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Muscle fatigue is a common experience in daily life. Many authors have defined it as the incapacity to maintain the required or expected force, and therefore, force, power and torque recordings have been used as direct measurements of muscle fatigue. In addition, the measurement of these variables combined with the measurement of surface electromyography sEMG recordings which can be measured during all types of movements during exercise may be useful to assess and understand muscle fatigue. EMG signal can be easily analyzed in time domain, frequency domain and time frequency domain. The time domain features are the most popular in EMG pattern recognition because they are easy and quick to calculate and they do not require a transformation. The purpose of this study was to analyze the fatigue and to study the endurance occurrence in the Gastrocnemius muscle with a pre defined exercise protocol for the targeted muscle. For this purpose, sEMG Amplitude parameters were characterized. Relation between EMG features like mean, force, standard deviation, etc. is verified for fatigue detection as well as to identify the Endurance developed in the Gastrocnemius muscle. Gaurav Patti | Poonam Kumari "Effect of Endurance on Gastrocnemius Muscle with Exercise by Employing EMG Amplitude Parameters" Published in International Journal of Trend in Scientific Research and Development (ijtsrd), ISSN: 2456-6470, Volume-4 | Issue-5 , August 2020, URL: https://www.ijtsrd.com/papers/ijtsrd33222.pdf Paper Url :https://www.ijtsrd.com/engineering/other/33222/effect-of-endurance-on-gastrocnemius-muscle-with-exercise-by-employing-emg-amplitude-parameters/gaurav-patti
The human foot are adaptable structures of bones, joints, muscles and soft tissue that let us stand upright and perform exercises like walking, running and jumping. To perform a direct investigation or experiment on human foot, it seems very difficult since the structures are very complex compared to other human part body. The study of human foot behaviour is significant to identify the location of injury occurrence and the cause in order to increase the knowledge in the improvement the way to prevent an injury and very useful to improve footwear design as well as enhance its development. The purposes of this study are to develop a finite element model of the human foot and investigate the effect of various loadings produce on various surfaces such as artificial grass, concrete and rubber toward the biomechanical response of the human foot. The foot model reconstruct in CATIA software while finite element model as well as the analysis has done in ANSYS 14.5 software. The rubber surfaces produce the higher peak load when the experimental while concrete surface is the lowest. The peak of stress and strain distribution were occur on the below of human foot location. Strain and stress effect were decreasing when Young’s Modulus value increase with the same amount of loading.
Effect of Endurance on Gastrocnemius Muscle with Exercise by Employing EMG Am...ijtsrd
Muscle fatigue is a common experience in daily life. Many authors have defined it as the incapacity to maintain the required or expected force, and therefore, force, power and torque recordings have been used as direct measurements of muscle fatigue. In addition, the measurement of these variables combined with the measurement of surface electromyography sEMG recordings which can be measured during all types of movements during exercise may be useful to assess and understand muscle fatigue. EMG signal can be easily analyzed in time domain, frequency domain and time frequency domain. The time domain features are the most popular in EMG pattern recognition because they are easy and quick to calculate and they do not require a transformation. The purpose of this study was to analyze the fatigue and to study the endurance occurrence in the Gastrocnemius muscle with a pre defined exercise protocol for the targeted muscle. For this purpose, sEMG Amplitude parameters were characterized. Relation between EMG features like mean, force, standard deviation, etc. is verified for fatigue detection as well as to identify the Endurance developed in the Gastrocnemius muscle. Gaurav Patti | Poonam Kumari "Effect of Endurance on Gastrocnemius Muscle with Exercise by Employing EMG Amplitude Parameters" Published in International Journal of Trend in Scientific Research and Development (ijtsrd), ISSN: 2456-6470, Volume-4 | Issue-5 , August 2020, URL: https://www.ijtsrd.com/papers/ijtsrd33222.pdf Paper Url :https://www.ijtsrd.com/engineering/other/33222/effect-of-endurance-on-gastrocnemius-muscle-with-exercise-by-employing-emg-amplitude-parameters/gaurav-patti
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IJRET : International Journal of Research in Engineering and Technology is an international peer reviewed, online journal published by eSAT Publishing House for the enhancement of research in various disciplines of Engineering and Technology. The aim and scope of the journal is to provide an academic medium and an important reference for the advancement and dissemination of research results that support high-level learning, teaching and research in the fields of Engineering and Technology. We bring together Scientists, Academician, Field Engineers, Scholars and Students of related fields of Engineering and Technology.
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UPPER EXTREMITY ROBOTICS EXOSKELETON: APPLICATION, STRUCTURE AND ACTUATIONijbesjournal
Robotic exoskeleton is getting important to human in many aspects such as power assist, muscle training, regain motor function and rehabilitation. The research and development towards these functions are expected to be combined and integrated with the human intelligent and machine power, eventually becoming another generation of robot which will enhance the machine intelligent and human power. This paper reviews the upper extremity exoskeleton with different functions, actuators and degree of freedom (DOF). Among the functions, rehabilitation and power assist have been highlighted while pneumatic actuator, pneumatic muscle, motor and hydraulic actuator are presented under the categories of actuator. In addition, the structure of exoskeleton is separated by its DOF in terms of shoulder, elbow, wrist and hand.
Crimson Publishers- The Effect of Medial Hamstring Weakness on Soft Tissue Lo...CrimsonPublishers-SBB
Anterior cruciate ligament (ACL) reconstructions are frequently performed in the United States of America. The medial hamstrings graft has been shown to produce lower rates of osteoarthritis (OA) than the patellar tendon graft. The goal of this study was to determine how altering medial hamstring strength during surgery affects soft tissue loading, and hence the joint’s proclivity towards OA. Muscle-actuated forward dynamic simulations of running were performed for normal muscle strength and decreased medial hamstring strength. The results show weakening the medial hamstrings caused an overall decrease in total hamstrings force by 7%, in total quadriceps force by 35%, and in cartilage contact force by 6%. This decreased force may be protective against long-term OA.
MINIMIZATION OF METABOLIC COST OF MUSCLES BASED ON HUMAN EXOSKELETON MODELING...ijbesjournal
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devices using OpenSim platform has been attempted. Two musculoskeletal models, one with torsional ankle
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changes in the metabolic rate of the lower extremity muscles before and after the addition of the assistive
devices were tested. The results about the effect of these external devices on individual muscles of the lower
muscle group were analysed which provided effective results.
IJRET : International Journal of Research in Engineering and Technology is an international peer reviewed, online journal published by eSAT Publishing House for the enhancement of research in various disciplines of Engineering and Technology. The aim and scope of the journal is to provide an academic medium and an important reference for the advancement and dissemination of research results that support high-level learning, teaching and research in the fields of Engineering and Technology. We bring together Scientists, Academician, Field Engineers, Scholars and Students of related fields of Engineering and Technology.
Design Requirements For a Tendon Rehabilitation Robot: Results From a Survey ...ertekg
Download Link > https://ertekprojects.com/gurdal-ertek-publications/blog/design-requirements-for-a-tendon-rehabilitation-robot-results-from-a-survey-of-engineers-and-health-professionals/
Exoskeleton type finger rehabilitation robots are helpful in assisting the treatment of tendon injuries. A survey has been carried out with engineers and health professionals to further develop an existing finger exoskeleton prototype. The goal of the study is to better understand the relative importance of several design criteria through the analysis of survey results and to improve the finger exoskeleton accordingly. The survey questions with strong correlations are identified and the preferences of the two respondent groups are statistically compared. The results of the statistical analysis are interpreted and insights obtained are used to guide the design process. The answers to the qualitative questions are also discussed together with their design implications. Finally, Quality Function Deployment (QFD) has been employed for visualizing these functional requirements in relation to the customer requirements.
The effects of self-myofascial release using a foam roll or roller massager on joint range of motion, muscle recovery, and performance: a systematic review
Walker E, Sandercock T, Perreault E. Influence of scaling assumptions on tendon stiffness estimation. American Society of Biomechanics 2012, Gainesville FL, August 16 2012. (podium)
UPPER EXTREMITY ROBOTICS EXOSKELETON: APPLICATION, STRUCTURE AND ACTUATIONijbesjournal
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UPPER EXTREMITY ROBOTICS EXOSKELETON: APPLICATION, STRUCTURE AND ACTUATIONijbesjournal
Robotic exoskeleton is getting important to human in many aspects such as power assist, muscle training, regain motor function and rehabilitation. The research and development towards these functions are expected to be combined and integrated with the human intelligent and machine power, eventually becoming another generation of robot which will enhance the machine intelligent and human power. This paper reviews the upper extremity exoskeleton with different functions, actuators and degree of freedom (DOF). Among the functions, rehabilitation and power assist have been highlighted while pneumatic actuator, pneumatic muscle, motor and hydraulic actuator are presented under the categories of actuator. In addition, the structure of exoskeleton is separated by its DOF in terms of shoulder, elbow, wrist and hand.
Design requirements for a tendon rehabilitation robot: results from a survey ...Gurdal Ertek
Exoskeleton type nger rehabilitation robots are helpful in assisting the treatment of tendon injuries. A survey has been carried out with engineers and health professionals to further develop an existing nger exoskeleton prototype. The goal
of the study is to better understand the relative importance of several design criteria through the analysis of survey results and to improve the finger exoskeleton accordingly. The survey questions with strong correlations are identified and the
preferences of the two respondent groups are statistically compared. The results of the statistical analysis are interpreted and insights obtained are used to guide the design process. The answers to the qualitative questions are also discussed
together with their design implications. Finally, Quality Function Deployment (QFD) has been employed for visualizing these functional requirements in relation to the customer requirements.
http://research.sabanciuniv.edu.
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Massaging human feet_by_a_redundant_manipulator_eq (1)
1. See discussions, stats, and author profiles for this publication at: https://www.researchgate.net/publication/228900266
Massaging Human Feet by a Redundant Manipulator Equipped with Tactile
Sensor
Article · July 2010
DOI: 10.1109/AIM.2010.5695843
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3. and experiments are made and several subjects are discussed
in section 5. The concluding remarks and future works are
obtained in the last section.
II. THE ANALYSIS OF REFLEX PROPERTIES
As the reflexology theory indicates, practitioners believe
that the foot is divided into a number of reflex zones
corresponding to many parts of the body, and the practice
of massaging or applying pressure to parts of the feet will
produce a beneficial effect on corresponding parts of the
body, such as lung, shoulder, pancreas, kidneys and so on.
Pressure applied to the feet generates a signal through the
peripheral nervous system. From there it enters the central
nervous system where it is processed in various parts of the
brain. It is then relayed to the internal organs to allocate the
necessary adjustments in fuel and oxygen. Finally a response
is generated that is sent on to the motoric system. This
message is fed forward to adjust the body’s tone or overall
tension level[1].
The massaging gestures of practitioners always involve the
pressing, kneading, rubbing or tapping. In this paper, the
action of pressing will be performed by a robotic arm with
a series of forces exerted.
Massaging the feet reflexology by the robotic arm, will not
only save the labor to do repeated work, but also guarantee
the steady and standard practice, which will certainly be
helpful to improve the quality of massaging work.
Manipulator
foot
k
K
k
D
m
M
End-effector
Tactile Sensor
skin
m
K
m
D
m
M
Impedance Control
End-effector
PC
Fig. 2. System modeling and human skin model
III. MODELING OF THE SYSTEM AND SKIN
It is very difficult to determine skin properties and to
model its behavior, since human skin is a non-homogeneous,
anisotropic, non-linear viscoelastic material whose properties
also vary with age and individual, which is a very complex
biological structure to study. Therefore in this paper, the
variances of skin properties are not considered and we
consider only different kinds of skin surfaces and different
reflex points in the experiments.
A. System modeling
The massaging action needs both the position control and
the orientation control, therefore a lower-DOF manipulator is
not sufficient. The 7-DOF redundant manipulator is applied
to massage the human feet as the setup of system shown in
Fig. 2. The tactile sensor is installed at the tip of the end-
effector in order to get the pressure of contact points. The
tactile sensor is chosen as the module type of DSA 9210 with
the shell-like shape, having a size of 50mm×25mm, which
provides a spatial resolution of 3.4mm with 70 sensor cells.
The working principle of the tactile sensors depends on an
interface effect between metal electrodes and a conductive
polymer covering the sensing electrodes, and the resistance
between a common electrode and a sensor cell electrode
is a function of the applied load changing with time[10].
The output voltage of a resistive sensor cell in the electrical
circuit can be detected on real-time, and the pressure on it
will be obtained from the transducer characteristics. Then the
forces exerted on the sensor cell can be achieved easily by
transforming the sensor pressure.
B. Three contact types
In general, based on the shape of human feet, three types
of contact can be divided considering different surfaces as
convex, flat and concave surfaces as shown in Fig. 3(a), Fig.
3(c) and Fig. 3(e) respectively. The experiments are made
on three different parts of feet to get the performances of
tactile sensor. The corresponding pressures measured on the
contacted tactile sensor cells are shown in Fig. 3(b), Fig. 3(d)
and Fig. 3(f) respectively.
Comparing among the experiment results, it is easily found
that the reactive forces of the sensor cells are different
although the same force at the end of the end-effector
is exerted. The biggest reactive pressures of the contacted
sensor cells appear in the convex type as shown in Fig. 3(b),
but the concave type has relatively the smallest pressures of
contacted sensor cells in three contact types as shown in Fig.
3(f), since it has more contact areas than others. As expected,
the flat type arrives at a compromise.
C. Derivation of human skin elasticity
Skin can be divided into two separate layers, the epidermis
and dermis, and the studies show that the dermis is primarily
made of collagen, elastin and reticulin fibers, which all
contribute to the mechanical behavior of skin[11], though the
epidermis is stiffer than the dermis. In a soft environment,
the human feet skin is modeled as the mass-spring-damper
system in the control scheme and the contact model between
the end-effector with the tactile sensor equipped and the
human feet skin is built up as shown in Fig. 2, where Mm is
the inertia of the end-effector including the tactile sensor, Kk
and Dk are skin elasticity and damping coefficients while Km
and Dm are stiffness and dumping parameters of impedance
control.
In the simplified model, the reaction force Fe can be
expressed as
Fe = −Dkẋu −Kk(xu −xi) (1)
8
4. Tactile Sensor
Human Skin
(a) Convex Surface
0
10
20
30
−60
−40
−20
0
0
10
20
30
40
50
60
70
80
90
y
x
Pressure(kPa)
0
10
20
30
40
50
60
70
80
(b) Convex Surface Pres-
sure
Tactile Sensor
Human Skin
(c) Flat Surface
0
5
10
15
20
25
−60
−40
−20
0
0
20
40
60
80
100
y
x
Pressure(kPa)
0
10
20
30
40
50
60
70
80
(d) Flat Surface Pressure
Tactile Sensor
Human Skin
(e) Concave Surface
0
5
10
15
20
25
−60
−40
−20
0
0
10
20
30
40
50
y
x
Pressure(kPa)
0
5
10
15
20
25
30
35
40
45
(f) Concave Surface Pres-
sure
Fig. 3. Three contact models of human skin surface
where Fe is the external force in the dynamic model of
the massage motion and it can be obtained easily from the
impedance control discussed in the next section. xi is a initial
position where Fe becomes zero.
IV. IMPEDANCE CONTROL OF REDUNDANT
MANIPULATOR
Impedance control is an unified approach which can deal
with both free and contact motions without any switching
mechanism or selection of controlled subspaces[3][12] and
it is suitable for those tasks where contact forces must
be kept small while accurate regulation of forces is not
required. With generalized impedance control, the position
and force tracking accuracy of manipulator’s end-effector
can be balanced by properly adjusting impedance parame-
ters(stiffness and damping matrices) as a result of unexpected
interactions with the environment. The hybrid impedance
control, an unified approach for motion and force control,
is developed and then extended to redundant manipulator
systems, constructing the end-effector equations of motion
and describing their behavior with respect to joint forces[6].
A. Impedance control
The dynamics equation of a robot manipulator in the joint
space can be written as
M(q)q̈+C(q,q̇)q̇+G(q) = τ −JT
Fe (2)
where M(q) ∈ Rn×n is a symmetric and positive definite joint
inertia matrix, C(q,q̇)q̇ ∈ Rn is the Centripetal and Coriolis
force, G(q) ∈ Rn is the gravity force, τ is the joint torque
generated by the actuator, J is the jacobian matrix and Fe ∈
Rm is the contact force on the tip from the environment.
The desired impedance of the manipulator has the follow-
ing form:
Mdëp +Ddėp +Kdep = αFe (3)
where ep = xd − xu, Md, Dd and Kd ∈ Rm×m
are positive-
definite matrices representing inertia, damping and stiffness
respectively, and α is a force scaling matrix[14].
It can be easily known from the kinematics equation, ẍ =
Jq̈+ ˙
Jq̇, then combining it with (2) and (3) together, so the
required input joint torque can be derived with the pseudo
kinetic energy matrix Λ [JM−1JT ]−1 ∈ Rm×m as follows:
τ = JT
Λ[(ẍd − ˙
Jq̇)+M−1
d (Ddėp +Kdep −αFe)]
+C(q,q̇)q̇ +G(q)+JT
Fe (4)
Here M−1
d = JM−1JT will have some advantages[12], and
the generalized impedance control law can be rewritten as
τ = JT
[Λ(ẍd − ˙
Jq̇)+(Ddėp +Kdep +(In −α)Fe)]
+C(q,q̇)q̇+G(q) (5)
B. Impedance control for massaging manipulator
For a kinematically redundant robot manipulator, if ignor-
ing the null space, many of the redundancy advantages will
be lost. Therefore the null space joint torque will be added to
the impedance control law to control the null space motion.
1) Redundancy Resolution: Considering a n-DOF serial
manipulator operating in a m-dimensional task space (m
n), a nonempty null space N(J) exists and the number
of redundant DOFs is r = n − m. Let N1(q), N2(q), ···,
Nr(q) be a set of smooth and linearly dependant vectors in
the null space of N(J) making up of the matrix N(q) =
N1(q) ··· Nr(q)
, and there will always be the rela-
tionship,
J(q)N(q) = 0 (6)
The general inverse solution can be written as
q̇ = q̇p +q̇h = J†
(q)ẋ+(I −J†
(q)J(q))q̇0 (7)
where J† is the inertia-weighted pseudoinverse, q̇p is the
particular solution and q̇h is the homogeneous solution to
the problem (Jq̇ = 0) in the null space with another form of
q̇h = N(q)ẋN.
Corresponding with two kinds of kinematic solutions, the
kinematics of extended task space can be formulated by the
primary task and secondary task as ẋE =
ẋT ẋT
N
. Since
the vector space xN is not available, the velocity control
of null space motion[16] is the substitute and it has the
following form as: ẋN = (NT MN)−1NT Mq̇ JN(q)q̇.
Then the extended task space kinematics can be expressed
as ẋE =
ẋ
0
= JE(q)q̇, JE =
J
JN
is the extended
Jacobian by augmenting the null space into the bottom of
the Jacobian J. JN stands for the portion of the Jacobian
subjected to the n−m constraint equations f(q) = 0 and the
detailed derivation of JN can be found in [13].
9
5. 2) Extended Impedance Control: As the extended kine-
matics is discussed above in terms of the task space and null
space, the extended impedance control law has the form
τE = τP +τN +C(q,q̇)q̇+G(q) (8)
whereτP and τN are the vectors of task space and null
space joint torques respectively, C represents the coriolis and
centripetal matrix and G denotes the gravity force vector.
The extended impedance control law has the similar form
as the generalized impedance control law (5), and it can be
decomposed into the task space joint torque τP and the null
space torque τN,
τp = JT
[Λ(ẍd − ˙
Jq̇)+(Ddėp +Kdep +(In −α)Fe)] (9)
τN = JT
N {ΛN(ẍNd − ˙
JNq̇)+DNėN} (10)
where ΛN = NT
MN, ėN = ẋNd
− ẋN and DN is the damper
coefficient.
The block diagram of the extended impedance controller is
shown in Fig. 4, where the inner loop is an inverse dynamics
control and the outer loop is an additional control to achieve
the tracking goals.
C. Stability analysis of the system
The derivative of the null space velocity can be written as
VNe = ėN = ẋNd
−JN(q)q̇ (11)
where ẋNd
denotes the desired null space velocity.
Further, differentiating (11), the null space error accelera-
tion is
V̇Ne = ẍNd
−JN(q)q̈− ˙
JN(q)q̇ (12)
Combining (2), (8) and (12) together, by a simplification
of JN(q)M−1JT Λ = 0, the tracking error of null space accel-
eration can be rewritten as
V̇Ne = ẍNd
−JN(q)M−1
τN − ˙
JN(q)q̇ (13)
Substituting the null space control torque (10) into(13),
yields
V̇Ne = −DNėN = −DNVNe (14)
Here a Lyapunov function is defined as
ν =
1
2
VT
NeVNe (15)
6
6
6
6
6
6
6
d
K
)
(q
/
)
(q
J
)
(q
f
)
(q
JT
x
x
q
JN
)
(q
JN
N
D
6 6
G
C
x
q
e
F
W
d
x
x
d
x
x
x
d
x
x
Nd
x
x
x
Nd
x
x
N
x
N
W
p
W q
x
x
x
)
(q
JT
N
)
(q
N
/
x
x
q
J
ARM
D
I
Hu
ma
n
d
D
loop
Inner _
loop
Outer_
Fig. 4. Block diagram of extended impedance control
Then the derivative of the function is
ν̇ = VT
NeV̇Ne = −VT
NeDNVNe (16)
With the existence of null space N(J) and null space
Jacobian matrix J(N) and the diagonal matrix DN with
positive terms, the Lyapunov function ν is positive definite
and its derivative ν̇ is negative definite. Therefore the null
space velocity error converges to zero and the extended
impedance controller stabilizes the null space motion.
D. Optimization of null space motion
In addition to the primary task, the secondary task is
to minimize a desired cost function. Since the null space
has many forms, a proper choice of N(J) will achieve the
avoidance of rank deficient matrix.
The additional task is represented as
Z(q) = N(q)T
Φ(q) (17)
Therefore, the Jacobian matrix of null space can be written
as JN = ∂Zi(q)
∂qi
= ∂N(q)T Φ(q)
∂q . Φ(q) is a scalar objective func-
tion of the joint variables and Φ(q) is the vector function
representing the gradient of Φ. Here the kinematic constraint
function considered is the joint limit avoidance[15].
V. SIMULATIONS AND EXPERIMENTS
A. Simulations
Since reflexology involves the practice of massaging,
squeezing, or pushing on parts of the feet, we try to follow
the physician techniques in the simulations and experiments
and a desired trajectory is designed, which is to simulate
a kind of massaging trajectory on the feet, crossing several
reflex zones and points, such as lung, shoulder, solar plexus,
pancreas, adrenal, kidneys, small intestine and sigmoid colon
as shown in Fig. 5.
Fig. 5. Simulated trajectory
The experiment is set up with the Powercube modular
manipulator and the tactile sensor system(both sensor and
controller) installed on the tip of the end-effector as shown
in Fig. 1. A massaging bed is made mainly to place the feet
and the V-shape configuration will make people feel more
comfortable. The surface of tactile sensor contacts with the
10
6. 0 1 2 3 4 5 6
−100
−80
−60
−40
−20
0
20
40
60
time (s)
rotating
angles
of
seven
joints
q1
q2
q3
q4
q5
q6
q7
Fig. 6. The changes of seven joint variables in the simulation
human skin and the voltage feedbacks of sensor cells can be
monitored by the DSA-Explorer software.
The stiffness matrix is Kd = diag
500 500 500
,
the damping matrices are Dd = diag
50 50 50
and
DN = diag
40
, and the force scaling matrix is α =
diag
0.2 0.2 0.2
. The estimated parameters of human
skin are chosen with the reference of hard skin position[8],
Kk = 1327 and DK = 68. The desired pressing force on the
feet is chosen as Fe = 30N. More information can be found
in our related work[15], such as the initial parameters, the
kinematics modeling of redundant manipulator, the inertial
and Coriolis matrices, the choice of null space and so on.
The simulation results of joints variables are given out in
Fig. 6, which are listed one by one for that there are big
differences among different joints values and it is hard to
view the change if all seven joints variables are arranged in
one figure.
B. Experiments
The real experiment is made to follow the trajectory
similar as a kind of massaging work and the texel-voltages
changes of the contacted sensor cells are recorded through
the MATLAB OPC sever, which are then transformed to the
sensor pressures and contact forces. The force exerted on
each sensor cell will be added together to get the value of
the contact force between the sensor-equipped end-effector
and the human feet. A series of experimental screen shots of
massaging human foot are shown in Fig. 7.
Then the contact force between the end-effector and the
human feet can be obtained as shown in Fig. 8. It can be
easily found that the reactive force has smaller value in the
middle part mainly because of the loose contact in the central
part of human feet with complex shape, which generates
less contact than the beginning and end parts. The reactive
(a) t=0.32s (b) t=1.12s (c) t=1.36s
(d) t=2.00s (e) t=2.16s (f) t=2.36s
(g) t=2.56s (h) t=3.36s (i) t=3.56s
(j) t=4.12s (k) t=4.32s (l) t=4.48s
(m) t=5.12s (n) t=5.46s (o) t=6.00s
Fig. 7. Sequential snapshots of massaging the human foot by the
manipulator
forces obtained in the real experiment is quite different from
that of the simulation, partly because of many unknown and
unexpected factors in the experiments and partly because of
the estimated human skin parameters in the simulation.
C. Discussions
Although there are some ways to determine the human
skin properties[6], it will vary with many factors, like the
locations, the age and different peoples. The skin parameters
chosen lead to the differences between the simulation and
experimental results. So a lot of experiments should be made
on the human feet to determine the feet skin properties with
the aim of better massaging.
Besides, the unavoidable moving of human feet during the
operation will produce some influences on the measurement
of contact force. Also the skin reaction excited by the tactile
sensor will more or less generate some errors.
Another factor should not be neglected is the trajectory,
although it is designed to be close to the shape of human
feet, there’s still the difference between them because the
human feet is hard to model and it has a complex shape.
A challenge of making the sensor-tip follow the surface of
11
7. 0 1 2 3 4 5 6
−40
−35
−30
−25
−20
−15
−10
−5
0
time (s)
Pressing
force
of
feet
skin
in
the
real
experiment
Fig. 8. The reactive force of feet skin in the simulation
the feet will be beneficial to the safety and comfortability of
massaging.
Finally, the forces of all contacted sensor cells are added
together to be seen equivalent to the reaction force at
the contact region, however, since the tactile sensor has a
shell-like shape, the force components generated in other
directions will make it more or less inaccurate in the normal
direction.
VI. CONCLUSIONS AND FUTURE WORKS
A. Conclusions
Based on reflexology, the paper presents a way of mas-
saging human feet by a 7-DOF redundant manipulator with
tactile sensor installed at the end-effector. Since the hu-
man skin is very complicated and difficult to determine its
properties, it is simply modeled as the mass-spring-damper
system. Impedance control is extended to manage both the
task motion and the null space of the redundant manipulator.
Several key subjects are discussed, such as the contact
types, human skin elasticity and so on. Simulations and
real experiments are made respectively to track the desired
massaging trajectory and the results are compared while
several factors influencing the experimental performances are
considered and analyzed carefully.
B. Future Works
In the next step, the force sensor will be combined in
the system and the forces measured can be used to manage
the motion control more easily and accurately. Moreover,
hybrid sensors of tactile sensor and force senor will provide
more methods to implement complex massaging techniques
and guarantee the operating safety and comfortability. Other
control methods or mobile manipulator will also be used
and compared with current one[17][18], while parameters
identifications will be performed to identify accurate system
parameters[19].
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12
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