Characterization of the Rate-Dependent Mechanical Properties and Failure of Human Knee Ligaments
|
|
- Julia Andrea Miller
- 6 years ago
- Views:
Transcription
1 Characterization of the Rate-Dependent Mechanical Properties and Failure of Human Knee Ligaments J.A.W. van Dommelen *, B.J. Ivarsson, M. Minary Jolandan, S.A. Millington, M. Raut, J.R. Kerrigan, J.R. Crandall Center for Applied Biomechanics, University of Virginia, Charlottesville, USA D.R. Diduch Department of Orthopaedic Surgery, University of Virginia, Charlottesville, USA Copyright 25 SAE International ABSTRACT The structural properties of the four major human knee ligaments were investigated at different loading rates. Bone-ligament-bone specimens of the medial and lateral collateral ligaments and the anterior and posterior cruciate ligaments, obtained from post-mortem human donors, were tested in knee distraction loading in displacement control. All ligaments were tested in the anatomical position corresponding to a fully extended knee. The rate dependence of the structural response of the knee ligaments was investigated by applying loadingunloading cycles at a range of distraction rates. Ramps to failure were applied at knee distraction rates of.16 mm/s,, or 1,6 mm/s. Averages and corridors were constructed for the force response and the failure point of the different ligaments and loading rates. The structural response of the knee ligaments was found to depend on the deformation rate, being both stiffer and more linear at high loading rates. This rate dependence was found to be more pronounced at high loading rates. INTRODUCTION Automobile crashes involving pedestrians are very common, and often lead to severe injuries to the lower extremities. Lower extremity injuries often have longterm effects, and the associated societal cost is high. In a large portion of pedestrian-automobile collisions, knee ligament injuries are sustained. Of 357 fatal pedestrianautomobile collisions surveyed (Teresinski and Madro, 21), 8 % of all pedestrians sustained injuries to knee ligaments and epiphyses, versus 94 % of pedestrians in lateral impacts. Varus-valgus strain has been identified by Teresinski and Madro as the most common mechanism for knee injury in pedestrians hit from the lateral side. The collateral knee ligaments are the most commonly injured ligamentous structures when the knee sustains a varus-valgus strain (Kajzer et al., 199, 1993, 1997, 1999; Bhalla et al., 23; Kerrigan et al., 23a). Automobile manufacturers are currently designing and testing front-end components in anticipation of proposed regulations for injury prevention of lower extremities in pedestrian-automobile collisions. As computational modeling is a powerful tool, several research groups have developed finite element (FE) models of the human lower extremity to evaluate potential pedestrian-injury countermeasures (e.g. Bermond et al., 1993, 1994; Yang et al., 1996; Schuster et al., 2; Takahashi et al., 2, 23; Beillas et al., 21; Maeno et al., 21). Recent advances in computational modeling have made it possible to incorporate increased complexity in the constitutive representations of soft tissues. Since knee ligaments play a central role in knee-joint and lower limb kinematics, their constitutive properties are critical in FE analyses. These constitutive representations must be derived from results obtained in experimental testing. In pedestrian-automobile collisions, accurate descriptions of the collateral ligament behavior are essential for realistic knee-joint kinematics and injury prediction. Structural and material properties of human knee ligaments have been studied extensively, in particular the cruciate ligaments due to their frequent involvement in sports injuries (Trent et al., 1976; Kennedy et al., 1976; Noyes and Grood, 1976; Tremblay et al., 198; Piziali et al., 198; Marinozzi et al., 1983; Butler et al., 1986; Hollis et al., 1988; Rauch et al., 1988; Woo et al., 1991; Jones et al., 1995; Rowden et al., 1997). However, only few studied the human collateral ligaments (Trent et al., 1976; Kennedy et al., 1976; Marinozzi et al., 1983, Kerrigan et al., 23b). Material * Current address: Department of Mechanical Engineering, Eindhoven University of Technology, Eindhoven, The Netherlands.
2 properties of human collateral knee ligaments were reported by Butler et al. (1986) and Quapp and Weiss (1998). Butler et al. (1986) reported data from tests on bone-ligament-bone specimens of the anterior cruciate ligament (ACL), posterior cruciate ligament (PCL) and the lateral collateral ligaments (LCL) averaged together. Quapp and Weiss (1998) tested dog-bone shaped cutouts of the medial collateral ligaments (MCL) by applying a tensile force parallel to either the long axis or the transverse axis of the fibers. Most of the above-mentioned studies were conducted at strain rates at least an order of magnitude below those predicted in car-pedestrian collisions. Therefore, those ligament properties are inadequate for use in FE simulations of car-pedestrian collisions. Unpublished finite element simulations of lateral impact pedestrianautomobile collisions at 4 km/h predict that collateral ligaments are strained at 3-5 s 1. This paper provides new data for the structural behavior and failure of the medial and lateral collateral ligaments and the separate bundles of the anterior and posterior cruciate ligaments at a large range of knee distraction rates. This range of rates includes rates representative for ligament loading in pedestrian-automobile collisions. The results can be employed to validate detailed finite element models of the human lower extremity to be used in the development and evaluation of pedestrian injury countermeasures and to derive constitutive equations for these models. METHODOLOGY Bone-ligament-bone (BLB) specimens were tested to failure in tension by applying displacements to the bony ends of the specimen, with the knee in full extension, see Figure 1. The anatomical distraction orientation is obtained by applying appropriate transverse displacements to one of the bone ends using an xypositioning table. The orientation of the knee joint for ligament tensile tests affects the nature of load application to the ligament. The distraction orientation was chosen because it recruits a significant portion of each ligament s fibers in tension, it initially preserves the anatomical orientation of each ligament, and it is the preferred mode of loading for subsequent FE validations. SPECIMEN PREPARATION Eight male post-mortem human subjects were obtained and used in accordance with local and federal laws, as well as with the ethical guidelines and research protocol approved by the Human Usage Review Panel and a University of Virginia institutional review board. Anthropometric donor information is given in Table 1. The average donor age was 53.4 years, with an average weight of 76. kg. Pretest CT scans verified the absence of bone or joint pathology. All limbs were sectioned prior to thawing and defrosted individually in temperature controlled water for 24 hours prior to ligament specimen preparation. The bone-ligament-bone specimens were extracted and potted by an orthopaedic surgeon (S.A.M.). MCL ACL PCL Figure 1: Schematic representation of the vertical distraction orientation. Table 1: Anthropometric donor information. ID Gender Age (yr) Weight (kg) Height (cm) Race Cause of death 1 male white drowning 2 male white hypertensive cardiovascular disease 3 male white lung cancer 4 male white myocardial infarction 5 male white suicide by hanging 6 male white myocardial infarction 7 male white ETOH complications 8 male white lung cancer average LCL std The average and standard deviation of donor height are based on cadaver 1-7 only. Each lower limb specimen was dissected free of all tissue except for the bones and the major ligaments. For each knee, both collateral ligaments and one cruciate ligament bundle were saved. At this time, the location and orientation of the distal insertion with respect to its proximal insertion for each collateral ligament was recorded so that the in situ orientation could be reproduced during potting and subsequent testing. Also anthropometry measurements were taken from each specimen. The proximal tibiofibular joint was then disarticulated and the fibula was cut off 4-6 cm inferior to the ligament insertion. The proximal MCL and LCL bone plugs were obtained by bisecting the medial and lateral femoral condyles, respectively, in the sagittal plane. The tibia was cut 4-6 cm inferior to the most distal fiber insertion of the MCL and was then split in a sagittal plane. Holes were drilled in the bone plugs and two screws were inserted through each plug. The screws served to fixate the bone plug in the potting material. The specimens were potted in aluminum cups using R1 Fast Cast No. 891 (Goldenwest Mfg; Inc., Cedar Ridge, CA, USA), a fast setting urethane casting resin. Special care was taken to ensure that no resin came in contact with ligamentous tissue and that the bone plugs were cast in the proper anatomical orientation. All ligament
3 specimens were kept moist during the extraction and subsequent potting using physiological.9 % saline. After the potting, the specimens were wrapped in saline soaked gauze and refrozen. TEST METHOD Twelve to twenty-four hours prior to each test, the test specimen was allowed to thaw at 2 ºC in a refrigerator. Before testing, the specimen was removed from the refrigerator and submerged in saline (at room temperature) for a minimum of 15 minutes. The ligament length was then measured using digital calipers. The length was defined as the shortest distance between insertions, parallel to the long-axis of the ligament. The specimen was mounted in a test fixture that was attached to the cross head of the actuator of an Instron 88 servo hydraulic biaxial test machine (Instron, Canton, MA, USA), see Figure 2(a). order not to produce any macro- or micro-failures. The relative elongation ε of the ligament is defined as the ratio between the elongation and the anatomical length of the ligament: ε =, (1) where is the anatomical length (defined as the shortest distance between insertions) and is the elongation of the ligament in the ligament direction. The vertical displacement d required to produce a relative ligament elongation ε in a structure of length with an initial elevation angle ϕ (see Figure 2(b)) can be shown to be: 2 d = sin( ϕ ) + sin ϕ + ε( ε + 2). (2) mounting cup bone plugs mounting cup (a) actuator ligament loadcell xy-table Figure 2: Schematic illustration of (a) test setup and (b) mounted ligament. An accelerometer was mounted on the actuator to record its acceleration during the high rate (~1,6 mm/s) tests. A Denton 6-axis load cell (Robert A. Denton, Inc., Rochester Hills, MI, USA) was mounted between an xytable and the bottom plate to measure all components of the ligament force vector. An accelerometer was mounted on the bottom plate to record any vibrations of the load cell and bottom fixture. Once the specimen was mounted, the relative transverse displacement (defining the distraction orientation), as measured by the orthopaedic surgeon during specimen preparation, was applied to the distal bone cup. The ligament was kept moist by applying gauze soaked with room temperature physiological (.9 %) saline every 5-15 minutes during testing. The unpreconditioned zero strain position was determined by lowering the actuator until there was no load on the ligament, and then raising the actuator until the vertical tensile load through the ligament measured 2 N (Funk et al., 2). The ligament was then preconditioned by applying 24 cycles of a sinusoidal displacement at 8 Hz and a distraction amplitude leading to a relative ligament elongation of 8 %. The preconditioning amplitude was limited to this value in ϕ (b) After preconditioning, the ligament was allowed to recover for a minimum of 1, seconds in a slacked position. A new zero strain position (preconditioned zero strain) was then determined by again applying a 2 N preload. This zero strain position was maintained throughout the remaining of the test battery. The ligament was subjected to four (approximate) separate step-functions of relative ligament elongations of 8 %, 6.4 %, 4.8 %, and 3.2 %, respectively (see Figure 3), to measure force-relaxation. Each step was applied with a constant distraction rate of 1 mm/s. After each displacement step, the actuator position was held for 5 seconds during which the relaxation of the ligament force was measured. Data was acquired at a sample rate of 2, Hz during the first 5 seconds after the application of the step displacement, 2 Hz during the next 55 seconds and 2 Hz for the remaining time of the step. The ligament was allowed to recover at zero-strain for a minimum of 1, seconds after each step. Following these steps, three loading-unloading cycles to the preconditioning-amplitude were applied at a constant distraction rate of 1 mm/s, 1 mm/s, and 1 mm/s, respectively. Data was acquired at a sample rate of 1, Hz. After each cycle, the specimen was allowed to recover for 1, seconds at zero strain. displacement precond. step and hold loading unloading cycles time Figure 3: Schematic illustration of the test sequence: preconditioning, a series of step-and-hold tests with decreasing amplitude, and three loading-unloading cycles with increasing distraction rate. This test sequence was followed by a ramp to failure.
4 Following the series of tests, during which the displacement amplitude never exceeded the preconditioning amplitude, each ligament was subjected to a distraction ramp to failure, at a constant distraction rate of.16 mm/s,, or 1,6 mm/s. All cruciate ligaments were subjected to high rate loading (1,6 mm/s). During the tests, data was acquired at a rate of 2 Hz for the slow (.16 mm/s) and medium () rate tests and at 2, Hz for the high rate tests. Since it was desired to have the load applied to the ligament at constant actuator velocity, before the highest rate tests (1,6 mm/s), the actuator was lowered to put slack in the ligament. Slacking the ligament as much as possible allowed the actuator to accelerate to constant velocity before any load was applied to the ligament. The force at the zero strain position was used as the zero force level. High-speed video images (1, frames/s) were taken during the failure tests at the highest rate. High resolution digital photographs were taken approximately every second during the medium speed () tests. During the lowest speed failure tests (.16 mm/s) a photograph of the ligament was taken at 1 minute intervals. After the test, the ligament failure mode was documented. The structural response of a ligament is the result of the interplay between the material properties of ligamentous tissue and the geometry of the ligament. In this study, it was chosen to report structural properties only. All force levels reported represent the magnitude of the total force vector. The relative ligament elongation is defined as the elongation relative to its anatomical length, which is measured as the shortest distance between insertions. RESULTS RATE-DEPENDENCE Four steps in knee distraction were applied to the ligament at different levels of relative ligament elongation. The response to the step-and-hold tests are given in Figure 4 for a lateral collateral ligament. The initial (t < 1 s) relaxation behavior is independent of the applied deformation, i.e. time-deformation separability is applicable in this time range. The structural response of a lateral collateral ligament to the following three loadingunloading cycles at different rates of knee distraction is displayed in Figure % 6.4 % 4.8 % 3.2 % time [s] Figure 4: Response to step-and-hold tests for a lateral collateral ligament (LCL, donor 3). TEST MATRIX The cruciate ligaments were split into their functional bundles: the antero-medial part of the ACL (aacl), the postero-lateral bundle of the ACL (pacl), the anterolateral part of the PCL (apcl) and the postero-medial part of the PCL (ppcl). A total of 32 bone-ligament-bone (BLB) specimens were tested in tension to failure. The test matrix for the failure tests on these specimens is shown in Table mm/s 1 mm/s 1 mm/s Table 2: Test matrix for failure tests. The number of tests at each distraction rate by ligament type is given in each entry of the table. 1,6 mm/s.16 mm/s Total MCL LCL aacl pacl apcl ppcl Total Figure 5: Response to loading-unloading cycles at different rates of knee distraction for a lateral collateral ligament (LCL, donor 8). A clear rate-dependence can be observed in this figure. A similar response was obtained for all bone-ligament bone specimens. The force level during loading at a relative ligament elongation of.4 was determined for each cycle. The rate-dependence of this force level per specimen is shown in Figure 6 for each ligament type.
5 mm/s 1 mm/s 1 mm/s 1 mm/s.1 mm/s.1 mm/s log(rate) (a) MCL (a) MCL ε =.6 ε =.5 ε =.4 ε =.3 ε = log(rate) (b) LCL log(rate) (b) MCL aacl pacl apcl ppcl Figure 7: Response of a medial collateral ligament (donor 2) to loading-unloading cycles. (a) Force-elongation curves at different rates and (b) force level at various levels of relative ligament elongation vs. distraction rate log(rate) (c) cruciate ligaments Figure 6: Rate-dependence of the force at a relative ligament elongation of.4, for (a) 8 medial collateral ligaments, (b) 8 lateral collateral ligaments, and (c) 8 cruciate ligaments. The lines connect responses per specimen. For a number of ligaments, tests were performed at a larger range of knee distraction rates. These specimens were subjected to loading-unloading cycles to 8 % relative ligament elongation (i.e. the preconditioning level) at distraction rates ranging from.1 mm/s to 1, mm/s. The force-elongation responses are shown in Figures 7(a) and 8(a). Furthermore, Figure 7(b) and 8(b) show the force measures during loading at various levels of relative ligament elongation versus the applied loading rate. The dependence of these force levels on the loading rate is found to increase with the rate of distraction. FAILURE After subjecting the specimens to a sequence of preconditioning, step-and-hold tests and loadingunloading cycles, each bone-ligament-bone specimen was subjected to a ramp to failure at a constant rate of knee distraction. In four high rate tests for the medial collateral ligaments and two for the lateral collateral ligaments, failures were observed in either bone pieces (away from the insertion) or potting material. All cruciate specimens showed ligament failures. In Figure 9, individual failure curves are displayed for each type of ligaments. For specimens with non-ligament failures, dashed lines are used. In Figure 1, the relative ligament elongation is shown versus the time, multiplied by the chosen knee distraction rate (i.e..16 mm/s,, or 1,6 mm/s). The actual ligament elongation rate is, besides the chosen distraction rate, dependent on the ligament size and elevation angle and therefore differs between specimens. The average relative ligament elongation rates (in the region of constant distraction rate) are given in Table 3. The average relative elongation rate of the high rate tests is representative for ligament loading during pedestrian-automobile collisions.
6 22.16 mm/s 16 mm/s 2 1 mm/s 316 mm/s 1 mm/s 1 mm/s 1 mm/s.1 mm/s.1 mm/s (a) MCL.9 (a) LCL 7 ε =.6 ε =.5 ε =.4 ε =.3 ε = mm/s 16 mm/s log(rate) (b) LCL (b) LCL Figure 8: Response of a lateral collateral ligament (donor 3) to loading-unloading cycles. (a) Force-elongation curves at different rates and (b) force level at various levels of relative ligament elongation vs. distraction rate. aacl pacl apcl ppcl Table 3: Average relative ligament elongation rates and the corresponding standard deviations. MCL LCL aacl pacl apcl ppcl 1,6 mm/s -1 [s ] -3-1 [1 s ].16 mm/s -5-1 [1 s ] 45 ± ± ± ± ± ± ± ± ± ± 6.1 Due to the limited number of specimens, the (average - minimum) value is given instead of the standard deviation (c) cruciate ligaments Figure 9: Force responses during failure tests for (a) medial collateral ligaments, (b) lateral collateral ligaments, and (c) cruciate ligaments. Solid lines represent ligament failures, whereas dashed lines represent either non-ligament failures or unrecorded (denoted by *) failure points.
7 mm/s 16 mm/s responses and averaged failure points are shown in Figure 11. The failure point is defined as the location on the force-elongation curve corresponding to the force maximum mm/s 16 mm/s time*rate [mm] (a) MCL mm/s 16 mm/s mm/s 16 mm/s (a) MCL time*rate [mm] (b) LCL aacl pacl apcl ppcl aacl pacl apcl ppcl (b) LCL time*rate [mm] (c) cruciate ligaments Figure 1: Relative ligament elongation versus the time, multiplied by the (programmed) distraction rate for (a) medial collateral ligaments, (b) lateral collateral ligaments, and (c) cruciate ligaments. For a number of specimens, the application of slack prior to the high rate ramp was geometrically not possible, hence the smaller elongation rate in the early region (c) cruciate ligaments The averaged ligament response, as well as a standard deviation bandwidth was constructed for each ligament type and loading rate. To increase the number of specimens in the averaging process, also previously obtained data, partly published in Kerrigan et al. (23b), was included (see Table 4). Also the pre-failure response of specimens exhibiting non-ligament failure has been included in the averaging procedure. Averaged Figure 11: Averaged responses and averaged failure points for (a) medial collateral ligaments, (b) lateral collateral ligaments, and (c) cruciate ligaments. Solid lines represent averages of three or more curves and a one standard deviation bandwidth. Dashed lines represent averages of two curves and the minimum and maximum range.
8 Table 4: The total number of specimens used for response averaging (obtained by combining the newly obtained data with previously reported data (Kerrigan et al., 23b)). 1,6 mm/s.16 mm/s Total MCL LCL aacl pacl apcl ppcl Total For the collateral ligaments, which were tested at a large range of distraction rates, a rate-dependence is observed, with the high rate response being stiffer and more linear. The averaged responses indicate no large differences between either the antero-medial and the postero-lateral bundle of the ACL or the antero-lateral bundle and the postero-medial bundle of the PCL. The averaged failure points are summarized in Table 5. The average ligament elongation at failure is found to be considerably larger for the MCLs than for the other ligaments tested in this study. This can be partly attributed to the definition of ligament elongation used. This definition is based on the measured shortest length between insertions. However, the lower insertion of the medial collateral ligament extents well below the tibial condyle. This lower part is also a part of the load-bearing and straining structure. The average ratio of largest ligament length (based on lower insertion) / shortest ligament length (based on upper insertion) of the medial collateral ligaments was 2.9. Table 5: Average and standard deviation of failure points for data combined with Kerrigan et al. (23b) tests. rate f [kn] [-] [mm/s ] MCL ±.34.4 ± ± ±.51 1,6 1.4 ± ±.86 LCL ± ± ±.78.2 ±.55 1,6.54 ± ±.16 aacl 1,6.99 ± ±.28 pacl 1,6 1. ± ±.3 apcl 1,6.65 ± ±.23 ppcl 1,6.29 ± ±.14 Since only two curves are available, the (average - minimum) bandwidth is given instead of the standard deviation. where f is the magnitude of the force vector and ε denotes the relative ligament elongation, is fitted to the averaged failure curves. The obtained parameters are given in Table 6. Again, the force response is found to be more linear for high loading rates. Table 6: Parameters of a power law fit to the averaged failure curves. 1,6 mm/s.16 mm/s C [kn] n [-] C [kn] n [-] C [kn] n [-] MCL LCL aacl pacl apcl ppcl Typically observed failure modes are given in Table 7. The typical failure mode appeared to be dependent on the loading rate (although this is inconclusive due to the limited number of specimens). Typical post-failure images are shown in Figure 12. Table 7: Typical failure modes for bone-ligament-bone specimens in distraction loading. 1,6 mm/s.16 mm/s MCL tibial insertion tibial insertion midsubstance/ fem. ins. LCL femoral insertion fibular insertion fibular insertion cruc. lig. femoral insertion (a) MCL (b) MCL (c) LCL Figure 12: Typical failure modes; (a), (b) medial collateral ligaments, (c) lateral collateral ligament. The force-elongation curves of the bone-ligament-bone specimens have a strongly nonlinear shape. A two parameter power law, which can be written as: f n = Cε, (3)
9 In Figure 13, various stages of the failure process of a medial collateral ligament are displayed. The ligament is loaded at a knee distraction rate of 1,6 mm/s. For this ligament, failure occurs at the tibial insertion. bundles in this study as well as combined maximum force of the two PCL bundles lie within the range of forces reported in literature, although it is noted that the loading rate of the present study is considerably larger than most previously published studies. Moreover, the applied distraction orientation (the anatomical orientation corresponding to the fully extended knee) deviates from the orientation used in most other studies. CONCLUSION (a) ms (b) 7 ms (c) 14 ms (d) 21 ms (e) 28 ms (f) 35 ms Figure 13: Various stages of failure of a medial collateral ligament at a distraction rate of 1,6 mm/s. For the lateral collateral ligaments, the average maximum force observed in this study is in agreement with the range of 377 to 425 N reported in literature (Trent et al., 1976; Marinozzi et al., 1983). However, the average maximum force found for the medial collateral ligaments is considerably larger than reported in several other studies (Trent et al., 1976; Kennedy et al., 1976; Marinozzi et al., 1983). In the latter studies, the maximum force ranges from 465 to 665 N for loading rates comparable to the medium distraction rate of this study. The maximum force for the cruciate ligaments as found in literature varies widely (e.g. Trent et al., 1976; Kennedy et al., 1976; Noyes and Grood 1976; Tremblay et al., 198; Piziali et al., 198; Marinozzi et al., 1983; Butler et al., 1986; Hollis et al., 1988; Rauch et al., 1988; Woo et al., 1991; Jones et al., 1995; Rowden et al., 1997). For the ACL, maximum forces ranging from 335 to 2,195 N can be found in the above-mentioned studies, whereas the PCL maximum force ranges from 258 to 1,627 N. The combined maximum force of the two ACL In this study, the structural response to tensile loading at different rates was investigated for the four major human knee ligaments. Bone-ligament-bone specimens were tested in knee distraction loading. The anatomical orientation of the tested ligaments corresponded to the fully extended knee. A clear rate-dependence was observed when the same ligaments were loaded to nondamaging strain levels at different loading rates. The rate dependence was found to be stronger at high loading rates. The viscoelastic structural behavior of knee ligaments will be further discussed in Van Dommelen et al., 25a, 25b) The ligaments were loaded to failure in displacement control at knee distraction rates of.16 mm/s, 1.6 mm/s, and 1,6 mm/s. Averages and standard deviation corridors for the force response were reported, as well as for the failure point and loading rates. Again, the structural response of the knee ligaments was found to be affected by the deformation rate. The ligaments were both stiffer and the response was more linear at high loading rates. No large differences were observed between the averaged responses of either the anteromedial and the postero-lateral bundle of the ACL or between the averaged curves of the antero-lateral and the postero-medial bundle of the PCL. The maximum force levels observed in the medial collateral ligaments were considerably larger than those of the lateral collateral ligaments. Moreover, also the average ligament elongation at failure was found to be significantly larger for the MCLs than for the other ligaments tested. The latter was attributed to the definition of relative ligament elongation used in combination with the complicated geometry of the MCL. REFERENCES 1. Beillas, P., Begeman, P.C., Yang, K.H., King, A.I., Arnoux, P-J., Kang, H-S., Kayvantash, K., Brunte, C., Cavallero, C., and Prasad, P. Lower limb: advanced FE model and new experimental data. Stapp Car Crash Journal, pp , Bermond, F., Ramet, M., Bouquet, R., and Cesari, D. A finite element model of the pedestrian knee-joint in lateral impact. International Conference on the Biomechanics of Impacts (IRCOBI), 1993.
10 3. Bermond, F., Ramet, M., Bouquet, R., and Cesari, D. A finite element model of the pedestrian leg in lateral impact. 14th International Conference on the Enhanced Safety of Vehicles (ESV) Bhalla, K., Bose, K., Madeley, N.J., Kerrigan, J., Crandall, J., Longhitano, D., and Takahashi, Y. Evaluation of the response of mechanical pedestrian knee joint impactors in bending and shear loading. 18th ESV, Bose, D., Sanghavi, P., Kerrigan, J.R., Madeley, N.J., Bhalla, K.S., and Crandall, J.R. Material characterization of ligaments using non-contact strain measurement and digitization. Injury Biomechanics Research, Proceedings of the Thirtieth International Workshop Butler, D.L., Kay, M.D., Stouffer, D.C. Comparison of material properties in fascicle-bone units from human patellar tendon and knee ligaments. Journal of Biomechanics, 19(6), pp , Van Dommelen, J.A.W., Minary Jolandan, M., Ivarsson, B.J., Millington, S.A., Raut, M., Kerrigan, J.R., Crandall, J.R., and Diduch, D. R. Pedestrian injuries: viscoelastic properties of human knee ligaments at high loading rates. In preparation. 8. Van Dommelen, J.A.W., Minary Jolandan, M., Ivarsson, B.J., Millington, S.A., Raut, M., Kerrigan, J.R., Crandall, J.R., and Diduch, D. R. Viscoplastic flow of human knee ligaments. In preparation. 9. Funk, J., Hall, G., Crandall, J.R., and Pilkey, W. Linear and quasi-linear viscoelastic characterization of ankle ligaments, Journal of Biomechanical Engineering, 122, pp , 2 1. Hollis, J.M., Lyon, R.M., Marcin, S., Horibe, E.B., Lee, Woo, S.L.-Y. Effect of age and loading axis on the failure properties of the human ACL. Transactions of the Orthopaedic Research Society, 13, pp. 81, Jones, R.S., Nawana, N.S., Pearcy, M.J., Learmonth, D.J.A., Bickerstaff, D.R., Costi, J.J., Paterson, R.S. Mechanical properties of the human anterior cruciate ligament. Clinical Biomechanics, 1(7), pp , Kajzer, J., Cavallero, S., Ghanouchi, S., Bonnoit, J., Aghorbel. Response of the knee joint in lateral impact: effect of shearing loads, IRCOBI, pp , Kajzer, J., Cavallero, S., Bonnoit, J., Morjane, A., Ghanouchi, S. Response of the knee joint in lateral impact: effect of bending moment. IRCOBI, Kajzer, J., Schroeder, G., Ishikawa, H., Matsui, Y., Bosch, U., Shearing and bending effects at the knee joint at high speed lateral loading, Society of Automotive Engineers, SAE Paper , Kajzer, J., Ishikawa, H., Matsui, Y., Schroeder, G., Bosch, U., Shearing and bending effects at the knee joint at low speed lateral loading, Society of Automotive Engineers, SAE Paper , Kennedy, J.C., Hawkins, R.J., Willis, R.B., Danylchuck, K.D. Tension studies of human knee ligaments. yield point, ultimate failure, and disruption of the cruciate and tibial collateral ligaments. Journal of Bone and Joint Surgery, American Volume 58(3), pp , Kerrigan, J.R., Bhalla, K.S., Madeley, N.J., Funk, J.R., Bose, D., Crandall, J.R. Experiments for establishing pedestrian-impact lower limb injury criteria. Society of Automotive Engineers, SAE Paper , 23a. 18. Kerrigan, J.R., Ivarsson, B.J., Bose, D., Madeley, N.J., Millington, S.A., Bhalla, K.S., Crandall, J.R. Rate-sensitive constitutive and failure properties of human collateral ligaments, IRCOBI Conference on the Biomechanics of Impacts, 23b. 19. Maeno, T., and Hasegawa, J. Development of a finite element model of the total human model for safety (THUMS) and application to car-pedestrian impacts. 17th ESV, Marinozzi, G., Pappalardo, S., Steindler, R. Human knee ligaments: mechanical tests and ultrastructural observations. Italian Journal of Orthopaedics and Traumatology, 9(2), pp , Noyes, F.R., Grood, E.S. The strength of the anterior cruciate ligament in humans and rhesus monkeys. Journal of Bone Joint Surgery, American Volume 58(8), pp , Piziali, R.L., Rastegar, J., Nagel, D.A., Schurman, D.J. The contribution of the cruciate ligaments to the load-displacement characteristics of the human knee joint. Journal of Biomechanical Engineering, 12(4), pp , Quapp, K.M., Weiss, J.A. Material characterization of human medial collateral ligament. Journal of Biomechanical Engineering, 12, pp , Rauch, G., Allzeit, B., Gotzen, L. Biomecahnische Untersuchungen zur Zugfestigkeit des vorderen Kreuzbandes unter besonderer Berücksichtigung der Altersabhängigkeit. Unfallchirurg 91(1), pp , Rowden, N.J., Sher, D., Rogers, G.J., Schindhelm, K. Anterior cruciate ligament graft fixation. Initial comparison of patellar tendon and semitendinosus autografts in young fresh cadavers. American Journal of Sports Medicine, 25(4), pp , Schuster, P.J., Chou, C.C., Prasad, P., Jayaraman, G. Development and validation of a pedestrian lower limb non linear 3d finite element model. Stapp Car Crash Journal, 44, Takahashi, Y., Kikuchi, Y., Konosu, A., Ishikawa, H. Development and validation of the finite element model for the human lower limb of pedestrians, Stapp Car Crash Journal, 44, Takahashi Y., Kikuchi, Y., Mori, F., and Konosu, A., Advanced FE lower limb model for pedestrians. 18th ESV, Teresinski, G., and Madro, R. Knee joint injuries as a reconstructive factor in car-to-pedestrian accidents. Forensic Science International, 124, pp , 21.
11 3. Tremblay, G.R., Laurin, C.A., Drovin, G. The challenge of prosthetic cruciate ligament replacement. Clinical Orthopaedics and Related Research, (147), pp , Trent, P.S., Walker, P.S., Wolf, B. Ligament length patterns, strength, and rotational axes of the knee joint. Clinical Orthopaedics and Related Research (117), pp. 2, Yang, J.K., Wittek, A., Kajzer, J. Finite element model of the human lower extremity skeleton system in lateral impact. IRCOBI, Woo, S.L.-Y., Hollis, J.M., Adams, D.J., Lyon, R.M., Takai, S. Tensile properties of the human femuranterior cruciate ligament-tibia complex. The effects of specimen age and orientation. American Journal of Sports Medicine, 19(3), pp , 1991.
DYNAMIC CHARACTERIZATION OF BOVINE MEDIAL COLLATERAL LIGAMENTS
DYNAMIC CHARACTERIZATION OF BOVINE MEDIAL COLLATERAL LIGAMENTS A. Chawla, S. Mukherjee, H. Warhatkar Department of Mechanical Engineering, Indian Institute of Technology, New Delhi, INDIA R. Malhotra Department
More informationKNEE JOINT INJURY MECHANISMS AND INJURY CRITERIA IN FULL ²SCALE TESTS ACCORDING TO IMPACT POSITION
KNEE JOINT INJURY MECHANISMS AND INJURY CRITERIA IN FULL ²SCALE TESTS ACCORDING TO IMPACT POSITION ARNOUX P.J. 1, THOLLON L. 1, BEHR M. 1, BRUNET C. 1 CESARI D. 2 1 Laboratoire de Biomécanique Appliquée,
More informationFlex-GTR: Open questions and proposals for ACL, PCL and MCL injury thresholds
Bundesanstalt für Straßenwesen (Federal Highway Research Institute) TEG-078 Flex-GTR: Open questions and proposals for ACL, PCL and MCL injury thresholds 7th Meeting of the GRSP Flex PLI Technical Evaluation
More informationTHE STRAIN-RATE DEPENDENCE OF MECHANICAL PROPERTIES OF RABBIT KNEE LIGAMENTS
THE STRAIN-RATE DEPENDENCE OF MECHANICAL PROPERTIES OF RABBIT KNEE LIGAMENTS Sota Yamamoto Akinori Saito Kei Nagasaka Satoshi Sugimoto Koji Mizuno Eiichi Tanaka Nagoya University Japan Masaki Kabayama
More informationEFFECT OF MUSCLE CONTRACTION IN HIGH SPEED CAR- PEDESTRIAN IMPACT SIMULATIONS FOR WALKING POSTURE
EFFECT OF MUSCLE CONTRACTION IN HIGH SPEED CAR- PEDESTRIAN IMPACT SIMULATIONS FOR WALKING POSTURE Soni A., Chawla A., Mukherjee S. Department of Mechanical Engineering, Indian Institute of Technology,
More informationPedestrian CAE Models & Codes Version 1.2 September 2013 TB 013
Technical Bulletin Pedestrian CAE Models & Codes Version 1.2 September 2013 TB 013 Title Pedestrian CAE Models & Codes Version 1.2 Document Number TB013 Author Secretariat Date September 2013 Related Documents
More informationEFFECT OF ACTIVE MUSCLE FORCES ON KNEE INJURY RISKS FOR PEDESTRIAN STANDING POSTURE AT LOW SPEED IMPACTS
EFFECT OF ACTIVE MUSCLE FORCES ON KNEE INJURY RISKS FOR PEDESTRIAN STANDING POSTURE AT LOW SPEED IMPACTS Chawla A, Mukherjee S, Soni A Department of Mechanical Engineering, Indian Institute of Technology,
More informationPEDESTRIAN INJURY MECHANISMS & CRITERIA A COUPLED EXPERIMENTAL AND FINITE ELEMENT APPROACH
PEDESTRIAN INJURY MECHANISMS & CRITERIA A COUPLED EXPERIMENTAL AND FINITE ELEMENT APPROACH Catherine Masson Pierre-Jean Arnoux Christian Brunet Laboratory of Applied Biomechanics. French National Institute
More informationINJURY THRESHOLDS AND A MEASUREMENT TECHNIQUE FOR THE THIGH AND LEG OF A PEDESTRIAN DUMMY
INJURY THRESHOLDS AND A MEASUREMENT TECHNIQUE FOR THE THIGH AND LEG OF A PEDESTRIAN DUMMY Yukou Takahashi, Masayoshi Okamoto, Yuji Kikuchi, Akihiko Akiyama Honda R&D Co., Ltd. Automobile R&D Center ABSTRACT
More informationPedestrian CAE Models & Codes Version 1.4 June 2015 TB 013
Technical Bulletin Pedestrian CAE Models & Codes Version 1.4 June 2015 TB 013 Title Pedestrian CAE Models & Codes Version 1.4 Document Number TB013 Author Secretariat Date June 2015 Related Documents Pedestrian
More informationAnterior Tibia Impacts: A Biofidelity Study between Post-Mortem Human Subjects and Anthropomorphic Test Devices
Anterior Tibia Impacts: A Biofidelity Study between Post-Mortem Human Subjects and Anthropomorphic Test Devices H.M. Gustafson 1, J. McFadden 2 and R. Herriott 3, J.H. Bolte IV 1 1 The Ohio State University;
More informationEFFECT OF MUSCLE CONTRACTION ON KNEE LOADING FOR A STANDING PEDESTRIAN IN LATERAL IMPACTS
EFFECT OF MUSCLE CONTRACTION ON KNEE LOADING FOR A STANDING PEDESTRIAN IN LATERAL IMPACTS Anurag Soni Anoop Chawla Sudipto Mukherjee Department of Mechanical Engineering Indian Institute of Technology
More informationCOMPARISON OF ANKLE INJURY MECHANISM IN FULL FRONTAL AND OBLIQUE FRONTAL CRASH MODES WITH THOR DUMMY AND HUMAN FE MODELS
COMPARISON OF ANKLE INJURY MECHANISM IN FULL FRONTAL AND OBLIQUE FRONTAL CRASH MODES WITH THOR DUMMY AND HUMAN FE MODELS Kaitaro,Nambu Hisaki, Sugaya Hiroyuki, Mae Honda R&D Co., Ltd. Automobile R&D Center
More informationERIC P. SHIELDS UNIVERSITY OF FLORIDA
TENSILE AND VISCOELASTIC PROPERTIES OF TWO AND FOUR STRAND ANTERIOR TIBIALIS AND PERONEUS LONGUS GRAFTS AS A SUBSTITUTE FOR ANTERIOR CRUCIATE LIGAMENT RECONSTRUCTION By ERIC P. SHIELDS A THESIS PRESENTED
More informationValidation of Pedestrian Lower Limb Injury Assessment using Subsystem Impactors
Validation of Pedestrian Lower Limb Injury Assessment using Subsystem Impactors Yukou Takahashi Miwako Ikeda Iwao Imaizumi Yuji Kikuchi Satoru Takeishi Honda R&D Co., Ltd. 212 IRCOBI Conference September
More informationFlexible Pedestrian Legform Impactor Type GT (FLEX-GT) Car Test Results JAMA
TEG- 2 April 27 4 th Flex-TEG MT BASt, Bergisch Gladbach Flexible Pedestrian Legform Impactor Type GT (FLEX-GT) Car Test Results JAMA Japan Automobile Manufacturers Association, Inc. Flex-GT Information
More informationDevelopment of a Flex-PLI LS-DYNA Model
Development of a Flex-PLI LS-DYNA Model Shinya Hayashi 1, Masahiro Awano 2, Isamu Nishimura 2 1 JSOL Corporation, 2 Mitsubishi Motors Corporation Aichi, Japan Summary: A biofidelic flexible pedestrian
More informationSOME IDEAS OF THE LIGAMENT CONFIGURATIONS' EFFECT ON STRAIN CONCENTRATIONS
SOME IDEAS OF THE LIGAMENT CONFIGURATIONS' EFFECT ON STRAIN CONCENTRATIONS K. Yamamoto*, S. Hirokawa**, and T. Kawada*** *Deptment of Mechanical Engineering, Faculty of Engineering, Kurume Institute of
More informationFlexPLI vs. EEVC LFI Correlation
FlexPLI vs. EEVC LFI Correlation Action List Item 1. j) Evaluate and decide on performance / injury criteria and threshold values 5 th IG GTR9-PH2 Meeting 6-7/December/212 Japan Automobile Standards Internationalization
More informationImprovements and Validation of an Existing LS- DYNA Model of the Knee-Thigh-Hip of a 50 th Percentile Male Including Muscles and Ligaments
Improvements and Validation of an Existing LS- DYNA Model of the Knee-Thigh-Hip of a 50 th Percentile Male Including Muscles and Ligaments Dr. Chiara Silvestri, Mario Mongiardini, Prof. Dr. Malcolm H.
More informationCONCEPT DESIGN OF A 4-DOF PEDESTRIAN LEGFORM
CONCEPT DESIGN OF A 4-DOF PEDESTRIAN LEGFORM Qing Zhou Michael Quade* Huiliang Du State Key Laboratory of Automotive Safety and Energy Tsinghua University China * Exchange student from RWTH-Aachen, Germany
More informationDirect Measurement of Graft Tension in Anatomic Versus Non-anatomic ACL Reconstructions during a Dynamic Pivoting Maneuver
Direct Measurement of Graft Tension in Anatomic Versus Non-anatomic ACL Reconstructions during a Dynamic Pivoting Maneuver Scott A. Buhler 1, Newton Chan 2, Rikin Patel 2, Sabir K. Ismaily 2, Brian Vial
More informationConsolidated Technical Specifications for the Advanced Pedestrian Legform Impactor (apli)
IRC-18-42 IRCOBI conference 218 Consolidated Technical Specifications for the Advanced Pedestrian Legform Impactor (apli) Takahiro Isshiki, Jacobo Antona Makoshi, Atsuhiro Konosu, Yukou Takahashi Abstract
More informationPEDESTRIAN LOWER LIMB INJURY CRITERIA EVALUATION A FINITE ELEMENT APPROACH
PEDESTRIAN LOWER LIMB INJURY CRITERIA EVALUATION A FINITE ELEMENT APPROACH P.J. Arnoux 1, D. Cesari 2, M. Behr 1, L. Thollon 3, C. Brunet 1. 1 Laboratoire de Biomécanique Appliquée, UMRT 24 Faculté de
More informationUpdated Version of GTR9-1-07r1. March 28-29, 2012 Japan Automobile Standards Internationalization Center (JASIC) 1
Informal Group on GTR9 Phase2 (IG GTR9-PH2) 2 nd Meeting Technical Discussion Benefit Updated Version of GTR9-1-07r1 March 28-29, 2012 Japan Automobile Standards Internationalization Center (JASIC) 1 Outline
More informationAnterior Cruciate Ligament Surgery
Anatomy Anterior Cruciate Ligament Surgery Roger Ostrander, MD Andrews Institute Anatomy Anatomy Function Primary restraint to anterior tibial translation Secondary restraint to internal tibial rotation
More informationBiomechanical Effects of Femoral Component Axial Rotation in Total Knee Arthroplasty (TKA)
Biomechanical Effects of Femoral Component Axial Rotation in Total Knee Arthroplasty (TKA) Mohammad Kia, PhD, Timothy Wright, PhD, Michael Cross, MD, David Mayman, MD, Andrew Pearle, MD, Peter Sculco,
More informationTOTAL KNEE ARTHROPLASTY (TKA)
TOTAL KNEE ARTHROPLASTY (TKA) 1 Anatomy, Biomechanics, and Design 2 Femur Medial and lateral condyles Convex, asymmetric Medial larger than lateral 3 Tibia Tibial plateau Medial tibial condyle: concave
More informationAFX. Femoral Implant. System. The AperFix. AM Portal Surgical Technique Guide. with the. The AperFix System with the AFX Femoral Implant
The AperFix System AFX with the Femoral Implant AM Portal Surgical Technique Guide The Cayenne Medical AperFix system with the AFX Femoral Implant is the only anatomic system for soft tissue ACL reconstruction
More informationModeling of human knee joint and finite element analysis of landing impact motion
ISSN 1746-7659, England, UK Journal of Information and Computing Science Vol. 13, No. 1, 2018, pp.044-048 Modeling of human knee joint and finite element analysis of landing impact motion Bao Chunyu 1,3,Meng
More informationSide Impact Simulations using THUMS and WorldSID
Side Impact Simulations using THUMS and WorldSID 25 th September, 213 Tsuyoshi Yasuki, Yuichi Kitagawa, Shinobu Tanaka, Satoshi Fukushima TOYOTA MOTOR CORPORATION CONTENTS 1. Background 2. Objective 3.
More informationHistory of Development of the Flexible Pedestrian Legform Impactor (Flex-PLI)
GTR9-C-04 History of Development of the Flexible Pedestrian Legform Impactor (Flex-PLI) November 3 rd, 2011 Japan 1 Contents 1. Back ground 2. History of Flex-PLI Development (Overview) 2 1. Back ground
More informationJoints of the Lower Limb II
Joints of the Lower Limb II Lecture Objectives Describe the components of the knee and ankle joint. List the ligaments associated with these joints and their attachments. List the muscles acting on these
More informationOPEN KNEE: CAPACITY TO REPRODUCE ANTERIOR CRUCIATE LIGAMENT DEFORMATIONS
OPEN KNEE: CAPACITY TO REPRODUCE ANTERIOR CRUCIATE LIGAMENT DEFORMATIONS A. Erdemir1,2 and S. Sibole3 1. ABSTRACT Simulation-based explorations of the knee have commonly relied on finite element analysis.
More informationTensile Forces in Knee Ligaments in Response to Hyperextension
Tensile Forces in Knee Ligaments in Response to Hyperextension Kei Kimura 1, Hidenori Otsubo 2, Satoshi Yamakawa 1, Toshihiko Yamashita 2, Hiromichi Fujie 1. 1 Tokyo Metropolitan University, hino, Japan,
More informationDEVELOPMENT AND VALIDATION OF A CHILD FINITE ELEMENT MODEL FOR USE IN PEDESTRIAN ACCIDENT SIMULATIONS
DEVELOPMENT AND VALIDATION OF A CHILD FINITE ELEMENT MODEL FOR USE IN PEDESTRIAN ACCIDENT SIMULATIONS Yunzhu Meng Thesis submitted to the faculty of the Virginia Polytechnic Institute and State University
More informationDouble Bundle ACL Reconstruction using the Smith & Nephew Outside-In Anatomic ACL Guide System
Knee Series Technique Guide Double Bundle ACL Reconstruction using the Smith & Nephew Outside-In Anatomic ACL Guide System Luigi Adriano Pederzini, MD Massimo Tosi, MD Mauro Prandini, MD Luigi Milandri,
More informationAdvanced FE Modeling of Absorbable PLLA Screws
Advanced FE Modeling of Absorbable PLLA Screws Jorgen Bergstrom, Ph.D., David Quinn, Ph.D., Eric Schmitt jbergstrom@veryst.com, LLC September 14, 2011 Introduction Anterior cruciate ligament (ACL) reconstruction
More informationBiomechanical Characterization of a New, Noninvasive Model of Anterior Cruciate Ligament Rupture in the Rat
Biomechanical Characterization of a New, Noninvasive Model of Anterior Cruciate Ligament Rupture in the Rat Tristan Maerz, MS Eng 1, Michael Kurdziel, MS Eng 1, Abigail Davidson, BS Eng 1, Kevin Baker,
More informationA NEW DETAILED MULTI-BODY MODEL OF THE PEDESTRIAN LOWER EXTREMITY: DEVELOPMENT AND PRELIMINARY VALIDATION
A NEW DETAILED MULTI-BODY MODEL OF THE PEDESTRIAN LOWER EXTREMITY: DEVELOPMENT AND PRELIMINARY VALIDATION Jason Kerrigan, Dan Parent, Costin Untaroiu, Jeff Crandall, Bing Deng* University of Virginia Center
More informationCONTROL OF THE BOUNDARY CONDITIONS OF A DYNAMIC KNEE SIMULATOR
CONTROL OF THE BOUNDARY CONDITIONS OF A DYNAMIC KNEE SIMULATOR J. Tiré 1, J. Victor 2, P. De Baets 3 and M.A. Verstraete 2 1 Ghent University, Belgium 2 Ghent University, Department of Physical Medicine
More informationFlex-GTR: Proposal for ACL/PCL injury threshold
Flex-GTR: for ACL/PCL injury threshold 11th Meeting of the GRSP Flex PLI Technical Evaluation Group Bergisch Gladbach, April 21 st, 2010 Oliver Zander Bundesanstalt für Straßenwesen Bundesanstalt für Straßenwesen
More informationBiomechanics of the Knee. Valerie Nuñez SpR Frimley Park Hospital
Biomechanics of the Knee Valerie Nuñez SpR Frimley Park Hospital Knee Biomechanics Kinematics Range of Motion Joint Motion Kinetics Knee Stabilisers Joint Forces Axes The Mechanical Stresses to which
More informationSide Impact Crashworthiness Evaluation. Guidelines for Rating Injury Measures
Side Impact Crashworthiness Evaluation Guidelines for Rating Injury Measures October 2003 Side Impact Crashworthiness Evaluation Guidelines for Rating Injury Measures Injury measures obtained from instrumented
More informationNHTSA Evaluation of the Flex-GTR Legform on US Vehicles
NHTSA Evaluation of the Flex-GTR Legform on US Vehicles Brian Suntay & Ann Mallory Transportation Research Center Inc. Jason Stammen NHTSA Vehicle Research and Test Center 1 This is a work of the U.S.
More informationIntact and ACL-Deficient Knee MODEL Evaluation
Abstract The human knee joint has a three dimensional geometry with multiple body articulations that produce complex mechanical responses under loads that occur in everyday life and sports activities.
More informationInitial Fixation Strength of Bio-absorbable Magnesium Screw
Initial Fixation Strength of Bio-absorbable Magnesium Screw Joon Kyu Lee, MD, PhD, Sahnghoon Lee, Sang Cheol Seong, Myung Chul Lee, MD, PhD. Seoul National University College of Medicine, Seoul, Korea,
More informationCONTRIBUTING SURGEON. Barry Waldman, MD Director, Center for Joint Preservation and Replacement Sinai Hospital of Baltimore Baltimore, MD
CONTRIBUTING SURGEON Barry Waldman, MD Director, Center for Joint Preservation and Replacement Sinai Hospital of Baltimore Baltimore, MD System Overview The EPIK Uni is designed to ease the use of the
More informationMuscle-Tendon Mechanics Dr. Ted Milner (KIN 416)
Muscle-Tendon Mechanics Dr. Ted Milner (KIN 416) Muscle Fiber Geometry Muscle fibers are linked together by collagenous connective tissue. Endomysium surrounds individual fibers, perimysium collects bundles
More informationACL AND PCL INJURIES OF THE KNEE JOINT
ACL AND PCL INJURIES OF THE KNEE JOINT Dr.KN Subramanian M.Ch Orth., FRCS (Tr & Orth), CCT Orth(UK) Consultant Orthopaedic Surgeon, Special interest: Orthopaedic Sports Injury, Shoulder and Knee Surgery,
More informationDynamic full assembly certification test procedure (inverse test setup) in conjunction with functional test
Bundesanstalt für Straßenwesen (Federal Highway Research Institute) Dynamic full assembly certification test procedure (inverse test setup) in conjunction with functional test TEG-075 7th Meeting of the
More informationMasterclass. Tips and tricks for a successful outcome. E. Verhaven, M. Thaeter. September 15th, 2012, Brussels
Masterclass Tips and tricks for a successful outcome September 15th, 2012, Brussels E. Verhaven, M. Thaeter Belgium St. Nikolaus-Hospital Orthopaedics & Traumatology Ultimate Goal of TKR Normal alignment
More informationA Strain-Energy Model of Passive Knee Kinematics for the Study of Surgical Implantation Strategies
IN:Springer Lecture Notes in Computer Science 1935 A Strain-Energy Model of Passive Knee Kinematics for the Study of Surgical Implantation Strategies E. Chen R. E. Ellis J. T. Bryant Computing and Information
More informationAnisometry Anterior Cruciate Ligament Sport Injury Mechanism Study: A Finite Element Model with Optimization Method
Copyright 2014 Tech Science Press MCB, vol.11, no.2, pp.87-100, 2014 Anisometry Anterior Cruciate Ligament Sport Injury Mechanism Study: A Finite Element Model with Optimization Method Na Li, Wei Wang,
More informationIn the name of god. Knee. By: Tofigh Bahraminia Graduate Student of the Pathology Sports and corrective actions. Heat: Dr. Babakhani. Nov.
In the name of god Knee By: Tofigh Bahraminia Graduate Student of the Pathology Sports and corrective actions Heat: Dr. Babakhani Nov. 2014 1 Anatomy-Bones Bones Femur Medial/lateral femoral condyles articulate
More informationTEG th May th Flex-TEG Meeting JAMA/JARI
TEG-96 19 th May 29 8th Flex-TEG Meeting JAMA/JARI Development of a FE model and Analysis of the Correlation between the Flex- GTR-prototype and Human Lower Limb Outputs using Computer Simulation Models
More informationKnee Android Model Reproducing Internal-External Rotation with Screw-Home Movement of the Human Knee
Journal of Robotics, Networking and Artificial Life, Vol. 3, No. 2 (September 2016), 69-73 Knee Android Model Reproducing Internal-External Rotation with Screw-Home Movement of the Human Knee Daichi Yamauchi,
More informationCOLLATERAL LIGAMENT. Carlos Bonifasi-Lista. Master of Science. Department of Bioengineering. The University of Utah. December 2002
MULTIAXIAL VISCOELASTIC PROPERTIES OF HUMAN MEDIAL COLLATERAL LIGAMENT by Carlos Bonifasi-Lista A thesis submitted to the faculty of The University of Utah in partial fulfillment of the requirements for
More informationPosterolateral Corner Injuries of the Knee: Pearls and Pitfalls
Posterolateral Corner Injuries of the Knee: Pearls and Pitfalls Robert A. Arciero,MD,Col,ret Professor, Orthopaedics University of Connecticut Incidence of PLC Injuries with ACL Tears Fanelli, 1995 12%
More information.org. Tibia (Shinbone) Shaft Fractures. Anatomy. Types of Tibial Shaft Fractures
Tibia (Shinbone) Shaft Fractures Page ( 1 ) The tibia, or shinbone, is the most common fractured long bone in your body. The long bones include the femur, humerus, tibia, and fibula. A tibial shaft fracture
More informationIntroduction to Biomedical Engineering
Introduction to Biomedical Engineering FW 16/17, AUT Biomechanics of tendons and ligaments G. Rouhi Biomechanics of tendons and ligaments Biomechanics of soft tissues The major soft tissues in musculoskeletal
More informationThree-dimensional finite element analysis of the human ACL
Rhodes, Greece, August 0-, 008 Three-dimensional finite element analysis of the human ACL M.HAGHPANAHI, F.JALAYER Biomechanics Research Unit Iran University of Science and Technology Narmak, Tehran, 684634
More informationInformation on the Flexible Pedestrian Legform Impactor GT Alpha (Flex-GTa)
24 April 26 3 rd Flex-TEG MT BASt, Bergisch Information on the Flexible Pedestrian Legform Impactor GT Alpha (Flex-GTa) Atsuhiro Konosu Flex-TEG Chairperson /Japan Background At At the the 2 nd nd Flex-TEG
More informationA Finite Element Model of the Pelvis and Lower Limb for Automotive Impact Applications
12 th International LS-DYNA Users Conference Simulation(1) A Finite Element Model of the Pelvis and Lower Limb for Automotive Impact Applications Costin D. Untaroiu 1, Jaeho Shin 2, Neng Yue 2, Young-Ho
More informationKnee Injuries. PSK 4U Mr. S. Kelly North Grenville DHS. Medial Collateral Ligament Sprain
Knee Injuries PSK 4U Mr. S. Kelly North Grenville DHS Medial Collateral Ligament Sprain Result from either a direct blow from the lateral side in a medial direction or a severe outward twist Greater injury
More informationModeling And Biomechanical Analysis Of Human Knee Joint
Modeling And Biomechanical Analysis Of Human Knee Joint V Jeevan Kumar 1, P Satish Reddy 2,N Guru Murthy 3 PG Student, Assoc. Professor, Asst Professor Prasiddha College of Engg & Tech, Amalapuram jvankaya@yahoo.in,
More informationTRUMATCH PERSONALIZED SOLUTIONS with the SIGMA High Performance Instruments
TRUMATCH PERSONALIZED SOLUTIONS with the SIGMA High Performance Instruments Resection Guide System SURGICAL TECHNIQUE RESECTION GUIDE SURGICAL TECHNIQUE The following steps are an addendum to the SIGMA
More informationHuman ACL reconstruction
Human ACL reconstruction current state of the art Rudolph Geesink MD PhD Maastricht The Netherlands Human or canine ACL repair...!? ACL anatomy... right knees! ACL double bundles... ACL double or triple
More informationThe Development of the Lower Extremity of a Human FE Model and the Influence of Anatomical Detailed Modelling in Vehicle to Pedestrian Impacts
The Development of the Lower Extremity of a Human FE Model and the Influence of Anatomical Detailed Modelling in Vehicle to Pedestrian Impacts Shouhei Kunitomi, Yoshihiro Yamamoto, Ryosuke Kato, Jacobo
More informationA Finite Element Analysis of Mid-Shaft Femoral Tolerance under Combined Axial-Bending Loading
1 th International LS-DYNA Users Conference Simulation Technology (3) A Finite Element Analysis of Mid-Shaft Femoral Tolerance under Combined Axial-Bending Loading Costin Untaroiu, Dan Genovese, Johan
More informationDouble Bundle PCL Reconstruction. Surgical Technique
Double Bundle PCL Reconstruction Surgical Technique Double Bundle PCL Reconstruction With recent interest in double tunnel endoscopic PCL reconstruction, Arthrex has created a series of Femoral PCL Drill
More informationFatigue life prediction methodology of automotive rubber component. *Chang-Su Woo 1)
Fatigue life prediction methodology of automotive rubber component *Chang-Su Woo 1) 1) Department of Nano Mechanics, KIMM, Daejeon 305-345, Korea 1) cswoo@kimm.re.kr ABSTRACT Fatigue life prediction and
More informationReconstruction of the Ligaments of the Knee
Reconstruction of the Ligaments of the Knee Contents ACL reconstruction Evaluation Selection Evolution Graft issues Notchplasty Tunnel issues MCL PCL Posterolateral ligament complex Combined injuries Evaluation
More informationThe AperFix II System
The AperFix II System A Complete Anatomic Solution Transtibial Surgical Technique 2 AperFix II System Transtibial Surgical Technique Figure 1 A Complete Anatomic Solution The Cayenne Medical AperFix and
More informationShear loading of costal cartilage. Abstract. Introduction
Shear loading of costal cartilage Damien Subit, Jason Forman Center for Applied Biomechanics, University of Virginia, USA Abstract A series of tests were performed on a single post-mortem human subject
More informationNailing Stability during Tibia Fracture Early Healing Process: A Biomechanical Study
Nailing Stability during Tibia Fracture Early Healing Process: A Biomechanical Study Natacha Rosa, Fernão D. Magalhães, Ricardo Simões and António Torres Marques Enhanced Bone Healing in intramedullary
More informationAnterolateral Ligament. Bradd G. Burkhart, MD Orlando Orthopaedic Center Sports Medicine
Anterolateral Ligament Bradd G. Burkhart, MD Orlando Orthopaedic Center Sports Medicine What in the world? TIME magazine in November 2013 stated: In an age filled with advanced medical techniques like
More informationLateral knee injuries
Created as a free resource by Clinical Edge Based on Physio Edge podcast episode 051 with Matt Konopinski Get your free trial of online Physio education at Orthopaedic timeframes Traditionally Orthopaedic
More informationRevolution. Unicompartmental Knee System
Revolution Unicompartmental Knee System While Total Knee Arthroplasty (TKA) is one of the most predictable procedures in orthopedic surgery, many patients undergoing TKA are in fact excellent candidates
More informationCurriculum Vitae. Dr. J. Marcus Hollis, PhD, PE
Curriculum Vitae Dr. J. Marcus Hollis, PhD, PE Profession: Dr. Hollis is a bio-mechanical engineer specializing in biomechanics, injury causation, and seat belt effectiveness. He analyzes how the human
More informationThe Effect of Lateral Meniscal Root Injuries on the Stability of the Anterior Cruciate Ligament Deficient Knee
The Effect of Lateral Meniscal Root Injuries on the Stability of the Anterior Cruciate Ligament Deficient Knee Charles Vega 1, Jebran Haddad 1, Jerry Alexander 2, Jonathan Gold 2, Theodore Shybut 1, Philip
More informationESTIMATION OF ACL FORCES UTILIZING A NOVEL NON-INVASIVE METHODOLOGY THAT REPRODUCES KNEE KINEMATICS BETWEEN SETS OF KNEES. Shon Patrick Darcy
ESTIMATION OF ACL FORCES UTILIZING A NOVEL NON-INVASIVE METHODOLOGY THAT REPRODUCES KNEE KINEMATICS BETWEEN SETS OF KNEES by Shon Patrick Darcy BS, Walla Walla College, 2000 Submitted to the Graduate Faculty
More informationTorn ACL - Anatomic Footprint ACL Reconstruction
Torn ACL - Anatomic Footprint ACL Reconstruction The anterior cruciate ligament (ACL) is one of four ligaments that are crucial to the stability of your knee. It is a strong fibrous tissue that connects
More informationACL RECONSTRUCTION HAMSTRING METHOD. Presents ACL RECONSTRUCTION HAMSTRING METHOD. Multimedia Health Education
HAMSTRING METHOD Presents HAMSTRING METHOD Multimedia Health Education Disclaimer Stephen J. Incavo MD This movie is an educational resource only and should not be used to make a decision on Anterior Cruciate
More informationBIOMECHANICAL MECHANISMS FOR DAMAGE: RETRIEVAL ANALYSIS AND COMPUTATIONAL WEAR PREDICTIONS IN TOTAL KNEE REPLACEMENTS
Journal of Mechanics in Medicine and Biology Vol. 5, No. 3 (2005) 469 475 c World Scientific Publishing Company BIOMECHANICAL MECHANISMS FOR DAMAGE: RETRIEVAL ANALYSIS AND COMPUTATIONAL WEAR PREDICTIONS
More informationFirst Technology Safety Systems. Design Freeze Status. Flex-PLI-GTR Development
Based on TEG-047 29 Nov. 2007 JAMA-JARI JARI First Technology Safety Systems Design Freeze Status Flex-PLI-GTR Development Full Calibration Test Procedures Bernard Been FTSS Europe Comments addressed from
More informationBiomechanics of Two Reconstruction Techniques for Elbow Ulnar Collateral Ligament Insufficiency
Biomechanics of Two Reconstruction Techniques for Elbow Ulnar Collateral Ligament Insufficiency Justin E. Chronister, MD 1, Randal P. Morris, BS 2, Clark R. Andersen, MS 2, J. Michael Bennett, MD 3, Thomas
More informationDiscrepancies in Knee Joint Moments Using Common Anatomical Frames Defined by Different Palpable Landmarks
Journal of Applied Biomechanics, 2008, 24, 185-190 2008 Human Kinetics, Inc. Discrepancies in Knee Joint Moments Using Common Anatomical Frames Defined by Different Palpable Landmarks Dominic Thewlis,
More informationThe Lower Limb II. Anatomy RHS 241 Lecture 3 Dr. Einas Al-Eisa
The Lower Limb II Anatomy RHS 241 Lecture 3 Dr. Einas Al-Eisa Tibia The larger & medial bone of the leg Functions: Attachment of muscles Transfer of weight from femur to skeleton of the foot Articulations
More informationThe Knee. Prof. Oluwadiya Kehinde
The Knee Prof. Oluwadiya Kehinde www.oluwadiya.sitesled.com The Knee: Introduction 3 bones: femur, tibia and patella 2 separate joints: tibiofemoral and patellofemoral. Function: i. Primarily a hinge joint,
More informationZimmer FuZion Instruments. Surgical Technique (Beta Version)
Zimmer FuZion Surgical Technique (Beta Version) INTRO Surgical Technique Introduction Surgical goals during total knee arthroplasty (TKA) include establishment of normal leg alignment, secure implant fixation,
More informationPresenter: Mark Yeoman PhD Date: 19 October Research & Development, FEA, CFD, Material Selection, Testing & Assessment. Continuum Blue Ltd
Research & Development, FEA, CFD, Material Selection, Testing & Assessment Investigating the loading behaviour of intact & meniscectomy knee joints & the impact on surgical decisions M S Yeoman PhD 1 1.
More informationMultiapical Deformities p. 97 Osteotomy Concepts and Frontal Plane Realignment p. 99 Angulation Correction Axis (ACA) p. 99 Bisector Lines p.
Normal Lower Limb Alignment and Joint Orientation p. 1 Mechanical and Anatomic Bone Axes p. 1 Joint Center Points p. 5 Joint Orientation Lines p. 5 Ankle p. 5 Knee p. 5 Hip p. 8 Joint Orientation Angles
More informationThe Knee. Two Joints: Tibiofemoral. Patellofemoral
Evaluating the Knee The Knee Two Joints: Tibiofemoral Patellofemoral HISTORY Remember the questions from lecture #2? Girth OBSERVATION TibioFemoral Alignment What are the consequences of faulty alignment?
More informationARTICLE IN PRESS. Technical Note
Technical Note Hybrid Anterior Cruciate Ligament Reconstruction: Introduction of a New Technique for Anatomic Anterior Cruciate Ligament Reconstruction Darren A. Frank, M.D., Gregory T. Altman, M.D., and
More informationKnee Surgical Technique
Knee Surgical Technique COMPASS Universal Hinge by Jimmy Tucker, M.D. Orthopaedic Surgeon Director, Arkansas Sports Medicine, P.A. Little Rock, Arkansas Table of contents Design features 3 Indications
More informationDistal Cut First Femoral Preparation
Surgical Technique Distal Cut First Femoral Preparation Primary Total Knee Arthroplasty LEGION Total Knee System Femoral preparation Contents Introduction...3 DCF femoral highlights...4 Preoperative planning...6
More informationLoad-Displacement Characteristics of the Cervical Spine During Shear Loading
Load-Displacement Characteristics of the Cervical Spine During Shear Loading J.J. Dowling-Medley 1, R.J. Doodkorte 2, A.D. Melnyk 3, P.A. Cripton 1, T.R. Oxland 1,4 1 Department of Mechanical Engineering,
More information