Sci Rep. 2016 (Dec 1); 6: 38107 ~ FULL TEXT
Martha Funabashi, Gregory N. Kawchuk, Albert H. Vette,
Peter Goldsmith, and Narasimha Prasad
Department of Physical Therapy,
University of Alberta,
Edmonton, AB, Canada.
Spinal manipulative therapy (SMT) creates health benefits for some while for others, no benefit or even adverse events. Understanding these differential responses is important to optimize patient care and safety. Toward this, characterizing how loads created by SMT relate to those created by typical motions is fundamental. Using robotic testing, it is now possible to make these comparisons to determine if SMT generates unique loading scenarios. In 12 porcine cadavers, SMT and passive motions were applied to the L3/L4 segment and the resulting kinematics tracked. The L3/L4 segment was removed, mounted in a parallel robot and kinematics of SMT and passive movements replayed robotically. The resulting forces experienced by L3/L4 were collected. Overall, SMT created both significantly greater and smaller loads compared to passive motions, with SMT generating greater anterioposterior peak force (the direction of force application) compared to all passive motions. In some comparisons, SMT did not create significantly different loads in the intact specimen, but did so in specific spinal tissues. Despite methodological differences between studies, SMT forces and loading rates fell below published injury values. Future studies are warranted to understand if loading scenarios unique to SMT confer its differential therapeutic effects.
From the FULL TEXT Article:
Spinal manipulative therapy (SMT) is a clinical intervention for low back pain which, by some estimates, is the most frequently used form of complementary and alternative medicine (CAM).  Similarly, SMT is also one of the most studied CAM interventions with over 250 systematic reviews and 550 randomized controlled trials since 2000.
Unfortunately, this volume of literature is polarized, with an almost equal number of publications describing the benefit of SMT or its lack of therapeutic effect. Toward understanding this discrepancy, recent studies have suggested that some forms of low back pain respond to SMT while others do not. Specifically, SMT creates significant changes in spinal stiffness, muscle response and disc diffusion in SMT responders while these same changes are not observed in SMT non-responders.  In addition, approximately 3050% of persons who receive SMT experience some kind of benign adverse event that typically self-resolves in 2448 hours , with a minority of patients experiencing serious adverse events.  However, causation in these cases remains controversial. [7, 912]
To better understand this range of therapeutic responses in persons receiving SMT, it is important to understand the loads that are imparted to the spine as a result of SMT application. In response, we have developed a robotic technique that is capable of quantifying the in-situ loads experienced by spinal segments as well as specific spinal tissues. By robotically replicating the same kinematics experienced during SMT and sequentially removing specific spinal tissues between kinematic replication, the change in loading following spinal tissue removal can be considered to be the load experienced by that specific tissue. Using this approach, we have shown that, during the application of SMT on the skin overlying the L3 transverse process, the intervertebral disc is the spinal structure that experiences the greatest loads. 
While this approach can determine the load distribution within spinal tissues affected by SMT, we do not yet understand the importance of the magnitude of these loads. Specifically, we lack a frame of reference to understand whether these loads are larger, smaller or equal to those experienced by the spine during everyday motions. Having this comparison is fundamental toward identifying if unique spinal loads arise from SMT. If unique SMT loads exist compared to those arising in typical spinal motion, then it may be these loads that confer the beneficial (or harmful) effects of SMT. While previous investigations have reported vertebral motion, intradiscal pressure and spinal loading as a result of SMT  or typical spine movements [16, 17], methodological differences between these investigations preclude the direct comparison of biomechanical characteristics (e.g., spinal loading) during SMT application and typical movements. Therefore, a unified investigation of spinal loading during the application of both SMT and typical movements in one study within a single model using a standardized testing protocol is needed to identify if SMT provides unique loading features.
Given the above, the objective of this study was to compare loads in a lumbar spine segment arising from SMT and passive spinal movements (flexion, extension and axial rotation) using an established cadaveric model. We hypothesized the existence of significantly different forces arising from SMT when compared to those arising from passive movements.
Sample Size Calculation
A sample size calculation was conducted based on the data previously reported by Kawchuk and colleagues (2010)13 using the General Power Analysis Program (G*Power 2) (University of Trier, Germany). With statistical power set to 80%, a two-tailed test having a level of significance at 0.05 (5%) and an effect size of 0.991.2, a sample size of 9 was calculated. Five additional specimens were included to account for possible specimen loss due to testing complications, resulting in 14 cadaveric porcine specimens tested. All experimental protocols of this study were approved by the Animal Care and Use Committee of the University of Alberta.
Fourteen fresh porcine cadavers (Duroc X [Large White X Landrace breeds]) of approximately 6065 kg were included in this study. In each intact cadaver, ultra-sound imaging and needle probing were used to identify the L3 and L4 vertebrae and the L3/L4 left facet joint (FJ). Bone pins were drilled into the L3 and L4 vertebral bodies and a rectangular flag having 4 infrared light-emitting diode markers was attached to the upper end of each bone pin (Figure 1).
Each cadaveric pig was then positioned in a neutral, prone position on a hinged hardwood board that was fixed to a flexion-extension table (Leander Health Technologies, Lawrence, KS). The L3 and L4 vertebrae were positioned above and below the hinge line, respectively, and the cadaver fixed to the table by a strap around the lower thoracic region.  SMT was applied with the cadaver in this orientation. To apply passive movements, the portion of the cadaver superior to the hinge (L3) was kept stationary while the portion of the cadaver located inferior to the hinge (L4) was moved. Following the application of SMT and passive lumbar movements on the intact porcine cadaver (detailed in the following sections), the lumbar spine was removed en bloc.  The L3/L4 spinal segment was cleaned of non-ligamentous tissues, sealed in a plastic bag and kept refrigerated at 3 °C for less than 5 hours until potting and testing on the following day.  The specimen was kept moist with physiologic saline throughout preparation, embedding and testing. [20, 21] Due to complications in robotic calibration for attaining neutral position alignment, two specimens were excluded and, therefore, data from 12 specimens were analyzed. Given the fragile nature of the intertransverse ligaments and their frequent damage during en bloc spinal removal, all specimens had their intertransverse ligaments removed prior to testing. All methods in this study were performed in accordance with the NIH Guide for the Care and Use of Laboratory Animals.
Application of SMT
A trained clinician with 3 years of clinical experience was instructed to apply SMT using a hypothenar push manipulation in which the pisiform bone of the clinicians hand was positioned on the skin of the specimen overlying the left L3/L4 FJ.  To measure SMT force-time characteristics, a pressure array (Pressure Profile System, Inc. Los Angeles, CA) was placed between the clinicians hands and the cadaver skin. The pressure array was composed of 10 Χ 10 pressure sensors with a pressure sensitivity of 0.15% and a recording rate of 120 Hz.
Application of passive motion
Three passive lumbar movements were performed: flexion, extension and left axial rotation. Passive flexion movement was performed by the automatic flexion movement of the flexion-extension table where the table was moved mechanically to a maximum of 20° of flexion at an approximate rate of 0.8°/s (Figure 2). Passive extension was performed by manually moving both lower limbs in an upward direction at an average rate of 5°/s until the maximum extension between the L3/L4 segment was reached and the L2/L3 segment started to move visually (Figure 3). Passive left axial rotation was performed by manually stabilizing L3 and manually rotating the pelvis to the left side at an average rate of 3°/s until the maximum range of rotation was reached and the L3 bone pin began to rotate visually (Figure 4). Each passive lumbar movement was performed twice, and the data from the second movement was used for analysis.
Passive flexion movement
performed by the automatic flexion
movement of the flexion-extension
movement performed by manually
moving both lower limbs in the
Passive left axial rotation
movement performed by manually
stabilizing L3 and manually rotating
the pelvis to the left side.
Segmental motion recording
During the application of SMT and passive lumbar movement, the resulting motions of the L3 and L4 vertebrae were recorded by an optical tracking system (Optotrak Certus, NDI, Waterloo, Canada) in 3 dimensions at a rate of 400 Hz with a 0.01 mm system resolution and a 0.15 mm rigid body resolution.
After application of SMT and passive motions, the L3/L4 motion segment was removed as described previously, and the specimen potted in a vertical orientation using dental stone (Modern Materials, South Bend, IN) with the intervertebral disc positioned parallel to the horizontal plane as aligned by a projected laser beam. The caudal end (L4) of the potted spinal segment was fixed to a 6axis load cell (AMTI MC3A-1000, Advanced Mechanical Technology, Inc., Watertown, MA), which was mounted rigidly to a parallel robot platform (Parallel Robotics Systems corp., Hampton, NH), such that the anatomical axes of the specimen aligned with both the load cell axes and the robot axes as follows: x = mediolateral, y = anterioposterior, and z = superioinferior.
To calibrate the system, a series of known translations and rotations were provided to the robot and the resulting change in position of the optical markers on L4 recorded. This calibration provided the position and orientation of the L4 marker set with respect to the robotic platform.
The cranial end of the potted specimen was then fixed to a stationary cross beam and the segment positioned in the same position and orientation recorded previously from the cadavers intact neutral pose (Figure 5). By following the procedures described by Goldsmith et al. , the marker movements caused by SMT and each of the 3 passive motion were then transformed into robot trajectories that replicated the relative motions between L3 and L4 vertebrae recorded by the optical tracking system. These 4 trajectories were then applied by the robot in the order that the corresponding procedures were applied to the porcine cadaver, and forces experienced by the spinal segment were recorded by the load cell. Starting from the initial neutral position as obtained from the intact cadaver, passive lumbar movements were replicated first, followed by the SMT. Each applied trajectory was separated by a 2 minute recovery time with 3 pre-conditioning trials executed prior to testing and data collection. 
Potted spinal segment with L4
mounted to the 6axis load cell and L3
fixed to a stationary cross beam.
Following application of all robotic trajectories in the intact specimen, spinal structures were then removed and/or transected and the same robotic trajectories repeated. In this way, the loading distribution within specific spinal tissues was quantified. Based on the findings reported by Funabashi et al. , the following spinal structures were removed/transected (via scalpel unless otherwise noted) in the same order for all specimens: 1) supraspinous and interspinous ligaments (SL), 2) bilateral facet capsules, posterior facet joints (via rongeur) and ligamentum flavum (posterior joints, PJ), 3) intervertebral disc and anterior and posterior longitudinal ligaments (IVD).
For the SMT application, pressure data was plotted against time for each porcine cadaver by using the software provided by the manufacturer (Chameleon Visualization and Data Acquisition Software 2012, Version 220.127.116.11, Pressure Profile Systems. Inc., Los Angeles, CA). Maximum applied force and time to peak were extracted by the software and used for SMT force-time characterization.
For robotic kinematic replication, the resulting forces of each specimen were plotted against time. Peak and mean forces along each axis were identified by customized software (LabVIEW, National Instruments, Austin, TX). Peak force was considered to be the maximum measured force during the entirety of each applied trajectory. Mean forces corresponded to the average value of forces involving both the loading and unloading phase of each passive movement as well as preload and thrust phases of SMT. Using the same axis definitions as for the forces (see Robotic Testing), the values of L4 rotations relative to L3 where peak loads occurred were taken from the rotations of the robotic platform for each of the 4 trajectories.
Given that all passive lumbar movements and SMT application were performed in all specimens, each observation of forces generated during SMT and passive lumbar movements was considered to be a repeated measure. Although the data was not distributed normally, a repeated measures multivariate analysis of variance (MANOVA) was performed due to its robustness to non-normal data  followed by a Bonferroni post-hoc analysis for pairwise comparisons using IBM SPSS Statistics for Windows, Version 22.0 (Armonk, NY: IBM Corp.). Statistical significance was set at an alpha value of 0.05.
Spinal manipulative therapy characteristics
From pressure system recordings, SMT provided an average peak force magnitude of 524 N (SD: ±41 N), with a time to peak of 220 ms (±15 ms). This resulted in an average loading rate of 2.38 N/ms).
Rotations of L4 vertebrae relative to L3 at peak loads are shown in Table 1, stratified by the applied motion and the axis of rotation. These rotations are represented as Cardan angles in the rotation sequence of XYZ about the fixed axes. In general, rotations caused by SMT were significantly greater compared to passive motions. This was specifically the case for passive flexion where the rotation about each axis was not only significantly different from SMT, but opposite in direction (with the exception of rotation around z-axis, which had equal direction to SMT). Given that flexion and extension are opposite motions, this finding was expected; that is, SMT could not create similar motion as both flexion and extension.
Intact Specimen Forces
For general orientation, Figure 6 shows a representative example of the raw forces (along y-axis) created by SMT and passive motions in a single, intact L3/L4 segment. Providing more detail, Table 2 presents the peak and mean forces for all specimens during SMT application and passive lumbar movements. Table 2 additionally displays statistical comparisons between SMT and passive movements of which there were 4 comparisons that were statistically significant, with all 4 having greater specific forces created during SMT. Among these 4 comparisons, 3 were notable in that the peak force created by SMT was in the anterioposterior direction and was significantly greater compared to the peak force generated by any of the passive lumbar movements (Figure 7).
Serial Dissection Loading Distribution
Given that the objective of this study was to compare SMT to passive lumbar movements, we will not comment on results showing significant differences between the 3 passive movements; however, these results are displayed in Figure 8.
Our serial dissection results demonstrated that although forces generated by SMT were not always significantly different from passive motions in the intact specimen, SMT sometimes created significantly different forces in specific tissues. In other words, the intact specimen may experience forces from SMT that are not significantly greater than passive movements, but in that same axis, specific spinal tissues may experience greater forces from SMT compared to one or more passive motions.
Overall, SMT created forces measured in distinct spinal tissues that were greater than those created by each of the passive motions. Specifically, SMT created significantly different forces in comparison to all passive motions in 2 cases (red boxes, 6 comparisons, Figure 8). Of note, compared to all passive movements, SMT created significantly greater mean forces in the supraspinous and interspinous ligaments (SL) structures in the superioinferior direction.
Among these comparisons, some are of note in that SMT created significantly different forces in both specific tissues and the intact specimen. Specifically, SMT caused significantly greater peak anterioposterior forces in comparison to all three passive motions in the intact specimen while in specific tissues, SMT created significantly greater forces than passive flexion and axial rotation in the IVD structures and significantly smaller forces than passive extension in the IVD structures (Figure 8).
Additionally, SMT also caused significantly different tissue loading than (i) two of three passive motions (yellow boxes, 8 comparisons, Figure 8) and (ii) one of three passive motions (navy boxes, 6 comparisons, Figure 8).
This study aimed to quantify and compare the forces experienced by spinal segments of a porcine cadaveric model during the application of SMT and passive lumbar movements. Our results support our stated hypothesis; SMT created unique loads when compared to passive lumbar movements of flexion, extension and left axial rotation. Interestingly, SMT generated loads within one specific axis (anteroposterior) that were greater than those created in the same axis by any of the three passive motions tested. This axis, the anteroposterior axis, was the direction in which the SMT was applied. In addition, SMT also created loading conditions that in some cases were significantly increased in the intact specimen as well as in individual spinal tissues (IVD structures). In other cases, SMT loading conditions were no different than passive motions in the intact specimen, but significantly different for a distinct spinal tissue. Although prior studies have investigated loading created during lumbar movement [16, 26] and SMT application , this is the first study to quantify and compare the loads arising from both passive lumbar movement and SMT in a unified study with comparable specimens and testing protocol. Given that SMT appears to provide loading environments which are different from passive movements, it may be these unique SMT loads that confer its various effects, beneficial or otherwise.
SMT force-time characteristics measured here were found to be similar to those reported by previous investigations. [27, 28] Likewise, the time for SMT application to reach peak force as well as the SMT loading rate are also in agreement with previous research.  These comparisons suggest that SMT applied in this experiment was representative of SMT applications performed on human subjects.
In addition, the relative vertebral motions observed during SMT in this current study (Table 1) are similar to those of our prior study  which used a similar animal model. In both studies, the greatest relative rotation was observed around the z-axis (torsion). With respect to vertebral motions measured by other groups, Gal et al.  observed significant relative flexion extension rotations (0.21.8°) during SMT application in unembalmed human cadavers. These comparisons suggest that, like the SMT application parameters measured in this study, the resulting vertebral kinematics arising from SMT are similar between porcine and human cadavers. [33, 34] Importantly, such comparisons should be made with caution as coordinate systems between studies may differ. Given these cautions, relative vertebral rotations observed during both SMT and passive lumbar movements (Table 1) generally remained within ranges reported in the literature. 
As unique SMT loads occurred in both the intact segment as well as in specific tissues, it is possible that the physiological effects of SMT are tissue specific. Indirect support for this idea comes from prior studies showing that SMT creates unique strain patterns in facet joints compared to physiological axial rotation , and that specific tissue properties change in those who are SMT responders.  Similarly, particular spines, spinal conditions, or tissues (e.g., degenerative spine or tissues) may not be impacted by these same loads which may help to explain SMT non-responders or when adverse events occur following SMT. Future studies are planned to investigate how these specific loads may influence specific physical responses.
Of note, the approach used in this study not only permits identification of unique SMT loads compared to passive motions, but to also observe if loads created by SMT exceed known thresholds for tissue injury. Previous investigations using finite element models have shown that high loading rates increase the risk of spinal structures injury  as a result of the viscoelastic behavior of spinal structures. Specifically, Wang et al.  assessed slow (0.6 N/ms and 0.003°/ms) and fast loading rates (6.6 N/ms and 0.03°/ms) of combined compression and flexion movements and found that high loading rates increased intradiscal pressure as well as forces and moments experienced by spinal structures. Additionally, El-Rich et al.  investigated spine flexion and extension using three loading rates (0.05°/ms, 0.5°/ms and 5°/ms) and found that spinal injuries, such as bone fracture and ligament failure, can occur in loading rates higher than 0.5°/ms. Further, Wagnac et al.  applied flexion, extension, anterior and posterior shear at low (0.1 m/s) and high rates (1.0 m/s for compression and 4.0 m/s for flexion and extension) and observed that loading rate significantly influenced spinal injury site. In the current study, SMT was applied with loading and rotation rates (2.38 N/ms, 0.04 m/s and 0.014°/ms) which are near or below the lower loading rates used in the abovementioned studies.
Additionally, the estimated stiffness of the L3/L4 spinal segment arising from SMT application was also smaller in magnitude when compared to the magnitude of stiffness observed to occur immediately before spinal injury.  Specifically, our data allows us to estimate L3/L4 spinal stiffness during SMT to be 0.33 Nm/deg in extension and 1.51 Nm/deg in axial rotation; values that are smaller than the extension stiffness described by Garges et al.  of 10 Nm/deg and torsion stiffness described by Bisschop et al.  of 5.7 Nm/deg.
Despite the greater anterioposterior forces created by SMT when compared to passive lumbar motion, the magnitudes of forces experienced during SMT are considerably smaller than those reported in previous research that investigated porcine spinal structural failure at 800 N to 8700 N.  Although the comparison between anterioposterior forces between the current study and previous investigations is limited due to methodological differences, anterioposterior forces created by SMT did not exceed 40 N.
It is important to note that, although the loading rates, stiffness values and load magnitudes obtained in this study fall below injury thresholds reported previously, our data cannot be used to suggest SMT is safe and/or would be unlikely to cause injury as our experiment was not constructed to assess SMT safety. Indeed, although porcine lumbar spine models have been described to be suitable models to investigate the human spine [33, 34], anatomical and biomechanical differences exist which also include a lack of biologically active tissues in our model (i.e., muscle). Therefore, extrapolation of these results to human living subjects is limited. Additionally, given the results reported by Funabashi et al. , our observations are specific to the order in which spinal structures were removed from the specimen; a different order of tissue removal may affect the loads recorded within each spinal tissue, but not the results obtained for the intact specimen. Further, to avoid potential confounding factors due to viscoelastic behaviour [55, 56], this study standardized the order of robotic kinematic replication: passive movements were replicated first followed by the SMT. In this way, potential experimental differences due to changes in water content were standardized among specimens. In addition, although the processes used to perform passive movements were not quantified for their reliability, increased variability in passive motion application would make it more likely that loads created by SMT were similar to those created by passive movements the opposite of our findings. Finally, as SMT was provided by a single clinician in this study, these results cannot be generalized to other clinicians or to all SMT techniques.
This study was supported by funding from the Canadian Institutes of Health Research (CIHR # TIR-112758), Alberta References Innovates Health Solutions (AIHS # 20111389) and Women and Childrens Health Research Institute (WCHRI # RES0013182). GNK is supported by the Canadian Research Chair Program.
M.F. contributed to data collection, data analysis and interpretation and manuscript writing. G.K. contributed to data collection, data interpretation and manuscript writing. A.V. contributed to data interpretation and manuscript writing. P.G. contributed to data interpretation and manuscript writing. N.P. contributed to data analysis and manuscript writing. All authors reviewed the manuscript.
The Use of Complementary and Alternative Medicine in the United States.
Wong AYL, Parent EC, Dhillon SS, Prasad N, Kawchuk GN.
Do Participants with Low Back Pain who Respond to Spinal Manipulative Therapy Differ Biomechanically
From Nonresponders, Untreated Controls or Asymptomatic Controls?
Spine (Phila Pa 1976). 2015 (Sep 1); 40 (17): 13291337
Fritz J. M. et al. .
Preliminary Investigation of the Mechanisms Underlying the Effects of Manipulation:
Exploration of a Multivariate Model Including Spinal Stiffness, Multifidus
Recruitment, and Clinical Findings
Spine (Phila Pa 1976). 2011 (Oct 1); 36 (21): 1772-1781
Beattie P. F., Butts R., Donley J. W. & Liuzzo D. M.
The Within-Session Change in Low Back Pain Intensity Following Spinal Manipulative Therapy Is Related to Differences in Diffusion of Water in the Intervertebral Discs of the Upper Lumbar Spine and L5-S1.
J. Orthop. Sport. Phys. Ther. 44, 1929 (2014)
Paanalahti K. et al. .
Adverse events after manual therapy among patients seeking care for neck and/or back pain: a randomized controlled trial.
BMC Musculoskelet. Disord. 15, 77 (2014)
Cagnie B, Vinck E, Beernaert A, et al.
How Common Are Side Effects of Spinal Manipulation And Can These Side Effects Be Predicted?
Manual Therapy 2004 (Aug); 9 (3): 151156
Carnes D., Mars T. S., Mullinger B., Froud R. & Underwood M.
Adverse events and manual therapy: A systematic review.
Man. Ther. 15, 355363 (2010)
Adverse effects of spinal manipulation: a systematic review.
J. R. Soc. Med. 100, 330338 (2007)
Hebert J. J., Stomski N. J., French S. D. & Rubinstein S. M.
Serious Adverse Events and Spinal Manipulative Therapy of the Low Back Region: A Systematic Review of Cases.
J. Manipulative Physiol. Ther. (2013)
Gouveia L. O., Castanho P. & Ferreira J. J.
Safety of chiropractic interventions: a systematic review.
Spine (Phila. Pa. 1976). 34, E405E413 (2009)
Safety of Spinal Manipulation in the Treatment of Lumbar Disk Herniations:
A Systematic Review and Risk Assessment
J Manipulative Physiol Ther 2004 (Mar); 27 (3): 197210
Walker, BF, Hebert, JJ, Stomski, NJ et al.
Outcomes of Usual Chiropractic. The OUCH Randomized Controlled Trial of Adverse Events
Spine (Phila Pa 1976). 2013 (Sep 15); 38 (20): 17231729
Kawchuk G. N., Carrasco A., Beecher G., Goertzen D. & Prasad N.
Identification of spinal tissues loaded by manual therapy: a robot-based serial dissection technique applied in porcine motion segments.
Spine (Phila. Pa. 1976). 35, 198390 (2010)
Lisi A. J. et al. .
Measurement of in vivo lumbar intervertebral disc pressure during spinal manipulation: a feasibility study.
J. Appl. Biomech. 22, 2349 (2006)
Keller TS, Colloca CJ, Gunzburg R.
Neuromechanical Characterization of in vivo Lumbar Spinal Manipulation.
Part I. Vertebral Motion
J Manipulative Physiol Ther. 2003 (Nov); 26 (9): 567578
Rohlmann a, Zander T., Rao M. & Bergmann G.
Realistic loading conditions for upper body bending.
J. Biomech. 42, 88490 (2009)
Yang G., Marras W. S. & Best T. M.
The biochemical response to biomechanical tissue loading on the low back during physical work exposure.
Clin. Biomech. (Bristol, Avon) 26, 4317 (2011)
Kaigle A., Holm S. & Hansson T.
Kinematic Behaviour of the Porcine Lumbar Spine: A Chronic Lesion Model.
Spine (Phila. Pa. 1976). 22, 27962806 (1997)
Changoor A., Fereydoonzad L., Yaroshinsky A. & Buschmann M. D.
Effects of refrigeration and freezing on the electromechanical and biomechanical properties of articular cartilage.
J. Biomech. Eng. 132, 064502 (2010)
Lee R. Y. & Evans J. H.
The role of spinal tissues in resisting posteroanterior forces applied to the lumbar spine.
J. Manipulative Physiol. Ther. 23, 5516 (2000)
Gillespie K. a. & Dickey J. P.
Biomechanical role of lumbar spine ligaments in flexion and extension: determination using a parallel linkage robot and a porcine model.
Spine (Phila. Pa. 1976). 29, 120816 (2004)
Descarreaux M. & Dugas C.
Learning Spinal Manipulation Skills: Assessment of Biomechanical Parameters in a 5-Year Longitudinal Study.
J. Manipulative Physiol. Ther. 33, 226230 (2010)
Goldsmith P., Wynd S. & Kawchuk G.
Robotic measurement and control for chiropractic research.
Appl. Bionics Biomech. 3, 4348 (2006).
Funabashi M., El-Rich M., Prasad N. & Kawchuk G. N.
Quantification of loading in biomechanical testing: the influence of dissection sequence.
J. Biomech. 48, 35223526 (2015)
Yatim B. & Ismail S.
MANOVA versus alternative methods.
AIP Conf. Proc. 1635, 934939 (2014).
Bakker E. W. P. et al. .
Daily spinal mechanical loading as a risk factor for acute non-specific low back pain: A case-control study using the 24-Hour Schedule.
Eur. Spine J. 16, 107113 (2007)
Descarreaux M., Dugas C., Lalanne K., Vincellete M. & Normand M. C.
Learning spinal manipulation: The importance of augmented feedback relating to various kinetic parameters.
Spine J. 6, 138145 (2006)
Downie AS, Vemulpad S, Bull PW:
Quantifying the High-velocity, Low-amplitude Spinal Manipulative Thrust: A Systematic Review
J Manipulative Physiol Ther. 2010 (Sep); 33 (7): 542-53
Forand D., Drover J. Z. S., Symons B.& Herzog W.
The forces applied by female and male chiropractors during thoracic spinal manipulation.
J. Manipulative Physiol. Ther. 27, 4956 (2004)
Gudavalli M. R.
Instantaneous rate of loading during manual high-velocity, low-amplitude spinal manipulations.
J. Manipulative Physiol. Ther. 37, 294299 (2014)
Descarreaux M., Dugas C., Treboz J., Cheron C. & Nougarou F.
Learning Spinal Manipulation: The Effect of Expertise on Transfer Capability.
J. Manipulative Physiol. Ther. 38, 269274 (2015)
Gal J., Herzog W., Kawchuk G., Conway P. & Zhang Y.-T.
Movements of vertebrae during manipulative thrusts to unembalmed human cadavers.
J. Manipulative Physiol. Ther. 20, 3040 (1997)
Busscher I. et al. .
In vitro biomechanical characteristics of the spine: a comparison between human and porcine spinal segments.
Spine (Phila. Pa. 1976). 35, E3542 (2010)
Wilke H.-J., Geppert J. & Kienle A.
Biomechanical in vitro evaluation of the complete porcine spine in comparison with data of the human spine.
Eur. Spine J. 20, 185968 (2011)
Kozanek M. et al. .
Range of motion and orientation of the lumbar facet joints in vivo.
Spine (Phila. Pa. 1976). 34, E68996 (2009)
Li G. et al. .
Segmental in vivo vertebral motion during functional human lumbar spine activities.
Eur. Spine J. 18, 101321 (2009)
Passias P. G. et al. .
Segmental lumbar rotation in patients with discogenic low back pain during functional weight-bearing activities.
J. Bone Joint Surg. Am. 93, 2937 (2011)
Wheeler D. J. et al. .
Inter-laboratory variability in in vitro spinal segment flexibility testing.
J. Biomech. 44, 23837 (2011)
Heuer F., Schmidt H., Klezl Z., Claes L. & Wilke H.-J.
Stepwise reduction of functional spinal structures increase range of motion and change lordosis angle.
J. Biomech. 40, 27180 (2007)
Panjabi M. M., Krag M. H. & Chung T. Q.
Effects of disc injury on mechanical behavior of the human spine.
Spine 9, 707713 (1984)
Heuer F., Schmidt H., Claes L. & Wilke H. J.
Stepwise reduction of functional spinal structures increase vertebral translation and intradiscal pressure.
J. Biomech. 40, 795803 (2007)
Okushima Y. et al. .
Lateral translation of the lumbar spine: In vitro biomechanical study.
J. Appl. Biomech. 22, 8392 (2006)
Freudiger S., Dubois G. & Lorrain M.
Dynamic neutralisation of the lumbar spine confirmed on a new lumbar spine simulator in vitro.
Arch. Orthop. Trauma Surg. 119, 127132 (1999)
Ianuzzi A. & Khalsa P. S.
High loading rate during spinal manipulation produces unique facet joint capsule strain patterns compared with axial rotations.
J. Manipulative Physiol. Ther. 28, 67387 (2005)
El-Rich M., Arnoux P. J., Wagnac E., Brunet C. & Aubin C. E.
Finite element investigation of the loading rate effect on the spinal load-sharing changes under impact conditions.
J. Biomech. 42, 12521262 (2009)
Wang J. L., Parnianpour M., Shirazi-Adl a. & Engin a. E.
Viscoelastic finite-element analysis of a lumbar motion segment in combined compression and sagittal flexion. Effect of loading rate.
Spine (Phila. Pa. 1976). 25, 310318 (2000)
Wagnac E., Arnoux P.-J., Garo A. & Aubin C.-E.
Finite element analysis of the influence of loading rate on a model of the full lumbar spine under dynamic loading conditions.
Med. Biol. Eng. Comput. 50, 903915 (2012)
Schmidt H. et al. .
Computational biomechanics of a lumbar motion segment in pure and combined shear loads.
J. Biomech. 46, 25132521 (2013)
Garges K. J. et al. .
A Comparison of the Torsional Stiffness of the Lumbar Spine in Flexion and Extension.
J. Manipulative Physiol. Ther. 31, 563569 (2008)
Bisschop A. et al. .
Torsion biomechanics of the spine following lumbar laminectomy: A human cadaver study.
Eur. Spine J. 22, 17851793 (2013)
Lu W. W., Luk K. D. K., Holmes A. D., Cheung K. M. C. & Leong J. C. Y.
Pure shear properties of lumbar spinal joints and the effect of tissue sectioning on load sharing.
Spine (Phila. Pa. 1976). 30, E2049 (2005)
van Dieλn J. H., van der Veen A., van Royen B. J. & Kingma I.
Fatigue failure in shear loading of porcine lumbar spine segments.
Spine (Phila. Pa. 1976). 31, E4948 (2006)
Baranto A. et al. .
Fracture patterns of the adolescent porcine spine: an experimental loading study in bending-compression.
Spine (Phila. Pa. 1976). 30, 7582 (2005)
Thoreson O. et al. .
The immediate effect of repeated loading on the compressive strength of young porcine lumbar spine. Knee Surg. Sports Traumatol.
Arthrosc. 18, 694701 (2010)
Sopakayang R. & De Vita R.
A mathematical model for creep, relaxation and strain stiffening in parallel-fibered collagenous tissues.
Med. Eng. Phys. 33, 105663 (2011)
Chimich D., Shrive N., Frank C., Marchuk L. & Bray R.
Water content alters viscoelastic behaviour of the normal adolescent rabbit medial collateral ligament.
J. Biomech. 25, (1992)
Return to LOW BACK PAIN
Return to DISC HERNIATION & CHIROPRACTIC