Presentation on theme: "Doug Browne Jeff Markle Tyler Severance. Subdural hemorrhaging occurs when the blood vessels that connect the dura to the brain rupture This can happen."— Presentation transcript:
Doug Browne Jeff Markle Tyler Severance
Subdural hemorrhaging occurs when the blood vessels that connect the dura to the brain rupture This can happen when the brain moves relative to the dura, causing the connecting vessels to stretch and burst Due to a higher density of CSF relative to brain tissue density (4% greater) How much strain would be significant?
From cadaveric studies at Vanderbilt University, the connecting blood vessels undergo permanent deformation at 120% strain and total rupture at 150% strain which occurs at accelerations between 4,500 and 10,000 rad/s 2
Well verified that collisions in football can exceed dangerous levels of rotational acceleration In all levels of football (high school, college and professional) the top 1% of collisions far exceed critical levels of rotational acceleration Collisions cannot be prevented without drastic change in the sport; however, helmet design can be modified to protect against the potential risk LevelMeasurementStudy Translational Acceleration (g) Rotational Acceleration (rad/s^2 ) High SchoolTop 1% of ImpactsSchnebel et al., 2007114.5gNA College Top 1% of ImpactsSchnebel et al., 2007127.8gNA Average ImpactDuma et al., 200532g2,213 Professional Average ConcussionPellman et. al, part II97.8g6,432 Average Concussion + 1 standard deviation Pellman et. al, part II125.5g8,245
Conservation of Energy: Energy is neither created nor destroyed. Collisions in American football are inelastic collisions; kinetic energy is not conserved. In an example where two players strike each other and fall to the ground, the kinetic energies of both players immediately prior to the collision are converted to deformational energy as the respective velocities of both players rapidly decrease to 0. Energy attenuating properties of helmets (and shoulder pads) decrease the amount of deformational energy that is transmitted to vital structures.
Striking player comes from the left and drives through defender First response is helmet compression Force from Internal liners cause head to move about y-axis Impact only lasts about 15 msec in total Highest strains here occur in the midbrain several msec after impact forces have peaked http://www.youtube.com/watch?v=k1nXnX1sKIo
It is interesting to note the incidence of brain injuries actually peaked many years after the introduction of helmets. Helmet use became mandatory in the NCAA in 1939 and the NFL in 1940. These rule changes, and the addition of the facemask in the 1950s, afforded increased protection to the head but also led to unanticipated changes in behavior and/or technique—with initial contact now more frequently being made with the helmet. Consequently, the incidence of brain-injury related fatalities peaked during the 5-year span from 1965 to 1969. In response, the National Operating Committee on Standards for Athletic Equipment (NOCSAE) was founded in 1969 and the first safety standards for helmets were implemented in 1973.
The National Operating Committee on Standards for Athletic Equipment is the governing body that regulates standards for football helmets. Helmets are only required to prevent against levels of translational acceleration Strong emphasis placed on the drop test This is flawed Only been proven to correlate with skull fractures The demand to raise the threshold score of the test (to make it more applicable to concussions) has been discouraged due to “technological limitations and sacrifices to the sport”
Visited Southern Impact Research Center (one of the limited locations certified to test helmets) to meet with Dave Halstead, one of the nation’s leading experts on helmet design Additionally, Halstead explained and showed that concussions can occur without contact to the head Current helmets are effective at dampening blows to the head (difficult to improve upon), but this is a different issue than lowering overall angular acceleration
After meeting with Halstead, we identified several main issues our team could “tackle ” Helmet weight Detection of dangerous accelerations Large range of un-resisted motion Lightweight helmet that keeps similar levels of protection against linear acceleration as current models Include in the helmet a device that indicates when dangerous levels of rotational acceleration have been reached. Attempt to add increasing resistance to range of motion to prevent the head from reaching the peak levels during the collision
Spring coiled safety door closers use a dashpot to reduce acceleration when closing Example of controlled angular deceleration As angle inc, angular resistance inc Viscoelastic based properties One drawback -> one dimensional Might be possible to use network of these (shoulder pad = origin; helmet = insertion) to restrict quick movements but not inhibit deliberate ones
Spring loaded design Incorporate the padding system of a butterfly collar Used in 3 different directions of support Helmet would rest in between the padding network Focused in y axis with minimal emphasis on x and z Allow movement, inhibit rapid acceleration *** Helmet and Shoulder pads are a separate network… still are easy to remove and separate
Only potential drawback is the creation of a spring loaded design Spring rotators have a dashpot sense in that they offer a constant internal resistance Internal resistance reduces the peak acceleration/deceleration and this is where the design is successful
Testing at Southern Impact Hope to utilize high velocity projectile test to better simulate multiple directional force Also plan to use drop test but only to compare our model to existing ones Further testing and modification can occur as needed for the rest of the semester
Huang HM, Lee MC, Chiu WT, Chen CT, Lee SY: Three-dimensional finite element analysis for subdural hematoma. J Trauma 47: 538–544, 1999. Depreitere B, Van Lierde C, Vander Sloten J, Van Audekercke R, Van Der Perre G, Plets C et al.: Mechanics of acute subdural hematomas resulting from BV rupture. Journal of Neurosurgery 104(6): 950-956, 2006.Journal of Neurosurgery Löwenhielm P: Strain tolerance of the vv. cerebri sup. (BVs) calculated from head-on collision tests with cadavers. Z Rechtsmedizin 75:131–144, 1974. Gennarelli TA, Thibault LE: Biomechanics of acute subdural hematoma. J Trauma 22:680–686, 1982. Lee MC, Ueno K, Melvin JW: Finite element analysis of traumatic subdural hematoma, in Proceedings of the 31st Stapp Car Crash Conference. New York, NY, Society of Automotive Engineers, 1987, pp 67- 77.
Lee MC, Haut RC: Insensitivity of tensile failure properties of human BVs to strain rate: implication in biomechanics of subdural hematoma. J Biomech 22(6-7): 537-42, 1989. Forbes JA, Withrow TJ: Biomechanics of Subdural Hemorrhage in American Football. Vanderbilt University, 2010
To learn more about Southern Impact Research Center, please visit: http://www.youtube.com/watch?v=hwA-hiFu4Xw http://www.youtube.com/watch?v=hwA-hiFu4Xw http://www.soimpact.com/ http://www.soimpact.com/