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Автор: Grafiati
Опубліковано: 10 грудня 2022
Оновлено: 20 лютого 2023

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1

Hwang, Jaejin, Gregory G. Knapik, Jonathan S. Dufour, and William S. Marras. "A Comparison of Performance Between Straight-Line Muscle and Curved Muscle Models." Proceedings of the Human Factors and Ergonomics Society Annual Meeting 61, no. 1 (September 2017): 1339–40. http://dx.doi.org/10.1177/1541931213601817.

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Анотація:
The straight-line muscle biomechanical models of the lumbar spine have been utilized to predict spinal loads to assess the potential risk of work-related injuries. The curved muscle paths have been suggested to realistically simulate muscles’ behavior in complex lumbar motions. However, the effect of curved muscle paths on the modeling performances and spinal loads in the lumbar spine model during complex lifting exertions has not been fully investigated. The objective of this study was to characterize the differences in modeling performances and spinal loads between the conventional straight-line muscle model and the curved muscle model of the lumbar spine. Twelve subjects (6 males and 6 females) participated in this study. Mean values and standard deviations of age, body mass, and height of all subjects were 26.6 (5.3) years, 73.6 (13.3) kg, and 172.7 (5.4) cm, respectively. Electromyographic (EMG) activities with surface electrodes (Motion Lab Systems MA300-XVI, Baton Rouge, Louisiana, USA) were collected over 10 trunk muscles (pair of the latissimus dorsi, erector spinae, rectus abdominis, external oblique, and internal oblique) with 1000 Hz sampling rate. The OptiTrack optical motion capture system (NaturalPoint, Corvallis, OR, USA) with 24 Flex 3 infrared cameras was used to monitor whole body kinematics with 100 Hz sampling rate. A Bertec 4060A force plate (Bertec, Worthington, OH, USA) was used to measure ground reaction forces with 1000 Hz sampling rate. Customized Laboratory software via a National Instruments USB-6225 data acquisition board (National Instruments, Austin, TX, USA) was utilized to collect all signals simultaneously and efficiently run the model. Subjects performed complex lifting tasks by various load weight (9.1kg and 15.9kg), load origins (counterclockwise 90⁰, counterclockwise 45⁰, 0⁰, clockwise 45⁰, and clockwise 90⁰), and load height (mid-calf, mid-thigh, and shoulder). Both curved muscle model and straight-line muscle model were tested under same experiment conditions, respectively. The curved muscle model showed better model fidelity (average coefficient of determination (R2) = 0.83; average absolute error (AAE) = 14.4%) than the straight-line muscle model (R2 = 0.79; AAE = 20.7%), especially in upper levels of the lumbar spine. The curved muscle model showed higher R2 than the straight-line muscle model, and the T12/L1 level showed the biggest difference as 0.1. The curved muscle model had lower AAE than the straight-line muscle model, and the T12/L1 showed the biggest difference as 18%. The curved muscle model generally showed higher compression (up to 640N at T12/L1), lower anterior-posterior shear loads (up to 575N at T12/L1), and lower lateral shear loads (up to 521N at T12/L1) than the straight-line muscle model. The biggest difference in spinal loads between two models (especially in anterior-posterior shear and lateral shear loads) occurred at upper levels of the lumbar spine, which could be related to the amount of muscle curvatures at each spine level. The curved muscle model generally showed higher compression and lower anterior-posterior and lateral shear loads than the straight-line muscle model. It might be partially related to the muscle paths of the erector spinae (major power producing muscle). In curved muscle model, erector spinae was placed more parallel with the lumbar spine curvature than the straight-line muscle model. It could affect the spinal load distributions such as higher compression and lower shears loads in the curved muscle model compared to the straight-line muscle model. In conclusion, the improved performance of the curved muscle model indicated that the curved muscle approach would be advantageous to estimate precise spinal loads in complex lifting jobs compared to the straight-line muscle approach.
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2

Jorgensen, Michael J., William S. Marras, and Thomas R. Waters. "The Effect of a Variable Lumbar Erector Spinae Sagittal Plane Moment Arm on Predicted Spinal Loading." Proceedings of the Human Factors and Ergonomics Society Annual Meeting 46, no. 13 (September 2002): 1061–65. http://dx.doi.org/10.1177/154193120204601312.

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Анотація:
Recent research indicates that the sagittal plane moment arm of the erector spinae decreases at the L5/S1 level during torso flexion. The objective of this study was to assess the predicted L5/S1 spinal loading from a lifting task when allowing the erector spinae sagittal plane moment arm to vary during torso flexion. Nineteen male subjects lifted three loads from two origin locations to an upright neutral posture. Spinal loading was predicted from an EMG-assisted biomechanical model that allowed the erector spinae moment arm to vary during torso flexion. The predicted lateral, anterior-posterior shear and compression forces increased by 7.4%, 11.1% and 6.6%, respectively, when compared to using a biomechanical model that kept the erector spinae moment arm constant. These results suggest that models that account for the varying erector spinae moment arm predict greater spinal loads, especially for motions that involve a large degree of torso flexion.
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3

Rohlmann, A., R. Petersen, V. Schwachmeyer, F. Graichen, and G. Bergmann. "Spinal loads during position changes." Clinical Biomechanics 27, no. 8 (October 2012): 754–58. http://dx.doi.org/10.1016/j.clinbiomech.2012.04.006.

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4

Rohlmann, Antonius, Friedmar Graichen, and Georg Bergmann. "Influence of load carrying on loads in internal spinal fixators." Journal of Biomechanics 33, no. 9 (September 2000): 1099–104. http://dx.doi.org/10.1016/s0021-9290(00)00075-0.

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5

Rohlmann, A., G. Bergmann, F. Graichen, and U. Weber. "Loads on internal spinal fixation devices." Der Orthopäde 28, no. 5 (May 1999): 451–57. http://dx.doi.org/10.1007/pl00003629.

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6

Afaunov, Asker Alievich, Vladimir Dmitryevich Usikov, Ali Ibragimovich Afaunov, Igor Mikhailovich Dunaev, Nikolay Sveridovich Gavryushenko, Aleksey Viktorovich Mishagin, and Karapet Karapetovich Takhmazyan. "COMPARATIVE STUDY OF ROTATIONAL STABILITY PARAMETERS OF TRANSPEDICULAR SPINAL FUSION IN EXPERIMENT." Hirurgiâ pozvonočnika, no. 3 (August 23, 2005): 025–32. http://dx.doi.org/10.14531/ss2005.3.25-32.

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Анотація:
Objectives. To estimate macroscopically the strength, rigidity and limit of elasticity in the “spinal segments – transpedicular fixator” system. versus similar characteristics of the intact spine under dislocating rotational loads. Material and Methods. Еxperiments with anatomic specimens of Th12–L2 segments were performed. Unstable damages of L1 and transpedicular fixation with 4 screw transpedicular spinal system were imitated. All specimens were exposed to the testing rotational load in universal test machine Zwick 1464. Results. It is established that under rotational load general strength of the injured Th12–L1–L2 spinal segments fused with transpedicular fixator is 20 % lower than that in a corresponding intact spine segment. Rigidity parameters of fused segments are 17.5 % lower than those of intact segments. Destabilization of «spinal segments – transpedicular fixator» system under rotational loads is caused by the compression of a bone substance in Th12 and L2 bodies with screws and a turn of screws around longitudinal rods due to a rod slip in anchoring elements. Conclusion. The performed study may serve a basis for following data analysis from a viewpoint of metal resistance and for development of optimal rehabilitation loads to the injured spine during postoperative period.
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7

Behjati, Mohamad, and Navid Arjmand. "Biomechanical Assessment of the NIOSH Lifting Equation in Asymmetric Load-Handling Activities Using a Detailed Musculoskeletal Model." Human Factors: The Journal of the Human Factors and Ergonomics Society 61, no. 2 (September 17, 2018): 191–202. http://dx.doi.org/10.1177/0018720818795038.

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Анотація:
Objective: To assess adequacy of the National Institute for Occupational Safety and Health (NIOSH) Lifting Equation (NLE) in controlling lumbar spine loads below their recommended action limits during asymmetric load-handling activities using a detailed musculoskeletal model, that is, the AnyBody Modeling System. Background: The NIOSH committee employed simplistic biomechanical models for the calculation of the spine compressive loads with no estimates of the shear loads. It is therefore unknown whether the NLE would adequately control lumbar compression and shear loads below their recommended action limits during asymmetric load-handling activities. Method: Twenty-four static stoop lifting tasks at different load asymmetry angles, heights, and horizontal distances were performed by one normal-weight (70 kg) and one obese (93 kg) individual. For each task, the recommended weight limit computed by the NLE and body segment angles measured by a video-camera system (VICON) were prescribed in the participant-specific models developed in the AnyBody Modeling System that estimated spinal loads. Results: For both individuals, the NLE adequately controlled L5-S1 loads below their recommended action limits for all activities performed in upright postures. Both individuals, however, experienced compressive and/or shear L5-S1 loads beyond the recommended action limits when lifting was performed near the floor with large load asymmetry. Conclusion: The NLE failed to control spinal loads below the recommended limits during asymmetric lifting tasks performed near the floor. Application: The NLE should be used with caution for extreme tasks involving load handling near the floor with large load asymmetry.
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8

Afaunov, A. A., V. D. Usikov, A. I. Afaunov, and I. M. Dunaev. "Stability of Injured Spine in Relation to Bending Loads under Conditions of Transpedicular Osteosynthesis (Experimental Study)." N.N. Priorov Journal of Traumatology and Orthopedics 11, no. 3 (September 15, 2004): 23. http://dx.doi.org/10.17816/vto200411323.

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Анотація:
Study of T9—L3 spinal segment blocks using anatomic preparations has showed that in instable injury of T12 the rigidity of T11—L1 segments under conditions of transpedicular osteosynthesis with four screws spinal system is on average 25% and 14.7% lower than the normal rigidity of the intact T11—L1 segments in relation to bending kyphotic loads and lateral bending loads, respectively. The rigidity of synthesized spinal segments to lateral bending loads is 1.9 times lower than the rigidity to sagittal bending loads. With use of metalwork the rigidity indices of the synthesized spinal segments are on average 1.2 times higher as compared with the rigidity of the intact spine.
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9

Izzo, R., A. A. Diano, F. Lacquaniti, F. Zeccolini, and M. Muto. "Biomechanics of the Spine II." Rivista di Neuroradiologia 18, no. 5-6 (December 2005): 592–605. http://dx.doi.org/10.1177/197140090501800511.

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Анотація:
Spine biomechanics represents a traditional area of research by orthopaedists, neurosurgeons, bioengineers and physicists. Working in an emergency setting and managing spinal traumas every day we began a study on extended literature devoted to biomechanics of the spine, to see beyond the usual static evaluation of neuroimaging patterns. After our earlier paper on biomechanics of the spine16, we have reviewed and broadened some topics such as the role of the ligaments and introduced the main mechanisms of primary spinal traumas and deformations. The spine is a multiarticular complex structure controlled by the muscles whose correct function presupposes its stability. Several “stability factors” ensure spinal stability and correct movements. A number of biomechanical studies analysed the contribution of individual bony and soft spinal elements to stability and the effects of traumas. Several theories have been derived from these studies to account for the distribution of loads and vector forces, including failure-producing loads, among the components of functional spinal units (FSU). Holdsworth's initial two column concept, the three column models by Louis and Denis up to most recent four column theory by Cartolari all represent evolutions in assessing the distribution of loads and the presence and degree of instability in spinal traumas. Whether acute or chronic spinal instability means a partial or complete loss of one or both functions of the spine: load-bearing and cord protection. The diagnosis of spinal instability is crucial to establish the most appropriate strategy of management, namely in acute conditions. Biomechanical concepts are fundamental to understand the factors deciding the type, location and extent of spinal traumas, possible instability and the primary mechanism of the main types of injuries.
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10

Rohlmann, Antonius, Thomas Zander, Friedmar Graichen, Hendrik Schmidt, and Georg Bergmann. "Spinal Loads during Cycling on an Ergometer." PLoS ONE 9, no. 4 (April 17, 2014): e95497. http://dx.doi.org/10.1371/journal.pone.0095497.

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11

KIM BURTON, A., K. MALCOLM TILLOTSON, and MARK G. BOOCOCK. "Estimation of spinal loads in overhead work." Ergonomics 37, no. 8 (August 1994): 1311–21. http://dx.doi.org/10.1080/00140139408964910.

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12

Dennis, G. J., and R. S. Barrett. "Spinal loads during individual and team lifting." Ergonomics 45, no. 10 (August 2002): 671–81. http://dx.doi.org/10.1080/00140130210148537.

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13

Rohlmann, Antonius, Verena Schwachmeyer, Friedmar Graichen, and Georg Bergmann. "Spinal Loads during Post-Operative Physiotherapeutic Exercises." PLoS ONE 9, no. 7 (July 7, 2014): e102005. http://dx.doi.org/10.1371/journal.pone.0102005.

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14

Srbinoska, H., M. Dreischarf, T. Consmüller, G. Bergmann, and A. Rohlmann. "Correlation between back shape and spinal loads." Journal of Biomechanics 46, no. 11 (July 2013): 1972–75. http://dx.doi.org/10.1016/j.jbiomech.2013.04.024.

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15

Triano, John, and Albert B. Schultz. "Loads Transmitted During Lumbosacral Spinal Manipulative Therapy." Spine 22, no. 17 (September 1997): 1955–64. http://dx.doi.org/10.1097/00007632-199709010-00003.

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16

Buttermann, G. R., R. D. Kahmann, J. L. Lewis, and D. S. Bradford. "An Experimental Method for Measuring Force on the Spinal Facet Joint: Description and Application of the Method." Journal of Biomechanical Engineering 113, no. 4 (November 1, 1991): 375–86. http://dx.doi.org/10.1115/1.2895415.

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Анотація:
A technique is described for measuring load magnitude and resultant load contact location in the facet joint in response to applied loads and moments, and the technique applied to the canine lumbar spine motion segment. Due to the cantilever beam geometry of the cranial articular process, facet joint loads result in surface strains on the lateral aspect of the cranial articular process. Strains were quantified by four strain gages cemented to the bony surface of the process. Strain measured at any one gage depended on the loading site on the articular surface of the caudal facet and on the magnitude of the facet load. Determination of facet loads during in vitro motion segment testing required calibration of the strains to known loads of various magnitudes applied to multiple sites on the caudal facet. The technique is described in detail, including placement of the strain gages. There is good repeatability of strains to applied facet loads and the strains appear independent of load distribution area. Error in the technique depends on the location of the applied facet loads, but is only significant in nonphysiologic locations. The technique was validated by two independent methods in axial torsion. Application of the technique to five in vitro canine L2–3 motion segments testing resulted in facet loads (in newtons, N) of 74 + / −23 N (mean + /−STD) in 2 newton-meter, Nm, extension, to unloaded in flexion. Lateral bending resulted in loads in the right facet of 40 + /− 32 N for 1 Nm right lateral bending and 54 + / − 29 N for 1 Nm left lateral bending. 4 Nm Torsion with and without 100 N axial compression resulted in facet loads of 92 + / − 27 N and 69 + / − 19 N, respectively. The technique is applicable to dynamic and in vivo studies.
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17

Kovacı, Halim, Ali Fatih Yetim, and Ayhan Çelik. "Biomechanical analysis of spinal implants with different rod diameters under static and fatigue loads: an experimental study." Biomedical Engineering / Biomedizinische Technik 64, no. 3 (May 27, 2019): 339–46. http://dx.doi.org/10.1515/bmt-2017-0236.

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Анотація:
Abstract Spinal implants are commonly used in the treatment of spinal disorders or injuries. However, the biomechanical analyses of them are rarely investigated in terms of both biomechanical and clinical perspectives. Therefore, the main purpose of this study is to investigate the effects of rod diameter on the biomechanical behavior of spinal implants and to make a comparison among them. For this purpose, three spinal implants composed of pedicle screws, setscrews and rods, which were manufactured from Ti6Al4V, with diameters of 5.5 mm, 6 mm and 6.35 mm were used and a bilateral vertebrectomy model was applied to spinal systems. Then, the obtained spinal systems were tested under static tension-compression and fatigue (dynamic compression) conditions. Also, failure analyses were performed to investigate the fatigue behavior of spinal implants. After static tension-compression and fatigue tests, it was found that the yield loads, stiffness values, load carrying capacities and fatigue performances of spinal implants enhanced with increasing spinal rod diameter. In comparison to spinal implants with 5.5 mm rods, the fatigue limits of implants showed 13% and 33% improvements in spinal implants having 6 mm and 6.35 mm rods, respectively. The highest static and fatigue test results were obtained from spinal implants having 6.35 mm rods among the tested implants. Also, it was observed that the increasing yield load and stiffness values caused an increase in the fatigue limits of spinal implants.
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18

Edwards, W. T., W. C. Hayes, I. Posner, A. A. White, and R. W. Mann. "Variation of Lumbar Spine Stiffness With Load." Journal of Biomechanical Engineering 109, no. 1 (February 1, 1987): 35–42. http://dx.doi.org/10.1115/1.3138639.

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Анотація:
Mechanical studies of the Functional Spinal Unit (FSU) in-vitro have shown that the slopes of the load-displacement curves increase with load. This nonlinearity implies that the stiffness of the FSU is not constant over the range of physiologic loads, and that measurements obtained for FSU specimens through the application of individual loads cannot be summed to predict the response of the specimens to combined loads. Both experimental and analytical methods were developed in the present study to better quantify the nonlinear FSU load-displacement response and to calculate the coupled stiffness of FSU specimens at combined states of load reflecting in-vivo conditions. Results referenced to the center of the vertebral body indicate that lumbar FSU specimens are stiffer in flexion than in extension, and that FSU specimens loaded in flexion are stiffer at high loads than at low loads. The importance of combined load testing and a nonlinear interpretation of load-displacement data is demonstrated.
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19

Dennis, G. J., and R. S. Barrett. "Spinal loads during two-person team lifting: effect of load mass distribution." International Journal of Industrial Ergonomics 32, no. 5 (November 2003): 349–58. http://dx.doi.org/10.1016/s0169-8141(03)00075-1.

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20

Ferrara, Lisa A., Illya Gordon, Madeline Coquillette, Ryan Milks, Aaron J. Fleischman, Shuvo Roy, Vijay K. Goel, and Edward C. Benzel. "A preliminary biomechanical evaluation in a simulated spinal fusion model." Journal of Neurosurgery: Spine 7, no. 5 (November 2007): 542–48. http://dx.doi.org/10.3171/spi-07/11/542.

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Анотація:
Object A preliminary in vitro biomechanical study was conducted to determine if the pressure at a bone graft–mortise interface and the load transmitted along a ventral cervical plate could be used as parameters to assess fusion status. Methods An interbody bone graft and a ventral plate were placed at the C3–4 motion segment in six fresh cadaveric goat spines. Polymethylmethacrylate (PMMA) was used to simulate early bone fusion at the bone graft site. The loads along the plate and the simultaneous pressures induced at the graft–endplate interfaces were monitored during simulated stages of bone healing. Each specimen was nondestructively tested in compression loading while the pressures and loads at the graft site were recorded continuously. Each specimen was tested under five conditions (Disc, Graft, Plate, PMMA, and Removal). Results The pressure at the interface of the bone graft and vertebral endplate did not change significantly with the addition of the ventral plate. The interface pressure and segmental stiffness did increase following PMMA augmentation of the bone graft (simulating an intermediate phase of bone fusion). The load transmitted along the ventral plate in compression increased after the addition of the bone graft, but decreased after PMMA augmentation. Thus, there was an increase in pressure at the graft–endplate interface and a decrease in load transferred along the ventral plate after the simulation of bone fusion. Upon removal of the ventral plate, the simulated fusion bore most of the axial load, thus explaining a further increase in graft site pressure. Conclusions These observations support the notions of load sharing and the redistribution of loads occurring during and after bone graft incorporation. In the clinical setting, these parameters may be useful in the assessment of fusion after spine surgery. Although feasibility has been demonstrated in this preliminary study, further research is needed.
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21

Granata, Kevin P., and William S. Marras. "A Biomechanical Assessment of Axial Twisting Exertions." Proceedings of the Human Factors and Ergonomics Society Annual Meeting 39, no. 10 (October 1995): 600–604. http://dx.doi.org/10.1177/154193129503901013.

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Axial twisting of the torso has been identified as a significant risk factor for occupationally related low-back disorders. The purpose of this investigation was to examine the influence of dynamic twisting parameters upon spinal load. Measured trunk moments and muscle activities were employed in a biomechanical model to determine loads on the lumbar spine. Spinal loads were examined as a function of dynamic torsional exertions under various conditions of force, velocity, position, and direction. Results demonstrate significant flexion-extension and lateral moments were generated during the twisting exertions. Muscle coactivity was significantly greater than equivalent levels measured during sagittal lifting exertions. Relative spinal compression during dynamic twisting exertions was twice that of static exertions. Spine loading also varied as a function of whether the trunk was twisted to the left or right, and the direction of applied torsion, i.e. clockwise versus counter-clockwise. The results may help explain, biomechanically, why epidemiological findings have repeatedly identified twisting as a risk factor for low-back disorder
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22

Davis, Kermit G., and William S. Marras. "Is Changing Box Weight an Effective Ergonomic Control?" Proceedings of the Human Factors and Ergonomics Society Annual Meeting 42, no. 12 (October 1998): 906–10. http://dx.doi.org/10.1177/154193129804201214.

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Анотація:
With the rising costs of low back injuries, one low cost ergonomic solution would be to reduce the weight. But, limited research has investigated how the worker interacts with the box. This study evaluated how lifting different box weights effects the trunk kinematics, horizontal moment arm, and resulting spinal loads. Fifteen participants lifted a box weighing 9.1, 11.8, 14.5, 17.2, 20.0, 29.9, 32.7, 35.4, 38.1, and 41.7 kg., from knee height, carried it a distance of five feet, and placed it on a shelf at elbow height. The present study quantifies the utility of reducing the weight lifted. Small changes in weight were found to only slightly influence the trunk kinematics and spinal loads. The accuracy of the spinal load estimates were found to be influenced by the trunk dynamics and changes in horizontal moment arm, especially for the lighter weights evaluated in this study. These results can be used to establish potential weight limits to assist in the ergonomic redesign of a manual material handling task.
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23

Rohlmann, Antonius, David Pohl, Alwina Bender, Friedmar Graichen, Jörn Dymke, Hendrik Schmidt, and Georg Bergmann. "Activities of Everyday Life with High Spinal Loads." PLoS ONE 9, no. 5 (May 27, 2014): e98510. http://dx.doi.org/10.1371/journal.pone.0098510.

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24

Briggs, Andrew M., Jaap H. van Dieën, Tim V. Wrigley, Alison M. Greig, Bev Phillips, Sing Kai Lo, and Kim L. Bennell. "Thoracic Kyphosis Affects Spinal Loads and Trunk Muscle Force." Physical Therapy 87, no. 5 (May 1, 2007): 595–607. http://dx.doi.org/10.2522/ptj.20060119.

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Анотація:
Background and Purpose Patients with increased thoracic curvature often come to physical therapists for management of spinal pain and disorders. Although treatment approaches are aimed at normalizing or minimizing progression of kyphosis, the biomechanical rationales remain unsubstantiated. Subjects Forty-four subjects (mean age [±SD]=62.3±7.1 years) were dichotomized into high kyphosis and low kyphosis groups. Methods Lateral standing radiographs and photographs were captured and then digitized. These data were input into biomechanical models to estimate net segmental loading from T2–L5 as well as trunk muscle forces. Results The high kyphosis group demonstrated significantly greater normalized flexion moments and net compression and shear forces. Trunk muscle forces also were significantly greater in the high kyphosis group. A strong relationship existed between thoracic curvature and net segmental loads (r =.85–.93) and between thoracic curvature and muscle forces (r =.70–.82). Discussion and Conclusion This study provides biomechanical evidence that increases in thoracic kyphosis are associated with significantly higher multisegmental spinal loads and trunk muscle forces in upright stance. These factors are likely to accelerate degenerative processes in spinal motion segments and contribute to the development of dysfunction and pain.
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25

Fathallah, Fadi A., William S. Marras, and Mohamad Parnianpour. "Three-Dimensional Spinal Loading during Complex Lifting Tasks." Proceedings of the Human Factors and Ergonomics Society Annual Meeting 40, no. 13 (October 1996): 661–65. http://dx.doi.org/10.1177/154193129604001317.

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Анотація:
Knowledge of the complex three-dimensional loads imposed on the spine during typical manual materials handling (MMH) tasks could provide more insights about the mechanical etiology of low back injuries in occupational settings. Comprehensive treatment of such information has been lacking. Most previous studies quantified spinal loading in terms of compressive forces alone. However, there is enough empirical and epidemiological evidence to indicate that the shear forces imposed on the spine may be more important than mere compression. Hence, the purpose of this study was to assess, in-vivo, the three-dimensional complex spinal loading associated with lifting tasks. Subjects performed simulated lifting tasks with varying workplace characteristic. An EMG-assisted model provided the continuous three-dimensional spinal loads. Asymmetric (complex) lifting tasks showed distinctive loading patterns from those observed under symmetric conditions. Simultaneous occurrences of spinal loads in all three directions (compression and shear forces) were patterns unique under the “risky” asymmetric lifting conditions. These situations could be identified and abated through proper workplace design. In conclusion, this approach allow the determination of the magnitudes and temporal occurrence(s) of complex spinal loading, and assess the sensitivity of these loading patterns to workplace characteristics.
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Rohlmann, Antonius, Friedmar Graichen, and Georg Bergmann. "Loads on an Internal Spinal Fixation Device During Physical Therapy." Physical Therapy 82, no. 1 (January 1, 2002): 44–52. http://dx.doi.org/10.1093/ptj/82.1.44.

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Abstract Background and Purpose. Modified internal spinal fixation devices allow the measurement of the forces and moments acting on the implants. The aim of this study was to measure the loads on internal fixation devices for selected body positions and movements during physical therapy. Subjects and Methods. Loads on an internal spinal fixation device were measured in 10 patients with degenerative instability or compression fractures using a telemeterized implant. Results. Relatively low implant loads were found in the recumbent body positions. Most exercises performed in a lying position caused implant loads less than that measured for standing and are therefore not likely to increase the risk of screw breakage. Fixation device loads were lower for sitting relaxed than for standing. The highest implant loads (128% of the value for standing) were measured during walking. Standing up, sitting down, and lateral bending and axial rotation of the upper body while standing led to fixation device loads between 111% and 120% related to the value for standing. Even higher fixation device loads were measured for ventral flexion and extension of the upper body while standing. Kneeling on hands and knees, and flexing and extending the back in this position, caused implant loads that were lower than for standing. Discussion and Conclusion. Standing up, sitting down, and lateral bending and axial rotation of the upper body while standing may slightly increase the risk of pedicle screw breakage, whereas ventral flexion and extension of the upper body while standing may increase this risk considerably if the region bridged by the implant is distracted (the distance between upper and lower screws was increased) during surgery. However, walking is the exercise that plays the major role concerning pedicle screw breakage because it causes the highest bending moments of all exercises studied and it loads the fixation devices most frequently.
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27

Grimston, Susan K., Jack R. Engsberg, Reinhard Kloiber, and David A. Hanley. "Bone Mass, External Loads, and Stress Fracture in Female Runners." International Journal of Sport Biomechanics 7, no. 3 (August 1991): 293–302. http://dx.doi.org/10.1123/ijsb.7.3.293.

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Increased incidence of stress fracture has been reported for amenorrheic runners, while some studies have reported decreased spinal bone mass in amenorrheic runners. Based on results from these studies, one tends to associate decreased spinal bone mass with an increased risk of stress fracture. The present study compared regional bone mass and external loads during running between six female runners reporting a history of stress fracture (seven tibial and three femoral neck) and eight female runners with no history of stress fracture. Dual photon absorptiometry measures indicated significantly greater spinal (L2-L4) and femoral neck bone mineral density in stress fracture subjects (p<0.05) but no differences between groups for tibial bone density. Normalized forces recorded from Kistler force plates indicated significantly greater vertical propulsive, maximal medial, lateral, and posterior forces for stress fracture subjects during running (p<0.05).
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28

Patwardhan, Avinash G., Kevin P. Meade, and Brian Lee. "A Frontal Plane Model of the Lumbar Spine Subjected to a Follower Load: Implications for the Role of Muscles." Journal of Biomechanical Engineering 123, no. 3 (December 21, 2000): 212–17. http://dx.doi.org/10.1115/1.1372699.

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Compression on the lumbar spine is 1000 N for standing and walking and is higher during lifting. Ex vivo experiments show it buckles under a vertical load of 80–100 N. Conversely, the whole lumbar spine can support physiologic compressive loads without large displacements when the load is applied along a follower path that approximates the tangent to the curve of the lumbar spine. This study utilized a two-dimensional beam–column model of the lumbar spine in the frontal plane under gravitational and active muscle loads to address the following question: Can trunk muscle activation cause the path of the internal force resultant to approximate the tangent to the spinal curve and allow the lumbar spine to support compressive loads of physiologic magnitudes? The study identified muscle activation patterns that maintained the lumbar spine model under compressive follower load, resulting in the minimization of internal shear forces and bending moments simultaneously at all lumbar levels. The internal force resultant was compressive, and the lumbar spine model, loaded in compression along the follower load path, supported compressive loads of physiologic magnitudes with minimal change in curvature in the frontal plane. Trunk muscles may coactivate to generate a follower load path and allow the ligamentous lumbar spine to support physiologic compressive loads.
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29

Pashman, Robert S., Serena S. Hu, Michael J. Schendel, and David S. Bradford. "Sacral Screw Loads in Lumbosacral Fixation for Spinal Deformity." Spine 18, no. 16 (December 1993): 2465–70. http://dx.doi.org/10.1097/00007632-199312000-00016.

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30

Pankoke, Steffen, Jörg Hofmann, and Horst P. Wölfel. "Determination of vibration-related spinal loads by numerical simulation." Clinical Biomechanics 16 (January 2001): S45—S56. http://dx.doi.org/10.1016/s0268-0033(00)00100-5.

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31

Rohlmann, Antonius, Ulrike Arntz, Friedmar Graichen, and Georg Bergmann. "Loads on an internal spinal fixation device during sitting." Journal of Biomechanics 34, no. 8 (August 2001): 989–93. http://dx.doi.org/10.1016/s0021-9290(01)00073-2.

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32

Han, Kap-Soo, Antonius Rohlmann, Thomas Zander, and William R. Taylor. "Lumbar spinal loads vary with body height and weight." Medical Engineering & Physics 35, no. 7 (July 2013): 969–77. http://dx.doi.org/10.1016/j.medengphy.2012.09.009.

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33

D’amico, M., P. Roncoletta, and M. Vallasciani. "Spinal intervertebral loads assessment in posture and gait analysis." Gait & Posture 33 (April 2011): S37. http://dx.doi.org/10.1016/j.gaitpost.2010.10.045.

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34

Rohlmann, Antonius, Georg Bergmann, and Friedmar Graichen. "Loads on an internal spinal fixation device during walking." Journal of Biomechanics 30, no. 1 (January 1997): 41–47. http://dx.doi.org/10.1016/s0021-9290(96)00103-0.

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35

Suri, Cazmon, Iman Shojaei, and Babak Bazrgari. "Effects of School Backpacks on Spine Biomechanics During Daily Activities: A Narrative Review of Literature." Human Factors: The Journal of the Human Factors and Ergonomics Society 62, no. 6 (July 12, 2019): 909–18. http://dx.doi.org/10.1177/0018720819858792.

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Objective The purpose of this narrative review is to summarize the effects of carrying school backpacks on spine and low-back biomechanics as a risk factor for low back pain in young individuals. Background Backpacks constitute a considerable daily load for schoolchildren. Consistently, a large number of children attribute their low back pain experience to backpack use. Method A literature search was conducted using a combination of keywords related to the impact of carrying backpacks on lower back biomechanics. The references of each identified study were further investigated to identify additional studies. Results Twenty-two studies met inclusion criteria. A total of 1,159 people aged 7 to 27 years were included in the studies. The added load of a backpack and the changes in spinal posture when carrying a backpack impose considerable demand on internal tissues and likely result in considerable spinal loads. The findings included results related to the effects of backpack weight and position on trunk kinematics and spine posture as well as trunk muscle activity during upright standing, walking, and ascending and descending stairs. Conclusion Backpack-induced changes in trunk kinematics for a given activity reflect alterations in mechanical demand of the activity on the lower back that should be balanced internally by the active and passive responses of lower back tissues. Although the reported alterations in trunk muscle activities and lumbar posture are indications of changes in the active and passive response of the lower back tissues, the resultant effects on spinal load, that is, an important causal factor for low back pain, remains to be investigated in the future. A knowledge of backpack-induced changes in spinal loads can inform design of interventions aimed at reduction of spinal load via improved backpack design or limitation on carrying duration. Application This narrative review is intended to serve as an educational article for students and trainees in ergonomics and occupational biomechanics.
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Cadel, Eileen, Ember Krech, Paul Arnold, and Elizabeth Friis. "Stacked PZT Discs Generate Necessary Power for Bone Healing through Electrical Stimulation in a Composite Spinal Fusion Implant." Bioengineering 5, no. 4 (October 23, 2018): 90. http://dx.doi.org/10.3390/bioengineering5040090.

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Electrical stimulation devices can be used as adjunct therapy to lumbar spinal fusion to promote bone healing, but their adoption has been hindered by the large battery packs necessary to provide power. Piezoelectric composite materials within a spinal interbody cage to produce power in response to physiological lumbar loads have recently been investigated. A piezoelectric macro-fiber composite spinal interbody generated sufficient power to stimulate bone growth in a pilot ovine study, despite fabrication challenges. The objective of the present study was to electromechanically evaluate three new piezoelectric disc composites, 15-disc insert, seven-disc insert, and seven-disc Compliant Layer Adaptive Composite Stack (CLACS) insert, within a spinal interbody, and validate their use for electrical stimulation and promoting bone growth. All implants were electromechanically assessed under cyclic loads of 1000 N at 2 Hz, representing physiological lumbar loading. All three configurations produced at least as much power as the piezoelectric macro-fiber composites, validating the use of piezoelectric discs for this application. Future work is needed to characterize the electromechanical performance of commercially manufactured piezoelectric stacks under physiological lumbar loads, and mechanically assess the composite implants according to FDA guidelines for lumbar interbody fusion devices.
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37

Zander, Thomas, Marcel Dreischarf, Hendrik Schmidt, Georg Bergmann, and Antonius Rohlmann. "Spinal loads as influenced by external loads: A combined in vivo and in silico investigation." Journal of Biomechanics 48, no. 4 (February 2015): 578–84. http://dx.doi.org/10.1016/j.jbiomech.2015.01.011.

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38

Yang, Gang, Riley Splittstoesser, Gregory Knapik, David Trippany, Sahika Vatan Korkmaz, Jeffry Hoyle, Parul Lahoti, Steven Lavender, Caroline Sommerich, and William Marras. "Comparison of Spinal Loads in Kneeling and Standing Postures during Manual Materials Handling." Proceedings of the Human Factors and Ergonomics Society Annual Meeting 49, no. 14 (September 2005): 1320–24. http://dx.doi.org/10.1177/154193120504901412.

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Kneeling in a restricted posture during manual materials handling has been associated with increased risk of low back pain. Little is known about the effect of kneeling posture on spinal loads. The purpose of this study was to compare differences in spinal loading between kneeling and standing postures for lifting tasks. Twelve subjects asymmetrically lifted luggage of three weights to three heights from floor while kneeling. Three subjects also performed the same tasks from waist height while standing. An adapted free-dynamic EMG-assisted biomechanical model was used to calculate spinal loads. Statistical analysis showed that there was no difference in compression between kneeling and standing (p=0.9605), but kneeling resulted in increased anterior-posterior and lateral shear forces on the lumbar spine (p =0.0002 and p<0.0001, respectively). Spinal loading changes while kneeling in a restricted posture may increase the risk of low back injury and must be considered in ergonomic job design.
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39

Maiman, Dennis J., Anthony Sances, Sanford J. Larson, Joel B. Myklebust, Michael A. Chilbert, Sam P. Nesemann, and Thomas J. Flatley. "Comparison of the Failure Biomechanics of Spinal Fixation Devices." Neurosurgery 17, no. 4 (October 1, 1985): 574–80. http://dx.doi.org/10.1227/00006123-198510000-00007.

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Abstract The failure biomechanics of Harrington distraction rods, modified Weiss springs, and Luque rods were studied in intact cadavers and isolated spinal columns using flexion-compression loading. Most spines fractured at T-11 or T-12 at applied loads ranging between 556 and 4220 newtons (mean = 1833 N). After Harrington distraction rod placement, the same spines failed at a mean load of 859 N (42% of control), always as a result of hook extrusion and often including lamina fracture (seven cases). When modified Weiss springs were used, the spines failed at a mean load of 1128 N (54% of control) by allowing the spine to bend to the initial failure angle; in most instances, deformities resolved when the load was reduced. Luque rods were tested in four specimens; these provided the most rigid stabilization and failed at 83% of control values. Modified Weiss springs often maintain spinal stability better than Harrington distraction rods.
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40

Brownlee, WJ, DR Altmann, P. Alves Da Mota, JK Swanton, KA Miszkiel, CAM Gandini Wheeler-Kingshott, O. Ciccarelli, and DH Miller. "Association of asymptomatic spinal cord lesions and atrophy with disability 5 years after a clinically isolated syndrome." Multiple Sclerosis Journal 23, no. 5 (August 1, 2016): 665–74. http://dx.doi.org/10.1177/1352458516663034.

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Background: Spinal cord pathology is an important substrate for long-term disability in multiple sclerosis (MS). Objective: To investigate longitudinal changes in spinal cord lesions and atrophy in patients with a non-spinal clinically isolated syndrome (CIS), and how they relate to the development of disability. Methods: In all, 131 patients with a non-spinal CIS had brain and spinal cord imaging at the time of CIS and approximately 5 years later (median: 5.2 years, range: 3.0–7.9 years). Brain magnetic resonance imaging (MRI) measures consisted of T2-hyperintense and T1-hypointense lesion loads plus brain atrophy. Spinal cord MRI measures consisted of lesion number and the upper cervical cord cross-sectional area (UCCA). Disability was measured using the Expanded Disability Status Scale (EDSS). Multiple linear regression was used to identify independent predictors of disability after 5 years. Results: During follow-up, 93 (71%) patients were diagnosed with MS. Baseline spinal cord lesion number, change in cord lesion number and change in UCCA were independently associated with EDSS ( R2 = 0.53) at follow-up. Including brain T2 lesion load and brain atrophy only modestly increased the predictive power of the model ( R2 = 0.64). Conclusion: Asymptomatic spinal cord lesions and spinal cord atrophy contribute to the development of MS-related disability over the first 5 years after a non-spinal CIS.
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41

Weston, Eric B., Alexander Aurand, Jonathan S. Dufour, Gregory G. Knapik, and William S. Marras. "Spinal Loading During One and Two-Handed Lifting." Proceedings of the Human Factors and Ergonomics Society Annual Meeting 63, no. 1 (November 2019): 1126–27. http://dx.doi.org/10.1177/1071181319631067.

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Background: Lifting at work remains one of the most highly studied potential risk factors for low back disorders, but most of the studies that have been conducted on this topic focus on lifting scenarios in which two hands are used to lift the weight. Few investigations have examined one-handed lifting scenarios, as might be observed when lifting objects from industrial storage bins or stocking products onto shelves. Moreover, there remains a need to re-examine one versus two-handed lifting scenarios utilizing a more advanced and accurate biomechanical model than was used previously (Ferguson et al., 2002; Kingma and van Dieen, 2004; Marras and Davis, 1998). The objective of this study was to quantify biomechanical loads imposed upon the lumbar spine during one-handed lifting versus two-handed lifting, specifically in relation to any interaction effects present between the number of hands used to perform the lift and external lifting conditions like the lift origin or object weight. Methods: Thirty subjects (15 male, 15 female) were recruited for this laboratory study. In each experimental task, subjects lifted one of three medicine balls (of the same size/shape but differing in weight) with either one or two hands from the lift origin predefined by the study design to a common lift destination directly in front of the body. All one-handed exertions were performed with the dominant hand, and asymmetric conditions were tested on the dominant side of the body. Independent variables included lift origin height (ankle, knee, waist), lift origin asymmetry (0 degrees, 45 degrees, 90 degrees), load weight (2.7 kg, 7.3 kg, 11.4 kg), horizontal distance of the lift origin from the body (40 cm, 70 cm), and the number of hands used to perform the lift (one, two). An EMG-driven biomechanical spine model was implemented to evaluate lumbar spinal loads in compression, anterior/posterior (A/P) shear, and lateral shear (Dufour et al., 2013; Hwang et al., 2016a, 2016b). Results and Discussion: One-handed lifting resulted in 6% lower spinal compression and 16% lower A/P shear loads than two-handed lifting on average, but lateral shear was increased by 23% for one-handed lifting relative to two-handed lifting (p<0.001). Consistent with Marras and Davis (1998), spinal compression increased with increased lift origin asymmetry in two-handed lifting but decreased with increased lift origin asymmetry in one-handed lifting (p<0.001). The effects of using one versus two hands to perform the lift were generally amplified at lower lift origin heights, lower weights, and for the far reach distance. Effects were likely driven by differing moment exposures on the spine attributable to the weight of the torso. Conclusion: One-handed lifting resulted in lower peak spinal compression and peak A/P shear loads on the lumbar spine, so it may be preferred to two-handed lifting if the load to be lifted falls within the strength capabilities of the worker population. However, while this study shows benefits of one-handed lifting for the low back, these results should be placed in context with future studies aimed at assessing the impacts of one-handed lifting on the upper extremity. Acknowledgement: This study was funded, in part, by the Ohio Bureau of Workers’ Compensation.
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42

Davis, Kermit G. "The Effect of Lifting vs. Lowering on Spinal Loading." Proceedings of the Human Factors and Ergonomics Society Annual Meeting 40, no. 13 (October 1996): 599–603. http://dx.doi.org/10.1177/154193129604001304.

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In industry, workers perform tasks requiring both lifting and lowering. During concentric lifting, the muscles are shortening as the force is being generated. Conversely, the muscle lengthens while generating force during eccentric lowering. While research on various lifting tasks is extensive, there has been limited research performed to evaluate the lowering tasks. Most of the research that does exist on lowering has investigated muscle activity and trunk strength. None of these studies have investigated spinal loading. The current study estimated the effects of lifting and lowering on spinal loads and predicted moments imposed on the spine. Ten subjects performed both eccentric and concentric lifts under sagittally symmetric conditions. The tasks were performed under isokinetic trunk velocities of 5, 10, 20, 40, and 80 deg/s while holding a box with weights of 9.1, 18.2, and 27.3 kg. Spinal loads and predicted moments in three dimensional space were estimated by an EMG-assisted model which has been adjusted to incorporate the artifacts of eccentric lifting. Eccentric strength was found to be 56 percent greater than during concentric lifting. The lowering tasks produced significantly higher compression forces but lower anterior-posterior shear forces than the concentric lifting tasks. The differences in the spinal loads between the two lifting tasks were attributed to the internal muscle forces and unequal moments resulting from differences in the lifting path of the box. Thus, the differences between the lifting tasks resulted from different lifting styles associated with eccentric and concentric movements
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43

Davis, K. G., W. S. Marras, C. A. Heaney, and A. B. Maronitis. "Influence of Job Stress on Muscle Activity and Spinal Loads." Proceedings of the Human Factors and Ergonomics Society Annual Meeting 44, no. 29 (July 2000): 5–59. http://dx.doi.org/10.1177/154193120004402916.

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44

MCGILL, S. M., M. T. SHARRATT, and J. P. SEGUIN. "Loads on spinal tissues during simultaneous lifting and ventilatory challenge." Ergonomics 38, no. 9 (September 1995): 1772–92. http://dx.doi.org/10.1080/00140139508925226.

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45

Granata, Kevin P., and W. S. Marras. "The Influence of Trunk Muscle Coactivity on Dynamic Spinal Loads." Spine 20, no. 8 (April 1995): 913–19. http://dx.doi.org/10.1097/00007632-199504150-00006.

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46

Lim, Young-Tae, John W. Chow, and Woen-Sik Chae. "Lumbar spinal loads and muscle activity during a golf swing." Sports Biomechanics 11, no. 2 (June 2012): 197–211. http://dx.doi.org/10.1080/14763141.2012.670662.

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47

Rohlmann, A., G. Bergmann, F. Graichen, and G. Neff. "Braces do not reduce loads on internal spinal fixation devices." Clinical Biomechanics 14, no. 2 (February 1999): 97–102. http://dx.doi.org/10.1016/s0268-0033(98)00056-4.

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48

Arjmand, N., A. Plamondon, A. Shirazi-Adl, C. Larivière, and M. Parnianpour. "Predictive equations to estimate spinal loads in symmetric lifting tasks." Journal of Biomechanics 44, no. 1 (January 2011): 84–91. http://dx.doi.org/10.1016/j.jbiomech.2010.08.028.

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49

Fathallah, Fadi A., William S. Marras, and Mohamad Parnianpour. "An Assessment of Complex Spinal Loads During Dynamic Lifting Tasks." Spine 23, no. 6 (March 1998): 706–16. http://dx.doi.org/10.1097/00007632-199803150-00012.

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50

WEI YANG, SAI, NOSHIR A. LANGRANA, and CASEY K. LEE. "Biomechanics of Lumbosacral Spinal Fusion in Combined Compression-Torsion Loads." Spine 11, no. 9 (November 1986): 937–41. http://dx.doi.org/10.1097/00007632-198611000-00014.

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