mihradi 2011
TRANSCRIPT
2011 International Conference on Instrumentation, Communication, Information Technology and Biomedical Engineering
8-9 November 2011, Bandung, Indonesia
3D Kinematics of Human Walking Based on
Segment Orientation
S. Mihradi, A. I. Henda, T. Dirgantara, A. I. Mahyuddin*
Faculty of Mechanical and Aerospace Engineering,
Institut Teknologi Bandung, Indonesia
*Corresponding author: [email protected]
Abstract-Human walking analysis is instrumental in medical
rehabilitation because it gives quantitative information of
human body segment during walking. The present work is a
part of research on the development of 3D gait analyzer
system. The system consists of a program to process and
display 3D kinematics parameter of human gait based on
position and displacement of markers. Observational data is in
the form of marker position as a function of time in x, y, z axis.
This data is then processed to obtain somegait parameters. To
achieve good results, the marker position data is initially
smoothed to eliminate noises before further processing. The
program developed in the present research could succesfully
calculate some parameters of human gait such as spatio
temporal parameters, linear kinematics and angular
kinematics of joints.
Keywords: 3D Kinematics, Human Body Model, Gait
Analysis
I. INTRODUCTION
Human movement analysis has long been studied and
applied in various fields. The one that specifically studied
the characteristics of human walking is called gait analysis.
Human gait analysis is instrumental in medical rehabilitation
because it gives quantative information of human body
segment during walking.
In general, human gait can be measured by direct
measurement techniques and also imaging (optical)
measurement techniques. The main problem in direct
measurement techniques is subject has to carry many cables
or other components that can affects walking motion [1].
Most of the problems encountered by direct measurement
techniques can be overcame by imaging (optical)
measurement techniques.
Recently, the authors have developed an affordable
system for 2D kinematics and dynamics analysis of human
gait [2] by using a 25 fps home video recorder. The system
is further improved to overcome the occlusion problem of
markers [3] and has been successfully used to determine 2D
gait parameters of Indonesian people as an effort to develop
the first Indonesian gait database [4-5]. However,
information obtained from 2D measurement, i.e. in sagittal
plane is not as much as information obtained from 3D
measurement. Although the sagittal plane is probably the
most important one, where much of the movement
parameters could be observed, there are certain gait
pathologies where another plane (e.g., the frontal plane)
would yield useful information [6]. Therefore, development
of 3D gait analysis system is needed to obtain gait
parameters in frontal and transverse planes.
The present work is a part of research on development of
3D gait analyzer system. Acomputer program to process and
display 3D kinematics parameter of human walking based
on position and displacement of markers attached to some
body segments is developed. Observational data in the form
of marker position as a function of time in 3D space is
obtained from the 3D optical motion-capture system.
However, for the present analysis, dummy data is used
instead, in order to check the reliability of the developed
program by comparing kinematics parameters calculated by
the program with the ones from literature.
II. KINEMATICS MODEL
To observe the kinematics of human walking, a model
of human body should be constructed first. In this research,
human body is modeled by 8 segments as shown in Fig. 1.
This model is an improvement of a model introduced by
Vaughan, where he divides the human body into 7 segments,
where pelvis and HAT (Head Arm Trunk) is in one segment
[6]. For the present model, pelvis and HAT is divided into 2
segments. Therefore, the 8 segments are right foot, right
calf, right thigh, pelvis, HAT, left thigh, left calf, and left
foot.
In analyzing the kinematics of a system, reference axes is
required. Reference axes provides the position and
orientation of each segment. Fig. 2 illustrates the local
reference system (LRS) and global reference system (GRS).
The GRS has X-Y-Zaxes, and this axes are fixed for any
given camera arrangement. The second referenceis LRS
with x-y-z axes,where each of LRS is attached to one
segment. The LRS is called anatomical axes and there are 8
anatomical axes to describe orientation of 8 segments [7].
386978-1-4577-1166-4/11/$26.00 ©2011 IEEE
2011 International Conference on Instrumentation, Communication, Information Technology and Biomedical Engineering
8-9 November 2011, Bandung, Indonesia
Fig.1. Human body model
Fig.2. Reference axes system
III. MARKER SYSTEM
The marker system described here referred to Vaughan
Kit Marker Set, developed by Vaughan [6]. The set uses 15
markers attached to lower part of human body.Thepositions
of markers are depicted in Fig 3.
To check whether or not the dummy data that represent
the markers position met the system of Vaughan Kit Marker
Set, at first, those data is visualized by the developed
program as skeleton display as depicted in Fig. 4. Red
circles describe positions of markers and the blue ones
describe approximate position of the joints.
IV. SMOOTHING PROCEDURE
To obtain good results, at first the marker position data
should be smoothed to eliminate noises. This step is
necessary since calculation of second or third order
parameters such velocity and accelaration is very sensitive
to noises. If those data are
Fig.3. Vaughan Kit Marker Set [2]
Fig.4. Skeleton display based on marker position data
used directly in the kinematics analysis, the results will be
highly inaccurate, as shown by dashed line in Fig. 5and6. In order to remove the noises, smoothing spline technique
is adopted to the raw data [8]. By using the smoothed data,
then the foot velocities and accelerations are calculated as
represented by solid lines in Fig. 5 and 6.
To obtain the most appropriate smoothing parameter
value, trial and error process is conducted until the obtained
curve is close to the one in the literature. Literature used in
the process is the velocity-accelaration curve of Vaughan
[6]. The process is illustrated in Fig. 7. Curves on the left are
calculation results obtained by varying the smoothing
parameter value.The curve on the right is from literature.
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2011 International Conference on Instrumentation, Communication, Information Technology and Biomedical Engineering
8-9 November 2011, Bandung, Indonesia
Fig.5.Right foot velocity in x-y-z direction before (dashed line) and after
(solid line) smoothing
Fig.1. Right foot acceleration in x-y-z direction before (dashed line) and
after (solid line) smoothing
V. KINEMATIC ANALYSIS PROCEDURE
The procedure for kinematics calculations is described in
the flowchart shown in Fig. 8. Based on the flowchart and
the method described in [6], a computer program is
developed by using MATLAB. The graphical user interface
(GUI) is also constructed to help user to execute the
program easily. The GUI is shown in Fig. 9.
VI. RESULTS AND DISCUSSION
The program developed in the present workis used to
calculate general gait /spatio temporal parameters (cycle
time, cadence, stride length and speed), linear kinematics
parameters and angular kinematics parameters. The obtained
parameters are presented in the subsequent sub-chapters.
Fig.2. Smoothing parameter selection process
Fig.3. Flowchart of kinematics analysis.
Fig.4. Program developed in the presentwork.
A. Spatio Temporal
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2011 International Conference on Instrumentation, Communication, Information Technology and Biomedical Engineering
8-9 November 2011, Bandung, Indonesia
Since the distance, the time and the number of steps are
all known from simulation, the kinematics gait parameters
could be easily calculated using the following formula:
1. Cycle time (s) = time (s) × 2/(steps counted)
2. Cadence (steps/min) = (steps counted)× 60/time (s)
3. Stride length (m) = distance (m) × 2/(steps counted)
4. Speed (m/s) = distance (m)/time (s)
Table 1 shows several calculated spatio temporal
parameters of the present data of human gait.
Table 1. Several kinematics parameters
Cadence
(steps/min)
Cycle
time (s)
Stride length
(m)
Speed
(m/s)
96 1.25 1.3 1.03
B. Linear Kinematics
At present, the program could calculate somelinear
kinematics parameter such as joint/segment position, its
velocity and linear acceleration. Fig. 10 shows right foot
position versus time, while velocity and linear acceleration
of the foot are depicted in Fig. 11 and 12.
Fig.5. Right foot position in x-y-z direction
Fig.6. Right foot velocities in x-y-z direction
Fig.7. Right foot accelerations in x-y-z direction
C. Angular Kinematics
Angular kinematics parameters obtained by the program
are joint angles, angular velocities and accelarations. The
results are shown in Figs. 13-17.
Fig.8. Joint angles of sagittal plane
Fig.9. Joint angles of transverse plane
Fig.10 Joint angles of frontal plane
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2011 International Conference on Instrumentation, Communication, Information Technology and Biomedical Engineering
8-9 November 2011, Bandung, Indonesia
Fig.11. Right calf angular velocities
Fig.12. Right calf angular accelarations
VII. CONCLUSIONS
In the present research, a computer program to process
and display 3D kinematics parameter of human walking
based on position and displacement of markers attached to
some body segments has been developed. The program
could successfully calculate spatio temporal, linear and
angular kinematics parameters of human walking.
To ensure the reliability of the developed program, the
results have been compared to some parameters obtained
from the literature. The comparison showed that the
developed program sufficiently accurate and feasible to use.
ACKNOWLEDGMENT
The authors gratefully acknowledge the support from
Program Riset dan Inovasi KK ITB 2011 for the present
project.
REFERENCES
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