[ieee 2014 international conference on electronic systems, signal processing and computing...
TRANSCRIPT
Implementation of Real Time Control Algorithm for Gait Assistive Exoskeleton
Devices for Stroke Survivors
Jhulan Kumar, Neelesh Kumar, Dinesh Pankaj, Amod Kumar Biomedical Instrumentation Unit,
Central Scientific Instruments Organisation, (CSIR-CSIO), Chandigarh 160030 India
*Email: [email protected]
Abstract- Controlling human gait by wearable assistive
devices is a dynamic and time critical activity and thus
requires a dedicated real time control environment. The
paper discusses an implementation strategy for real time
control algorithm for GaExoD prototype. Control approach
follows gait trajectory using feedback sensors and actuators
for movement control. NI Lab VIEW, Robotics, FPGA and
RT module were used and prove beneficial in shorter
development time. Position control errors were estimated
for standing and sitting functions provided which is
significantly lower for sitting function.
Keywords-Exoskeleton device, Real time control, Gait
phases, LabVIEW
I. INTRODUCTION Exoskeleton Devices (ExoD) are wearable robotic
mechanism used to support and augment the physical
action performed by human body. Earlier
development of these ExoD was envisaged as
mechatronics devices to support lifting & carrying
more weight by soldiers. In the last decade, there are
research evidences which support the effectiveness of
robot assisted rehabilitation. [1, 2] According to an
estimate in USA there are about 700000 people suffer
stroke every year. About 50% of the stroke survivors
required assistance in performing daily activities. [3]
Mobility disorders after stroke is the most common
among stroke survivors. Research activities are going
on for developing external wearable mechanics to
support walking of stroke patients. Literatures
confirm that these robotic devices are able to perform
the gait rehabilitation of stroke patient in much
improved and efficient manner. [4] These devices help
to achieve variable gait patterns and extended range
of activities on Assistive Daily Living (ADL) scale.
Authors at CSIR-CSIO are involved in development
of Gait Assistive Exoskeleton Device (GaExoD). [5]
Human gait is rhythmic activity involving multiple
joint having multiple degrees of freedom and
kinematics. For accurate control it is important to
measure range of motion is important while the
kinetics and physiological activity parameters are
need to be monitored in real time [6]. Realizing a
natural gait with an externally worn mechanism
2014 International Conference on Electronic Systems, Signal Processing and Computing Technologies
978-1-4799-2102-7/14 $31.00 © 2014 IEEE
DOI 10.1109/ICESC.2014.99
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with limited degree of freedom is a challenging task.
For implementing the real time gait control the
controller demands higher processing capabilities.
The sequential controllers like PLC, microcontrollers
etc. will limit the performance and thus there is a
need of a controller and control algorithm which
executes the process in real time. The paper discusses
the algorithm developed for controlling developed
prototype of GaExoD using parallel processing of
input data and implementing it on a FPGA hardware.
II. METHODS AND MATERIALS
A. GaExoD Prototype Development:
Authors developed a prototype of wearable
exoskeleton mechanism which supports the walking
of person recovering from stroke. It has three joint
segments, hip, knee and ankle with 1 degree of
freedom at each respective joint. The gait cycle
movement was achieved by synchronizing all three
joints. The range of joint angle motion was recorded
with 3 axis accelerometers and in-house developed
electrogoniometers. The high torque of selected
actuators can support the walking of subject’s
weighing up-to 100 kg. A body unweighing system
can also be used in conjunction to reduce the torque
requirement.
B. Controller Design:
Gait cycle for a healthy human typically completes in
0.9 second. The gait cycle is divided into swing phase
and stance phase which is further subdivided into
seven gait phases. The smallest gait phase duration is
10% of gait cycle. To control the gait in real time the
controller should respond a programmable control
action in 90ms. The input processing time is critical
and dependent of the type of input signal used. When
the controller has to process the bio-physical signal
like EMG then the design architecture of controller
becomes important. The figure 1 shows the controller
design; the Real time processor handles the logic
element and communicates information with other
devices. The main task of a reconfigurable FPGA is
to process the input information and update the
actuators position. The process control algorithm is
executed by real time processor of 1.33 GHz. It can
be used in network mode with high speed gigabit
communication protocol.
Figure 1: architecture of RT Controller
C. Control Algorithm
The closed loop control algorithm uses feedback
input from sensors mounted on the GaEx GaExoD
prototype. Figure 2 shows the block diagram of the
control.
Figure 2: Block diagram of control
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The gait is rhythmic activity with seven distinguish
phases. These phases have different range of joint
angles for different human joint during a dynamic
gait. Table 1 informs about the various joint angle
ranges computed from OpensimTM Simulation
software. These ranges are also validated by
performing gait experiments in lab on normal healthy
individuals he generated gait range database also acts
as a reference data base to compute the algorithm
error and achieve near normal gait. The control is
generating the gait trajectory with normal walking
speed. It scans the sensor information to know the
dynamic position of each joint and generates a
command to achieve next gait phase position. The
controller generated commands to all six actuators in
real time. The control for sitting and standing
function of GaExoD was also developed. The control
algorithm was developed using NI LabVIEW 2012,
Robotics, FPGA and RT modules.
Gait phaseposition
Hipmovement
(deg.)
Kneemovement
(deg.)
Ankle movement
Initial contact 30 0 Neutral (0)
Loading response 30-35 0 to -15 0 to 15PF
Mid stance 35-0 -15 to 0 15PF to 10DF
Terminal stance 0 to 0 0 to 0 10DF to 0
Pre swing -10 to 0 0 to -35 0to 10PF
Initial swing 0to20 -35 to -60 20PF to 10PF
Mid swing 20 to 30 -60 to -30 10PF - Neutral
Terminal swing no change -30 to 0 Neutral
Table 1: Joint range angles for Hip, Knee & Ankle
Joints during walking over level ground
III. RESULTS
For testing the developed control algorithm is
deployed on the selected RT controller. The GaExoD
prototype has operated for several gait cycles. The
trajectory of knee hip and ankle joint were recorded
and analysed for error estimation. Algorithm was
tested for fault tolerance by creating several possible
events where it can lose its dynamic position and
results in abnormal gait cycle. The role of the
exoskeleton control algorithm is to follow the
trajectory of normal gait cycle. The gait activity to
sub phasic gait level is also recorded to compute
control error. The error was estimated for stand
position and sit position in Fig. 3 & 4 respectively.
The calculated error during stand position was higher
at knee joint and lower at ankle joint. This range of
motion and higher dynamism at stand position were
the contributing factors to these errors. The error
estimation for sit position was significantly lower for
all joints as sit position being the terminal position.
IV. CONCLUSIONS
The real time control algorithm for gait cycle was
successfully implemented using RT controller.
Developed algorithm uses trajectory estimation
approach for control. Algorithms was deployed and
tested on a RT controller for gait cycle, sitting and
standing phase. The NI LabVIEW development
platform and associated modules were used for faster
and efficient algorithm development. The trajectories
for hip, knee and ankle joints of prototype were
recorded for estimating error. The error at standing
position which is also the reference position is higher
than the sitting position which was a terminal
position. The error can be reduced by using adaptive
control approaches in future.
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Figure 3: Estimated error during stand position
Figure 4: Estimated error during sit position
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ACKNOWLEDGEMENTS
The authors gratefully acknowledge the support of
Director, CSIR-CSIO, Chandigarh through BSH PSC
0103-05. The authors acknowledge the support of
Arpan Nath & Ratan Das for help in integration &
trial activities.
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