microscopy (MRM) – 100 μm3, 7 – 9.4 Tesla• Performed only on autopsied brain
• nano scale (nm) (10-9 m) – the axon neural filaments – Fig. E• Electron microscope to visualize
Invisible Injury – Why?
•Carpenter, M., Human Neuroanatomy. Baltimore, MD: Williams and Wilkins, 1976•Williams TH, Gluhbegovic N. Jew JY. The human brain: dissections of the real brain. Virtual Hospital, University of Iowa, 1997; www.vh.org/Providers/Textbooks/BrainAnatomy and www.brain-iniversity.com [21/10/22]•Callot, et. al, Short-scan-time multi-slice diffusion MRI of the mouse cervical spinal cord using echo planar imaging, NMR in Biomedicine, 2008
Accelerometer
TYPES OF ACCELERATION
Ax = Linear Acceleration, Forward-Backward DirectionAy = Linear Acceleration, Side to Side Direction
Az = Linear Acceleration, Vertical Direction
a x = Rotational Acceleration, About Forward-Backward Axis
a y = Rotational Acceleration, About Side to Side Axis
a z = Rotational Acceleration, About Vertical Axis
Linear Acceleration
Rotational Acceleration
Y
X
Z
TYPES OF ACCELERATION
Ax = Linear Acceleration, Forward-Backward DirectionAy = Linear Acceleration, Side to Side Direction
Az = Linear Acceleration, Vertical Direction
a x = Rotational Acceleration, About Forward-Backward Axis
a y = Rotational Acceleration, About Side to Side Axis
a z = Rotational Acceleration, About Vertical Axis
Linear Acceleration
Rotational Acceleration
Z
Y
X
TYPES OF ACCELERATION
Ax = Linear Acceleration, Forward-Backward DirectionAy = Linear Acceleration, Side to Side Direction
Az = Linear Acceleration, Vertical Direction
a x = Rotational Acceleration, About Forward-Backward Axis
a y = Rotational Acceleration, About Side to Side Axis
a z = Rotational Acceleration, About Vertical Axis
Linear Acceleration
Rotational Acceleration
Y
Z
X
TYPES OF ACCELERATION
Ax = Linear Acceleration, Forward-Backward DirectionAy = Linear Acceleration, Side to Side Direction
Az = Linear Acceleration, Vertical Direction
a x = Rotational Acceleration, About Forward-Backward Axis
a y = Rotational Acceleration, About Side to Side Axis
a z = Rotational Acceleration, About Vertical Axis
Linear Acceleration
Rotational Acceleration
Y
X
Z
TYPES OF ACCELERATION
Ax = Linear Acceleration, Forward-Backward DirectionAy = Linear Acceleration, Side to Side Direction
Az = Linear Acceleration, Vertical Direction
a x = Rotational Acceleration, About Forward-Backward Axis
a y = Rotational Acceleration, About Side to Side Axis
a z = Rotational Acceleration, About Vertical Axis
Linear Acceleration
Rotational Acceleration
Y
X
Z
TYPES OF ACCELERATION
Ax = Linear Acceleration, Forward-Backward DirectionAy = Linear Acceleration, Side to Side Direction
Az = Linear Acceleration, Vertical Direction
a x = Rotational Acceleration, About Forward-Backward Axis
a y = Rotational Acceleration, About Side to Side Axis
a z = Rotational Acceleration, About Vertical Axis
Linear Acceleration
Rotational Acceleration
Y
X
Z
TYPES OF ACCELERATION
Ax = Linear Acceleration, Forward-Backward DirectionAy = Linear Acceleration, Side to Side Direction
Az = Linear Acceleration, Vertical Direction
a x = Rotational Acceleration, About Forward-Backward Axis
a y = Rotational Acceleration, About Side to Side Axis
a z = Rotational Acceleration, About Vertical Axis
Linear Acceleration
Rotational Acceleration
Y
X
Z
TYPES OF ACCELERATION
Ax = Linear Acceleration, Forward-Backward DirectionAy = Linear Acceleration, Side to Side Direction
Az = Linear Acceleration, Vertical Direction
a x = Rotational Acceleration, About Forward-Backward Axis
a y = Rotational Acceleration, About Side to Side Axis
a z = Rotational Acceleration, About Vertical Axis
Linear Acceleration
Rotational Acceleration
Y
Z
X
4. External vs. Internal Injuries
Comparison of Pressure Contours on Brain and Skull
T=3.2ms
T=4.2ms
A. Angular Acceleration (1 of 3):
B. Linear Acceleration (1 of 3):
+
-
74
Angular Acceleration of the head has an effect on the entire brain
Equipment
Skull/Gel Model• Skull: A20/1
(Anatomical Chart Company; Hagerstown, MD)
• Gel: Sylgard 527 A&B Silicon Dielectric Gel(Dow Corning Corporation; Midland, MI)
Subject Seat• 1997 Ford F250
(VIN: 1FT HW26F 8 VE A67707)
Accelerometer• Type: ICSensors 3028
• Range: +/- 100g
• Serial Number: 0021-029
High Speed Camera• MotionScope®, Redlake Imaging
• Model: PCI 2000
• Model Number: 1108-0004
• Serial Number: 98P-0095
Skull: A20/1(Anatomical Chart Company; Hagerstown, MD)
Equipment
9hr cure 14hr cure
12hr cure
Silicon Gel PropertiesSylgard 5-27 A&B Silicon Dielectric Gel
(Dow Corning Corporation; Midland, MI)
Equipment
Brands, D., P. Bovendeered, G. Peter, et al. “Comparison of the Dynamic Behaviour of Brain Tissue and Two Model Materials”, SAE
99C21, Society of Automotive Engineers, Inc. 1999.
Properties Comparison Silicon Gel & Brain Tissue
0
2
4
6
8
10
12
14
0 0.01 0.02 0.03 0.04 0.05
Time(Sec)
Lin
ea
r A
cc
ele
rati
on
(G)
14.09g 10.55g
A. SEVERITY OF IMPACT
B. POSITION OF HEAD
75º
Simulation Experimental
Simulation Experimental 75º75º
Test Conditions (per ATB Simulation)
Skull/Gel Model Testing
• Severity of Impact (X = 10.10g, Y = 14.09g, Z = 4.02)•Tested at Y = 10.55g •Position of Head (Yaw 75º, Pitch 7º, Roll 6º)
Test Conditions (per ATB Simulation) :
Video Parameters:• Capture rate: 10,000 frames/sec• Slow motion (1/60th of actual velocity)
Skull/Gel Model Testing
• Severity of Impact (X = 10.10g, Y = 14.09g, Z = 4.02)•Tested at Y = 10.55g• Position of Head (Yaw 75º, Pitch 7º, Roll 6º)
Test Conditions (per ATB Simulation) :
Video Parameters:• Capture rate: 10,000 frames/sec• Slow motion (1/60th of actual velocity)
Transformed MRI Data
Source of Original Data:
• Dr. Orrison, Nevada Imaging Centers
Skull/Gel Model Testing
• Severity of Impact (X = 10.10g, Y = 14.09g, Z = 4.02)•Tested at Y = 10.55g• Position of Head (Yaw 75º, Pitch 7º, Roll 6º)
Test Conditions (per ATB Simulation) :
Video Parameters:• Capture rate: 10,000 frames/sec• Slow motion (1/60th of actual velocity)
Transformed MRI Data
Source of Original Data:
• Dr. Orrison, Nevada Imaging Centers
Approach
Rebound
Dynamic Pattern at Impact
The Head Model simulates all essential anatomical features of a male head, including the brain, falx and tentorium, CSF, dura mater, pia mater, skull and scalp.
Finite Element Modeling of the Human Head- Continuum Scale(Model currently used in Military Brain Trauma Analysis)
(US Department of Defense Research)
M Sotudeh Chafi, V Dirisala, G Karami, and M Ziejewski, A finite element method parametric study of the dynamic response of the human brain with different
cerebrospinal fluid constitutive properties, Proc. IMechE Part H: J. Engineering in Medicine, 2009; 223, 1003-101984
Variation of ICP and Shear Stress on the Brain with time
ICP
Shear
Stress
2.9
ms4.9
ms
4 ms
7 ms4.9
ms
3 ms
(kPa
)
• Supersonic overpressurization shockwave (>300m/s)
• Pressure increased to 10-100 MPa (1atm ≈ 100 kPa)
• Timescale in μs (microseconds)
Automotive Blast
Cavitation
Scanning Electron Micrograph
Crater
Brass Plate
Cavitation
Liquid Jet
~ 1 mm
Scanning Electron Micrograph
Crater
Brass Plate
Cavitation
Liquid Jet
~ 1 mm
CAVITATION DAMAGE
Macroscale
A. Spherical Bubble Collapse
B. Non-Spherical Bubble Collapse
Bubble Collapse
(Classical Approach)NanoscaleBubble Inception
(New Brain Injury Mechanism)
Liquid Jet
MassSpring
Fracture Point
Recoil pressure waves
MassSpring
VEHICLEDYNAMICS ANALYSIS
HUMAN BODYDYNAMICS ANALYSIS
INJURY MECHANISMS
Human Tolerance to Impact Conditions as Related to Motor Vehicle Design, SAE International, Revised Dec. 2003, SAE J885, Temporo-Parietal Bone p13.
Mean: 1910 lb Min: 1050 lb
Skull Fracture Research
Prasad, P., et al., (1985). The Position of the United States Delegation to the ISO Working Group on the Use of HIC in the
Automotive Environment. Ford Motor and G M Corp. SAE 851246
16%
25%
Prasad, P., et al., (1985). The Position of the United States Delegation to the ISO Working Group on the Use of HIC in the Automotive Environment. Ford Motor and G M Corp. SAE 851246
•Depreitere, B., Van Lierde, C., Vander Sloten, J., Van Audekercke, R., Van Der Perre, G., Plets, C., Goffin, J. (2006). Mechanics of acute subdural hematomas resulting from bridging vein rupture, Journal fo Neurosurgery, Vol. 104, J Neurosurg 104.
10,000rad/sec2
Tolerance Level:
Subdural Hematoma
Pulse Duration:
Shorter than: 10 ms
•Bandak, F., Eppinger, R. (1994). A Three-Dimensional Finite Element Analysis of The Human Brain Under Combined Rotational and Translational Accelerations, National Highway Traffic Safety Administration (NHTSA), SAE 942215.
Biomechanical Analysis Outcomes
1. Visualization of injury (beyond MRI’s)
• Resolution for MRI 0.25mm macroscale (10-3 m)• Details of biomechanic modeling nanoscale (10-9 m)
2. Mechanism of injury (beyond the current understanding)• Extremely dynamic oscillation of the brain tissue• Nanoscale Cavitation (New Brain Injury Mechanism)
3. Benefits• Current patients (location, extent of injury)• Prevention (protective systems, helmet)
6. Male vs.
Female
Quinlan, K., J. Annest, B. Myers, et.al. “Neck strains and sprains among motor vehicle occupants”,
Accident Analysis and Prevention 36, 2004.
~ 7000 Human TestsMaximum Acceleration: 80 G
Maximum Velocity: 17 m/s
Pulse Duration: 40-180 ms
AFRL/HEPA Vertical Deceleration Tower
M. Ziejewski and E.M. Yliniemi, “Prediction of Head Acceleration and Neck Loading in Vertical Impact”, The Impact of Technology on Sport III, 2009.
1.4 x
138 Tests
Female
Male
6.8 g
5.0 g
1.8 X
6mph
Female
Male
12g
6.5g
Hell W., S. Schick, and K. Langwieder “Biomechanics of Cervical Spine Injuries in Rear End Car Impacts: Influence of Car Seats and Possible Evaluation Criteria”, Traffic Injury Prevention, 2002.
2.5 XVan den Kroomerberg, M. Philippens, H. Cappon, J. Wismans, “Human Head-Neck Response During Low-Speed Rear Impacts”
SAE 983158.
6 mph
7. Humanvs.
Hybrid III
Kleinberger, M., R. Eppinger, M. Haffner, and M. Beebe, “Enhancing Safety with an Improved Cervical Test Device” Safety in Football, ASTM 1997.
3.5X5X
3X
2X
Stiffness in Neck
Stiffness in Neck
Human - Max
Human - Min
Hybrid III
Hybrid III
Human - Max
Human - Min
100°
80°
75°
55°
25°
20°
Kleinberger, M., R. Eppinger, M. Haffner, and M. Beebe, “Enhancing Safety with an Improved Cervical Test Device” Safety in Football, ASTM 1997.
2X3X
2X1.5X
Human - Max
Human - Min
Hybrid III
Human - Max
Human - Min
Hybrid III
Stiffness in Neck
Stiffness in Neck
105°
85°
35°
90°
70°
45°
Kleinberger, M., R. Eppinger, M. Haffner, and M. Beebe, “Enhancing Safety with an Improved Cervical Test Device” Safety in Football, ASTM 1997.
Gender: M Initial Head Angle: -9.0°
Weight: 175 Human Head Rotation: Forward
Human/Manikin Curve Matching
Gender: F Initial Head Angle: -28.9°
Weight: 136 Human Head Rotation: Forward
Human/Manikin Curve Matching
Headgear
Underwash: Fluid Flow Dynamics
Streamlines around unprotected and helmeted heads
0
100
200
300
400
500
600
700
800
-0.002 1E-17 0.002 0.004 0.006 0.008
Pre
ssu
re (
kP
a)
Time (s)
Helmeted
Velocity vectors- Top view
1) CPSC Headform 3) Human Head 4) Hybrid III2) Test Area
5) Human Head 6) Injury Diagram
7) Hybrid III with Exemplar Helmet
Impact Site Location
Temporal Bone Fracture
1) CPSC Headform 3) Human Head 4) Hybrid III2) Test Area
5) Human Head 6) Injury Diagram
7) Hybrid III with Exemplar Helmet
Impact Site Location
Temporal Bone Fracture
5) Human Head 6) Injury Diagram
7) Surrogate with Exemplar Helmet
Approximate impact site elevation for test to back of the helmet (1 in above the test line for the back impact)
1) DOT Headform 3) Human Head 4) Hybrid III2) Test Area
Impact Site Location
SNELL M2005 ECE 22.05
•Scheer, D., Karami, G., Ziejewski, M. (2015). An Evaluation of the Riddell IQ HITS System in Prediction of an Athlete’s Head Acceleration, 7th Asia-Pacific Congress on Sports Technology, SAE 942215.
Lateral Plane
•Scheer, D., Karami, G., Ziejewski, M. (2015). Effects of Helmet Surface Geometry on Head Acceleration in High Velocity Water Sports, 7th Asia-Pacific Congress on Sports Technology, SAE 942215.
•Scheer, D., Karami, G., Ziejewski, M. (2015). Effects of Helmet Surface Geometry on Head Acceleration in High Velocity Water Sports, 7th Asia-Pacific Congress on Sports Technology, SAE 942215.
•Scheer, D., Karami, G., Ziejewski, M. (2015). Effects of Helmet Surface Geometry on Head Acceleration in High Velocity Water Sports, 7th Asia-Pacific Congress on Sports Technology, SAE 942215.
•Scheer, D., Karami, G., Ziejewski, M. (2015). Effects of Helmet Surface Geometry on Head Acceleration in High Velocity Water Sports, 7th Asia-Pacific Congress on Sports Technology, SAE 942215.