This study sponsored by the National Natural Science Foundation of China (81772423), K. C. Wong Magna Fund in Ningbo University, and the National Key R&#38;D Program of China (2018YFF0300903).

Written informed consent was obtained from subjects and the testing procedures were approved by the university ethics committee. All participants were informed of the requirements and process of the trial.
1. Laboratory preparation
<ol>
	<li>During calibration, switch off the lights and remove other possibly reflective objects. Ensure that eight cameras are appropriately placed and have a clear view without re&#64258;ection.</li>
	<li>Open the Vicon Nexus 1.8.5 program, and then initialize the cameras. Select System | Local System | MX Cameras in the Resources pane and the cameras will engage. 
	NOTE: In the Properties pane, the parameters need to be adjusted. The range of values of the strobe intensity are adjusted to 0.95-1, and the value range of the threshold is set to 0.2-0.4. Set the grayscale mode to Auto. The Minimum circularity ratio is set to 0.5, and the Gain to times 1 (x1), the Max blob height to 50, and select Enable LEDs.</li>
	<li>Place the T-frame in the center of the capture area, select all the cameras in the system, and use 2D mode. Confirm that the T-frame is in the camera view without any interference points. Select the first item System Preparation in the toolbar. In the T-Frame drop-down list, select the 5 Marker Wand &#38; T-Frame calibration object.</li>
	<li>In the System Preparation Tools pane, click the Start button under the Mask Cameras section. Then click the Start button under Calibrate MX camera section. 
	NOTE: When the calibration process is completed, the progress bar is restored to 0%.</li>
	<li>Place the T-frame in the center of the camera to establish the origin of the coordinates.</li>
	<li>In the Tool pane, click the Start button under the Set Volume Origin section.</li>
	<li>Put the treadmill in the center of the test zone. The eight cameras are displayed around the treadmill (Figure 1).</li>
	<li>Attach a total of 22 reflective markers (diameter: 14 mm) with double-sided tape on the subjects in advance.</li>
</ol>
<img alt="Figure 1" class="xfigimg" src="/files/ftp_upload/61192/61192fig1.jpg" /> 
Figure 1: Test site layout. Cameras capture lower-limb motion while the subjects run on the treadmill. <a href="https://www.jove.com/files/ftp_upload/61192/61192fig1large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
2. Subject preparation
<ol>
	<li>Before the test, interview subjects in the laboratory and give a simple explanation of the experimental procedures. Then, have the participants complete a questionnaire. Summarize the results of these questionnaires.
	<ol>
		<li>Use the following questions:
		<ol>
			<li>How often do you run in a week?</li>
			<li>How many years have you been running for?</li>
			<li>Have you suffered any lower extremity injuries or received lower extremity surgeries in the last six months?</li>
			<li>How many kilometers do you run per week?</li>
		</ol>
		</li>
	</ol>
	</li>
	<li>Use the following inclusion criteria: all participants were right leg dominant and without any lower extremity injuries in the previous six months before the study. All participants ran at least 15 km per week. 
	NOTE: Ten healthy recreational female runners (ages: 23.4&#177;1.3 years; height: 160.7&#177;3.8 cm; mass: 50.3&#177;2.3 kg; running years: 3.2&#177;1.2 years) were selected.
	<ol>
		<li>Obtain written informed consent from participants who meet the inclusion criteria.</li>
	</ol>
	</li>
	<li>Require that participants wear uniform tights and pants.</li>
	<li>Record the subjects&#8217; height (mm), weight (kg), lower limb length (mm), knee width (mm) and ankle width (mm) for the statistics model.</li>
	<li>Place 16 reflective markers on subjects at the following locations: anterior-superior iliac spine, posterior-superior iliac spine, lateral mid-thigh, lateral knee, lateral mid-shank, lateral malleolus, second metatarsal head, and calcaneus. Place the markers on the second metatarsal head and calcaneus on the corresponding anatomical points of the socks and shoes.</li>
	<li>Instruct the participants to wear uniform sport running shoes. Have the participants warm up with light running and stretching for 5 min.</li>
</ol>
3. Static calibration
<ol>
	<li>Click the Data Management button on the toolbar, select Data Management. Click the New Database tab on the toolbar, select the location, describe the trial name and the Clinical Template, and click the create button.</li>
	<li>In the Open Database window, select the name of the database that was created. In the open interface, click the green New Patient Classification button, the yellow New Patient button, and the grey New session button to create the experimental information including subject type, subject name, and different action status.
	<ol>
		<li>Go back to the Nexus pane, in the left toolbar, click Subjects to create a New Subject data set, and choose the trial model. In the Properties pane, fill in all the anthropometric measurements: height (mm), weight (kg), lower limb length (mm), knee width (mm) and ankle width (mm).</li>
	</ol>
	</li>
	<li>Click the Go live button, select Spilt horizontally and choose the graph to check the Trajectory count. 
	NOTE: Ensure that all the markers are visible in the 3D Perspective view. This indicates that all markers can be captured for analysis.</li>
	<li>Prepare to capture the static model. On the Capture Tools pane, click the Start button in the Subject Capture section. 
	NOTE: During the whole data collection process, the subjects should remain stationary in the capture area to collect 140-200 frames of images. Then click the Stop button.</li>
	<li>In the perspective pane, view the capture marks. Click the Pipeline button in the Tools pane, select Running The Reconstruct Pipeline to create a 3D image of the captured markers. Then, manually label the static model. When the identification is completed, save and press ESC to exit.</li>
	<li>In the toolbar, choose the subject preparation and subject calibration. Select the Static plug-in gait option from the drop-down list. In the Static Settings pane, choose the left foot and right foot, click the start button and save the static model.</li>
</ol>
4. Dynamic trials
<ol>
	<li>When finished collecting the static data, select Capture in the right toolbar. Choose Trial Type and Session from top to bottom, and fill in the trial description.</li>
	<li>Ask participants to run on the treadmill in the following manner.
	<ol>
		<li>Warm up by walking at 8 km/h for 1 min.</li>
		<li>Ask the participant to run on the treadmill at speed of 10 km/h. After an adaption period of 4 min at this velocity, record the running data for 40 s. Collect the kinematic data at a distance of 0.5 km and 5 km, respectively.</li>
		<li>Ask the subjects to wear a heart rate monitor to record the heart rate and monitor the subjects&#8217; fatigue status while running.</li>
	</ol>
	</li>
	<li>In the Tool Capture pane, click the Start button. After collecting the dynamic trials, click Stop to end the collection.</li>
</ol>
5. Post-processing
<ol>
	<li>Open the Data Management window, double-click the trial name. Click the run Reconstruct Pipeline and Labels button in the toolbar to reconstruct the mark point position.</li>
	<li>In the Perspective window, move the blue triangles on the time bar to set the required range of time.</li>
	<li>Shift the view of the timeline so that it shows only the selected range, click on the time bar, and click Zoom to Region-of-Interest.</li>
	<li>At this point, select the Label button to identify and check the label points, with the same steps as the static identification process. If necessary, supplement some incomplete identification points. Delete the unlabeled marks.</li>
	<li>In the Subject Calibration pane, select the Dynamic Plug-in Gait. Click the Start button to run the data. Export motorial trials in c3d format for post-processing.</li>
</ol>
6. Data analysis
<ol>
	<li>Process the kinematics data. Apply a fourth-order low pass Butterworth filter with a cut off frequency of 10 Hz (kinematic) before exporting the joint angle data. Export the data of the joint angle.</li>
	<li>Calculate the range of motion (ROM), peak angle and peak angular velocity of the lower limb joints (hip, knee, and ankle) in three planes (sagittal, frontal, and transverse) during one stance phase.</li>
</ol>
7. Statistical analysis
<ol>
	<li>Use paired-sample T-test to compare lower limb kinematics (peak angles, ROM, peak angular velocity) between the initial (IR) and terminal phase (TR) of 5 km running.</li>
	<li>Calculate mean values and standard deviations of the five valid trials from each subject for different running distances. Set the significance level at p &#60; 0.05.</li>
</ol>

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Y., et al. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Running+from+Paris+to+Beijing:+biomechanical+and+physiological+consequences.">Running from Paris to Beijing: biomechanical and physiological consequences.</a> Eur J Appl Physiol. 107 (6), 731-738 (2009).</li><li>Mizrahi, J., Verbitsky, O., Isakov, E., Daily, D. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Effect+of+fatigue+on+leg+kinematics+and+impact+acceleration+in+long+distance+running.">Effect of fatigue on leg kinematics and impact acceleration in long distance running.</a> Human Movement Science. 19 (2), 139-151 (2000).</li><li>Bisiaux, M., Moretto, P. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=The+effects+of+fatigue+on+plantar+pressure+distribution+in+walking.">The effects of fatigue on plantar pressure distribution in walking.</a> Gait &amp; Posture. 28 (4), (2008).</li><li>Dierks, T. 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B., Sanchez, Z., Cunningham, T., Lattermann, C. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Proximal+and+distal+kinematics+in+female+runners+with+patellofemoral+pain.">Proximal and distal kinematics in female runners with patellofemoral pain.</a> Clinical Biomechanics. 27 (4), 366-371 (2012).</li><li>Souza, R. B., Powers, C. M. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/entrez/query.fcgi?db=PubMed&cmd=Search&doptcmdl=Citation&defaultField=Title+Word&term=Differences+in+hip+kinematics,+muscle+strength,+and+muscle+activation+between+subjects+with+and+without+patellofemoral+pain.">Differences in hip kinematics, muscle strength, and muscle activation between subjects with and without patellofemoral pain.</a> Journal of Orthopaedic &amp; Sports Physical Therapy. 39 (1), 12-19 (2009).</li><li>Ferber, R., Hreljac, A., Kendall, K. 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No potential conflict of interest was reported by the authors.

This study compared the effect of long distance running on the biomechanical characteristics of the lower extremity in amateur runners. It was found that the peak angle of ankle eversion and knee abduction increased after 5 km running, which is consistent with a previous study17. Studies have shown that excessive ankle eversion and eversion velocity are important factors that increase the risk of ankle injuries18,19. It is not surprising t...

Running is the most popular sport around the world. There are a large number of individuals that run and this number increases substantially every year1. It has been suggested that participation in regular exercise including running can promote health, reduce the risk of cardiovascular diseases and thus improve life expectancy2,3,4. Despite the significant health benefits of running, the incidence of running injuries has increased from 25% to 83% over the years5,6. There are some risks associated with running, especially to the lower extremities, which are mainly focused on musculoskeletal injuries7. The majority of common running-related injuries are related to patellofemoral pain, ankle sprain, tibial stress fractures, and plantar fasciitis8. Running injuries can be induced by many factors, such as incorrect foot striking patterns, incorrect shoe selection, and other individual biomechanical factors9. For instance, running with a heel-strike pattern can lead to greater pronation, and is accompanied by larger plantar pressure on the medial side of foot, which may lead a higher risk for Achilles tendinopathy and patellofemoral pain10. In addition, running with a greater knee internal rotation has been previously reported to be associated with the iliotibial band syndrome for female runners11, especially when running long distances.
Parameters of kinetics, kinematics, and time-space components can provide a precise analysis of gait biomechanics, and is currently considered to be an important parameter for clinical gait analysis12. Lower vertical ground reaction forces and larger impact accelerations are recoded after long-distance running13,14. Higher hip excursion and smaller knee flexions have also been found along with fatigued muscles15, and the increased stride frequency can result in reduced stride lengths13,16.
However, changes in biomechanical features of lower limbs at the phase of initial and terminal running have not been fully analyzed, since most studies measured biomechanical variation after running. Additionally, only a few studies use standard laboratory techniques to assess the effects of long-distance running on gait biomechanical changes in amateur runners. The main factors leading to running injuries are still unclear. Therefore, in order to reveal the underlying reasons for lower extremity injuries caused by long distance running, this study aims to compare the biomechanical changes of the lower extremity between the IR and TR phases in treadmill 5 km running in amateur runners.

<table><tbody><tr><td>14 mm Diameter Passive Retro-reflective Marker</td><td>Oxford Metrics Ltd., Oxford, UK</td><td></td><td>n=22</td></tr><tr><td>Double Adhesive Tape</td><td>Oxford Metrics Ltd., Oxford, UK</td><td></td><td>For fixing markers to skin</td></tr><tr><td>Heart Rate</td><td>Garmin, HRM3-SS, China</td><td></td><td>Detection of fatigue state</td></tr><tr><td>Motion Tracking Cameras</td><td>Oxford Metrics Ltd., Oxford, UK</td><td></td><td>n= 8</td></tr><tr><td>T-Frame</td><td>Oxford Metrics Ltd., Oxford, UK</td><td></td><td>-</td></tr><tr><td>Treadmill</td><td>Smart Run,China</td><td></td><td>Subject run on the treadmill for all the process.</td></tr><tr><td>Valid Dongle</td><td>Oxford Metrics Ltd., Oxford, UK</td><td></td><td>Vicon Nexus 1.4.116</td></tr><tr><td>Vicon Datastation ADC</td><td>Oxford Metrics Ltd., Oxford, UK</td><td></td><td>-</td></tr></tbody></table>

comparative analysis of lower limb kinematics between the initial and terminal  phase  of 5km treadmill running

Running is beneficial for physical health, but it is also accompanied by many injuries. However, the main factors leading to running injury remain unexplained. This study investigated the effects of long running distance on lower-limb kinematic variables and the lower limb kinematic difference of between the initial (IR) and terminal phase (TR) of 5 km running was compared. Ten amateur runners ran on a treadmill at the speed of 10 km/h. Dynamic kinematic data was collected at the phase of IR (0.5 km) and TR (5 km), respectively. The peak angle, peak angular velocities, and range of motion were recorded in this experiment. The main results demonstrated the following: ankle eversion and knee abduction were increased at TR; ROMs of ankle and knee were increased in the frontal plane at TR than IR; a larger peak angular velocity of ankle dorsiflexion and hip interrotation were found in TR compared to IR. These changes during the long distance running may provide some specific details for exploring potential reasons of running injuries.

The results showed that no differences in the peak angle of the ankle and hip were observed in the sagittal plane. Compared with IR, the peak angles of the ankle and the knee in the frontal plane were significantly increased at TR. A larger internal hip angle was found in TR as contrasted to IR. However, TR presented a smaller peak angle in hip abduction, ankle interrotation, and knee interrotation than IR (Figure 2).
In the sagittal plane, the ROMs of the ankle a...

Watch this Scientific Journal Video about Comparative Analysis of Lower Limb Kinematics between the Initial and Terminal  Phase  of 5km Treadmill Running at JoVE.com

Comparative Analysis of Lower Limb Kinematics between the Initial and Terminal  Phase  of 5km Treadmill Running

This study investigated the biomechanical characteristics of the lower extremity kinematic variables between the initial and terminal phase of 5 km treadmill running. The lower-limb kinematic data of 10 runners were collected using a three-dimensional motion capture system on a treadmill at the initial phase (0.5 km) and the terminal phase (5 km), respectively.

Running is beneficial for physical health, but it is also accompanied by many injuries. However, the main factors leading to running injury remain ...

comparative-analysis-lower-limb-kinematics-between-initial-terminal

Research

JoVE Journal

Behavior

6.0K Views.  Ningbo University. Deze methode kan worden gebruikt om tweede vraag over door eigenaar chemische veranderingen die zich voordoen in de natuur te onderzoeken en uit te schakelen fasen of lange afstand uit te werken in amateur-lopers. Een voordeel van deze technische is dat het specifieke details kan geven over hoe mogelijke factoren die loopschade veroorzaken te verkennen. Als u de analysesoftware wilt kalibreren, schakelt u de lichten in het lab uit en verwijdert u eventuele reflecterende objecten.Plaats...

Video: Comparative Analysis of Lower Limb Kinematics between the Initial and Terminal  Phase  of 5km Treadmill Running

Methods to Quantify Pharmacologically Induced Alterations in Motor Function in Human Incomplete SCI

Spinal cord injury (SCI) is a debilitating disorder, which produces profound deficits in volitional motor control. Following medical stabilization, recovery from SCI typically involves long term rehabilitation. While recovery of walking ability is a primary goal in many patients early after injury, those with a motor incomplete SCI, indicating partial preservation of volitional control, may have the sufficient residual descending pathways necessary to attain this goal. However, despite physical interventions, motor impairments including weakness, and the manifestation of abnormal involuntary reflex activity, called spasticity or spasms, are thought to contribute to reduced walking recovery. Doctrinaire thought suggests that remediation of this abnormal motor reflexes associated with SCI will produce functional benefits to the patient. For example, physicians and therapists will provide specific pharmacological or physical interventions directed towards reducing spasticity or spasms, although there continues to be little empirical data suggesting that these strategies improve walking ability.
In the past few decades, accumulating data has suggested that specific neuromodulatory agents, including agents which mimic or facilitate the actions of the monoamines, including serotonin (5HT) and norepinephrine (NE), can initiate or augment walking behaviors in animal models of SCI. Interestingly, many of these agents, particularly 5HTergic agonists, can markedly increase spinal excitability, which in turn also increases reflex activity in these animals. Counterintuitive to traditional theories of recovery following human SCI, the empirical evidence from basic science experiments suggest that this reflex hyper excitability and generation of locomotor behaviors are driven in parallel by neuromodulatory inputs (5HT) and may be necessary for functional recovery following SCI. 
The application of this novel concept derived from basic scientific studies to promote recovery following human SCI would appear to be seamless, although the direct translation of the findings can be extremely challenging. Specifically, in the animal models, an implanted catheter facilitates delivery of very specific 5HT agonist compounds directly onto the spinal circuitry. The translation of this technique to humans is hindered by the lack of specific surgical techniques or available pharmacological agents directed towards 5HT receptor subtypes that are safe and effective for human clinical trials. However, oral administration of commonly available 5HTergic agents, such as selective serotonin reuptake inhibitors (SSRIs), may be a viable option to increase central 5HT concentrations in order to facilitate walking recovery in humans. Systematic quantification of how these SSRIs modulate human motor behaviors following SCI, with a specific focus on strength, reflexes, and the recovery of walking ability, are missing.
This video demonstration is a progressive attempt to systematically and quantitatively assess the modulation of reflex activity, volitional strength and ambulation following the acute oral administration of an SSRI in human SCI. Agents are applied on single days to assess the immediate effects on motor function in this patient population, with long-term studies involving repeated drug administration combined with intensive physical interventions.

This video demonstrates modulation of reflex activity, volitional strength and ambulation through clinical and quantitative assessments in individuals with motor incomplete SCI as a result of acute oral administration of a serotonin reuptake inhibitor (SSRI).

Spinal cord injury (SCI) is a debilitating disorder, which produces profound deficits in volitional motor control. Following medical stabilization, ...

Medicine

Using a Split-belt Treadmill to Evaluate Generalization of Human Locomotor Adaptation

Understanding the mechanisms underlying locomotor learning helps researchers and clinicians optimize gait retraining as part of motor rehabilitation. However, studying human locomotor learning can be challenging. During infancy and childhood, the neuromuscular system is quite immature, and it is unlikely that locomotor learning during early stages of development is governed by the same mechanisms as in adulthood. By the time humans reach maturity, they are so proficient at walking that it is difficult to come up with a sufficiently novel task to study de novo locomotor learning. The split-belt treadmill, which has two belts that can drive each leg at a different speed, enables the study of both short- (i.e., immediate) and long-term (i.e., over minutes-days; a form of motor learning) gait modifications in response to a novel change in the walking environment. Individuals can easily be screened for previous exposure to the split-belt treadmill, thus ensuring that all experimental participants have no (or equivalent) prior experience. This paper describes a typical split-belt treadmill adaptation protocol that incorporates testing methods to quantify locomotor learning and generalization of this learning to other walking contexts. A discussion of important considerations for designing split-belt treadmill experiments follows, including factors like treadmill belt speeds, rest breaks, and distractors. Additionally, potential but understudied confounding variables (e.g., arm movements, prior experience) are considered in the discussion.

We describe a protocol for investigating human locomotor adaptation using the split-belt treadmill, which has two belts that can drive each leg at a different speed. We specifically focus on a paradigm designed to test the generalization of adapted locomotor patterns to different walking contexts (e.g., gait speeds, walking environments).

Understanding the mechanisms underlying locomotor learning helps researchers and clinicians optimize gait retraining as part of motor rehabilitation. ...

Using Gold-standard Gait Analysis Methods to Assess Experience Effects on Lower-limb Mechanics During Moderate High-heeled Jogging and Running

A limited number of studies have explored lower-limb biomechanics during high-heeled jogging and running, and most studies have failed to clarify the wearing experience of subjects. This protocol describes the differences in lower-limb kinematics and ground reaction force (GRF) between experienced wearers (EW) and inexperienced wearers (IEW) during moderate high-heeled jogging and running. A three-dimensional (3D) motion analysis system with a configured force platform was used to synchronously capture lower-limb joint movements and GRF. 36 young females volunteered to participate in this study and were asked about high-heeled shoe-wearing experience, including frequency, duration, heel types, and heel heights. Eleven who had the experience of 3 to 6 cm heels for a minimum of three days per week (6 h per day) for at least two years and eleven who wore high heels less than twice per month participated. Subjects performed jogging and running at comfortable low and high speeds, respectively, with the right foot completely stepping onto a force platform when passing by along a 10 m walkway. EW and IEW adopted different biomechanical adaptations while jogging and running. IEW exhibited a generally larger range of joint movement, while EW showed a dramatically larger loading rate of GRF during running. Hence, further studies on the lower-limb biomechanics of high-heeled gait should strictly control the wearing experience of the subjects.

This study investigated lower-limb kinematics and ground reaction force (GRF) during moderate high-heeled jogging and running. Subjects were divided into groups of experienced wearers and inexperienced wearers. A three-dimensional motion analysis system with a configured force platform captured lower-limb joint movements and GRF.

A limited number of studies have explored lower-limb biomechanics during high-heeled jogging and running, and most studies have failed to clarify the ...

Clinical-oriented Three-dimensional Gait Analysis Method for Evaluating Gait Disorder

Three-dimensional gait analysis (3DGA) is shown to be a useful clinical tool for the evaluation of gait abnormality due to movement disorders. However, the use of 3DGA in actual clinics remains uncommon. Possible reasons could include the time-consuming measurement process and difficulties in understanding measurement results, which are often presented using a large number of graphs. Here we present a clinician-friendly 3DGA method developed to facilitate the clinical use of 3DGA. This method consists of simplified preparation and measurement processes that can be performed in a short time period in clinical settings and intuitive results presentation to facilitate clinicians&#39; understanding of results. The quick, simplified measurement procedure is achieved by the use of minimum markers and measurement of patients on a treadmill. To facilitate clinician understanding, results are presented in figures based on the clinicians&#39; perspective. A Lissajous overview picture (LOP), which shows the trajectories of all markers from a holistic viewpoint, is used to facilitate intuitive understanding of gait patterns. Abnormal gait pattern indices, which are based on clinicians&#39; perspectives in gait evaluation and standardized using the data of healthy subjects, are used to evaluate the extent of typical abnormal gait patterns in stroke patients. A graph depicting the analysis of the toe clearance strategy, which depicts how patients rely on normal and compensatory strategies to achieve toe clearance, is also presented. These methods could facilitate implementation of 3DGA in clinical settings and further encourage development of measurement strategies from the clinician&#39;s point of view.

In this study, a clinician-friendly three-dimensional gait analysis method, which was designed to be performed in the rehabilitation clinic, is presented. The method consists of a simplified measurement method and intuitive figures to facilitate clinicians&#39; understanding of the results.

Three-dimensional gait analysis (3DGA) is shown to be a useful clinical tool for the evaluation of gait abnormality due to movement disorders. However, ...

3D Kinematic Gait Analysis for Preclinical Studies in Rodents

The utility of three-dimensional (3D) kinematic motion analysis systems is limited in rodents. Part of the reason for this inadequacy is the use of complex algorithms and mathematical modeling that accompany 3D data collection and analysis procedures. This work provides a simple, user-friendly, step-by-step detailed methodology for 3D kinematic gait analysis during treadmill locomotion in healthy and neurotraumatic rats using a six-camera motion capture system. Also provided are details on 1) calibration of the system in an experimental set-up customized for quadrupedal locomotion, 2) data collection for treadmill locomotion in adult rats using markers positioned on all four limbs, 3) options available for video tracking and processing, and 4) basic 3D kinematic data generation and visualization and quantification of data using the built-in data collection software. Finally, it is suggested that the utility of this motion capture system be expanded to studying a variety of motor behaviors before and after neurotrauma.

Presented here is a protocol to collect and analyze three-dimensional kinematics of quadrupedal locomotion in rodents for preclinical studies.

The utility of three-dimensional (3D) kinematic motion analysis systems is limited in rodents. Part of the reason for this inadequacy is the use of ...

An Inertial Measurement Unit Based Method to Estimate Hip and Knee Joint Kinematics in Team Sport Athletes on the Field

Current athlete monitoring practice in team sports is mainly based on positional data measured by global positioning or local positioning systems. The disadvantage of these measurement systems is that they do not register lower extremity kinematics, which could be a useful measure for identifying injury-risk factors. Rapid development in sensor technology may overcome the limitations of the current measurement systems. With inertial measurement units (IMUs) securely fixed to body segments, sensor fusion algorithms and a biomechanical model, joint kinematics could be estimated. The main purpose of this article is to demonstrate a sensor setup for estimating hip and knee joint kinematics of team sport athletes in the field. Five male subjects (age 22.5 &#177; 2.1 years; body mass 77.0 &#177; 3.8 kg; height 184.3 &#177; 5.2 cm; training experience 15.3 &#177; 4.8 years) performed a maximal 30-meter linear sprint. Hip and knee joint angles and angular velocities were obtained by five IMUs placed on the pelvis, both thighs and both shanks. Hip angles ranged from 195&#176; (&#177; 8&#176;) extension to 100.5&#176; (&#177; 8&#176;) flexion and knee angles ranged from 168.6&#176; (&#177; 12&#176;) minimal flexion and 62.8&#176; (&#177; 12&#176;) maximal flexion. Furthermore, hip angular velocity ranged between 802.6 &#176;&#183;s-1 (&#177; 192 &#176;&#183;s-1) and -674.9 &#176;&#183;s-1 (&#177; 130 &#176;&#183;s-1). Knee angular velocity ranged between 1155.9 &#176;&#183;s-1 (&#177; 200 &#176;&#183;s-1) and -1208.2 &#176;&#183;s-1 (&#177; 264 &#176;&#183;s-1). The sensor setup has been validated and could provide additional information with regard to athlete monitoring in the field.&#160;This may help professionals in a daily sports setting to evaluate their training programs, aiming to reduce injury and optimize performance.

Monitoring athletes is essential for improving performance and reducing injury risk in team sports. Current methods to monitor athletes do not include the lower extremities. Attaching multiple inertial measurement units to the lower extremities could improve monitoring athletes in the field.

Current athlete monitoring practice in team sports is mainly based on positional data measured by global positioning or local positioning systems. The ...

Lower-Limb Biomechanical Characteristics Associated with Unplanned Gait Termination Under Different Walking Speeds

Gait termination caused by unexpected stimulus is a common occurrence in everyday life. This study presents a protocol to investigate the lower-limb biomechanical changes that occur during unplanned gait termination (UGT) under different walking speeds. Fifteen male participants were asked to perform UGT on a walkway at normal walking speed (NWS) and fast walking speed (FWS), respectively. A motion analysis system and plantar pressure platform were applied to collect lower-limb kinematic and plantar pressure data. Paired-sampled T-test was used to examine the differences in lower-limb kinematics and plantar pressure data between two walking speeds. The results showed larger range of motion in the hip, knee, and ankle joints in the sagittal plane as well as plantar pressure in forefoot and heel regions during UGT at FWS when compared with NWS. With the increase in walking speed, subjects exhibited different lower-limb biomechanical characteristics that show FWS associated with greater potential injury risks.

This study compared the biomechanical characteristics of the lower extremity during unplanned gait termination under different walking speeds. The lower-limb kinematic and kinetic data from fifteen subjects with normal and fast walking speeds were collected using a motion analysis system and plantar pressure platform.

Gait termination caused by unexpected stimulus is a common occurrence in everyday life. This study presents a protocol to investigate the lower-limb ...

Home-Based Monitor for Gait and Activity Analysis

Current outcomes in neuromuscular disorder clinical trials include motor function scales, timed tests, and strength measures performed by trained clinical evaluators. These measures are slightly subjective and are performed during a visit to a clinic or hospital and constitute therefore a point assessment. Point assessments can be influenced by daily patient condition or factors such as fatigue, motivation, and intercurrent illness. To enable home-based monitoring of gait and activity, a wearable magneto-inertial sensor (WMIS) has been developed. This device is a movement monitor composed of two very light watch-like sensors and a docking station. Each sensor contains a tri-axial accelerometer, gyroscope, magnetometer, and a barometer that record linear acceleration, angular velocity, the magnetic field of the movement in all directions, and barometric altitude, respectively. The sensors can be worn on the wrist, ankle, or wheelchair to record the subject&#8217;s movements during the day. The docking station enables data uploading and recharging of sensor batteries during the night. Data are analyzed using proprietary algorithms to compute parameters representative of the type and intensity of the performed movement. This WMIS can record a set of digital biomarkers, including cumulative variables, such as total number of meters walked, and descriptive gait variables, such as the percentage of the most rapid or longest stride that represents the top performance of patient over a predefined period of time.

This innovative device uses magneto-inertial sensors to permit gait and activity analysis in uncontrolled environments. Currently in the qualification process as an outcome measure in the European Medical Agency, one of the applications will be to serve as a clinical endpoint in clinical trials in neuromuscular diseases.

Current outcomes in neuromuscular disorder clinical trials include motor function scales, timed tests, and strength measures performed by trained clinical ...

Bioengineering

Evaluation of Patients' Posture and Gait Profile After Lumbar Fusion Surgery by Video Rasterstereography and Treadmill Gait Analysis

This protocol provides guidance on how to perform high resolution video rasterstereography and treadmill gait analysis on patients after lumbar fusion surgery to obtain results about altered variables of gait and posture. These observed changes can then be correlated with the patient-reported outcome measure of pain relief. The rasterstereographic device projects lines of parallel light onto the surface of the tested subject&#39;s back. The deformation of these lines is recognized by the device. From these data, a special software then generates a 3-D profile based on the principle of triangulation. With an inaccuracy of only 0.2 mm it can measure changes in posture at very high precision. Gait and stance parameters are recorded using a treadmill equipped with an electric sensor mat that contains 10,200 miniature force sensors in the registering zone under the belt. Initial walking speed on the treadmill is 0.5 km/h. Speed is then gradually increased by increments of 0.1 km/h until each subject reaches his or her individual maximum well tolerable walking speed. At this speed, parameters are recorded during a 20 s measurement interval. Subjects are tested barefoot and without holding a handrail. Among various other parameters, stride width, step length, stance phase and foot rotation are measured. Both methods used reportedly have a high intra- and inter-observer reliability. The advantage of these highly accurate techniques is that they offer an objective and very detailed perspective on changes in the patient&#39;s posture and gait. Due to the amount of data generated, these techniques are, however, not so much suitable for everyday routine use, but rather interesting to scientifically evaluate long term alterations in posture and gait in patients like for example after lumbar fusion surgery.

Here, we present a protocol to analyze the posture and the gait of patients after lumbar fusion surgery by means of high-resolution video rasterstereography and a treadmill equipped with an integrated sensor mat. Allowing critical functional postoperative evaluation on a less subjective level may enhance accuracy and reliability of indication for surgery.

This protocol provides guidance on how to perform high resolution video rasterstereography and treadmill gait analysis on patients after lumbar fusion ...

The Lower Body Positive Pressure Treadmill for Knee Osteoarthritis Rehabilitation

Here, based on a clinician&rsquo;s point-of-view, we propose a two-model lower body positive pressure (LBPP) protocol (walking and squatting models) in addition to a clinical, functional assessment methodology, including details for further encouragement of the development of non-drug surgical intervention strategies in knee osteoarthritis patients. However, we only present the effect of LBPP training in improvement of pain and knee function in one patient through three-dimensional gait analysis. The exact, long-term effects of this approach should be explored in future studies.

Here, based on a clinician&#8217;s point-of-view, we propose a two-model lower body positive pressure (LBPP) protocol (walking and squatting models) in addition to a clinical, functional assessment methodology, including details for further encouragement of the development of non-drug surgical intervention strategies in knee osteoarthritis patients. However, we only present the effect of LBPP training in improvement of pain and knee function in one patient through three-dimensional gait analysis. The exact, long-term effects of this approach should be explored in future studies.

Here, based on a clinician&rsquo;s point-of-view, we propose a two-model lower body positive pressure (LBPP) protocol (walking and squatting models) in ...

Comparative Analysis of Lower Limb Kinematics between the Initial and Terminal Phase of 5km Treadmill Running

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