Active Orthosis for Ankle Articulation Pathologies
|
|
- Abraham Cameron Simmons
- 5 years ago
- Views:
Transcription
1 Active Orthosis for Ankle Articulation Pathologies Carlos André Freitas Vasconcelos IST, Universidade Técnica de Lisboa Av. Rovisco Pais, Lisboa, Portugal Abstract This work addresses the analysis, simulation, and control of the ankle joint during gait, with the goal of designing an active ankle-foot orthosis (AAFO) to assist individuals without motor control at the ankle joint. An elastic foot contact model was developed in SimMechanics, allowing that with knee and leg kinematics prescribed, the correct movement of ankle joint during gait cycle could be achieved by the controller. Three control strategies were implemented: proportional-derivative (P-D) control and linear quadratic regulator (LQR) for reference following, and impedance control (IC) for mimic the human control by considering an ankle stiffness and damping during gait cycle. An AAFO was designed for assisting the ankle movement during gait with the characteristics on biomechanical requirements for an individual with a body mass of 70kg. A series elastic actuator (SEA) provides the active control of the AAFO. The SEA was designed to be lightweight, compact, and with enough power to provide the ankle movement during gait. The presented AAFO is expected to be autonomous and assist the ankle movement in all phases of the gait cycle. Keywords: Active Ankle-Foot Orthosis (AAFO), Series Elastic Actuator (SEA), Ankle-Foot Complex Simulation and Control, Impedance Control, Human Gait. 1. INTRODUCTION Standing or walking is something people take it for granted, however, every year thousands of people are prevented of doing it. Facing various gait disabilities, several approaches of active systems have been made on trying to improve the patient s life, such as assist people actively with robotic solutions. It is in this context that the concept of wearable robots has emerged, where the robotic counterparts of orthoses are robotic exoskeletons (1). The function of the exoskeleton have been widely developed, since it can be applied not only on restoring handicapped functions or rehabilitation, but also on the improvement of human body performance. As a part of the locomotor unit, the ankle and foot are the final segments that provide support to the body by distributing gravitational and inertial loads. Thus, this dissertation investigates in particular the disabilities at the ankle joint, considering the worst scenario where the individual has very low or any motor control of the ankle joint. Assist this pathology, which can occur due to weakness in dorsiflexor and plantar flexor muscles, allows the full functioning of the ankle joint and faces the challenge of interrelating biomechanical principles with engineering concepts. Several techniques on assisting ankle pathologies have been developed for the different pathologies (2), however, ankle-foot orthoses (AFOs) are the most used systems. AFO is usually an orthosis that covers the foot, spans the ankle joint and covers the lower leg. This passive lower limb orthotic device can be divided into categories of metal, plastic, and more recently carbon (3), where its recent ankle joints allow much motion as possible while blocks unwanted movement (4). With the necessity of assisting ankle pathologies more actively, the AFOs have been endowed of active systems, generally denominated of active ankle-foot orthoses (AAFOs). Several active ankle-foot orthosis have been developed in the last decade for rehabilitation and gait assist purposes. The objective of this work is to develop a lightweight and autonomous system capable of providing ankle movement during gait cycle. A passive ankle-foot orthosis will be the basis of the system, which should be endowed of sensing devices that identify the different phases of the gait, and an actuator with enough power to provide the ankle movement during the gait cycle. Several control strategies will be developed to the system in order to control the angular position of the ankle joint during the gait cycle. 1
2 2. ANKLE FOOT COMPLEX Biomechanics of the human movement can be defined as the interdiscipline which describes, analyzes and assesses human movement (5). Understanding human movement is essential when developing systems capable of assisting human body, requiring the study of anatomy and physiology of the human body. In particular for the ankle movement, two movements are possible in the sagittal plane: dorsiflexion and plantar flexion. Figure 2.1: Movements of the foot in the sagittal plane(6). The kinematic variables evaluated in gait analysis are usually linear and angular displacements, velocities, and accelerations (5). Limb angles in the spatial reference system are defined using counterclockwise from the horizontal as positive. Thus angular velocities and accelerations are also positive in a counterclockwise direction in the plane of movement, which is essential for consistent use in subsequent kinetic analyses. Kinetics in human gait represents the forces and torques that cause the motion of the body (7), where both internal and external forces are included. Internal forces come from muscle activity, ligaments or friction in the muscles and forces, while external forces come from the ground or from external loads (5 p. 10). Figure 2.2: Schematic of the lower leg during gait - free body diagram of the foot showing the ankle moment, weight of the foot ( ), and ground reaction force (2 p. 59), The moment of force acting through ankle joint,, becomes (2.1) where is the ankle rotational inertia due to the mass of the foot, the ankle angular acceleration, and the position vectors of the center of mass (COM) and center of pressure (COP) relative to ankle joint center, respectively. 3. SIMULATION AND CONTROL When a passive system is endowed of active system, it is necessary to provide some kind of control strategy to have the desired behavior. When endowing an ankle-foot orthosis (AFO) with an actuator to assist ankle pathologies, several control strategies can be implemented. Three control strategies were proposed in this work. With rehabilitation purposes, a variation of a Proportional-Integral-Derivative (PID) controller and a Linear Quadratic Regulator (LQR),where the system is controlled by reference following. With a control behavior similar to the human control, Impedance Control (IC) is the control strategy for assisting the AAFO during free walking where the controller tries to mimic the human control Control System A control system consists of subsystems and processes (or plants) assembled for the purpose of controlling the output of the processes (8). These processes are characterized by its inputs and outputs. The system input is the manipulated variable, which is the condition that is varied by the controller to affect the controlled variable. The controlled variable is the system output, which is the condition that is measured and controlled (9). Manipulated and controlled variables are the key concept for the entire designing, since a bad choice of variables can affect the possibility of controlling the system. The control scheme presented in Figure 3.1 is a closed-loop control system, where the difference in the desired and actual condition creates a correction control command to remove the error (10). The controlled variable involved in this control scheme is the ankle angle sensor output, while the manipulated variable is the ankle torque that causes the rotation of the ankle joint. In fact, the ankle torque results from the output force of a series elastic actuator (SEA), this is a linear actuator in series with a spring that causes a torque through the ankle joint due to the offset of the application point with respect to the joint center. The existence of a spring in the actuator provides some mechanical compliance, acting 2
3 also as an indirect force sensor by measuring the deflection of the spring. It also makes the system more robust to the application of sudden external forces and more close to its biological counterpart, improving the overall response of the system in the correction of pathological gait. Figure 3.2: Scheme for the multibody ankle-foot model with the representation of kinematics prescribed at the knee joint. Figure 3.1: Diagram of a simplified control scheme for controlling the ankle movement with the AAFO. The control action of the AAFO is executed by an actuator (series elastic actuator), which causes a torque about the ankle joint with the goal of assisting the ankle movement during gait Mathematical Ankle-Foot Model A basic approximation for the mathematical ankle-foot model can passes by the application of Newton s second law for rotational motion (11), where the ankle torque,, is calculated. (3.1) where is the ankle rotational inertia due to foot mass, and the ankle angular acceleration. This equation can be written as a transfer function using the Laplace variables, assuming that ankle torque is the input, and the angular displacement of the ankle is the output. (3.2) The resulting transfer function represents a second order system, unstable, characterized by the two poles at the origin Multibody Ankle-Foot Model Instead of deriving and programming equations, biomechanical models can be developed in multibody simulation tools. Multibody systems are used to model the dynamic behavior of interconnected rigid or flexible bodies that have their relative motion constrained by kinematic joints that are acted by forces. Several foot models have been widely proposed as an attempt to calculate the ground reaction forces on the foot or the torque through the ankle joint. In the modeling of the ankle-foot complex, a currently accepted approach to quantify foot and ankle kinematics during gait is to represent the entire foot as a single rigid body with a revolute ankle joint, generally for sagittal plane studies (7). Thus, a simple foot contact model was considered for the modeling, adding to the foot (rigid body) elastic contacts. The developed foot model, presented in Figure 3.3, has two elastic contact points, considering for each the vertical and horizontal components of force. The contact forces,, are defined by the Hertz contact law (11) where (3.3) represents the foot penetration on the ground, and the stiffness of the contact point. The foot penetration is the displacement of the contact point below the ground (Y=0), i.e., when contact point is at negative values for the vertical coordinate (Y) the foot is actuated by the ground reaction forces. Figure 3.3: Elastic foot contact model for the multibody ankle-foot model. The software used in the development of multibody biomechanical model was SimMechanics. SimMechanics is a module from Simulink, which is a simulation tool from MATLAB (12) software. 3
4 For the configuration of the ankle-foot model, the development of the multibody system was realized in two phases. First phase was characterized by all joints having their kinematics prescribed, where the ankle torque was obtain through inverse dynamics. In the second phase, the ankle joint ceased to have prescribed kinematics, setting the ankle joint as a forward dynamics model. Figure 3.4: Multibody biomechanical model used in the simulation (SimMechanics ). With all joints kinematics prescribed, it was necessary to set the parameters of the ankle-foot model to use. The main goal was to assign a position and stiffness to each contact point on the foot, in order to replicate the ankle torque during gait cycle on the ankle joint due to reaction forces on the contact points. In an iterative procedure, the positions of the contact points on the foot were first chosen in an attempt to match some particular events during the stance phase with the intersection of the ground with the contact points. Figure 3.5: Dynamics of gait data and model during gait cycle: (a) ankle torque, (b) horizontal shear force, (c) vertical force. Achieving an acceptable ankle-foot model for the gait cycle, the ankle joint ceased to have prescribed kinematics. In this situation, the anklefoot model relies on the functional error for which this work has considered to assist, excessive dorsiflexion and plantar flexion. Thus, this model can be connected to a controller in order to assist the movement of the ankle joint during gait cycle System States Depending on the type of controllers, it may be required the definition of the state of the system, i.e., characterize the situation in which the system is. During the gait cycle, the ankle joint is subjected to a large movement and torque, which characterizes the system as nonlinear. Therefore, it is preferable to linearize or define different states for the system, allowing the controllers to have specific parameters for the different states. The linearization of the system provides a more efficient control of the system, demanding a lower control effort. A total of four states were defined for the gait cycle: state 1 as loading response, state 2 as stance, state 3 as pre swing, and state 4 as swing. Figure 3.6: Events that cause the transition of states. Sensors enabled in red and disabled in black P-D Control and LQR control The PID controller is the most commonly used controller (13 p. 216). In the basic PID control system, when the reference input is a step function, the presence of the derivative term in the control action, the manipulated variable,, involves an impulse function known as derivative kick (9). Derivative kick is a phenomenon that generally leads to the instability of the system, as also to the damage of physical components. To avoid the derivative kick phenomenon, it is necessary to operate the derivative action only in the feedback path so that differentiation occurs only on the feedback signal and not on the reference signal. The control 4
5 Ankle Angle (degrees) scheme arranged in this way is called the P-D control and was implemented in this work. The closed-loop transfer function of P-D controller can be compared with the typical transfer function of a second-order system. Hence, if and are given as design specifications, the following relations can be found (3.4) (3.5) LQR is an optimal control strategy. Given a system, optimal control objective s consists on finding a control law by recurring to a certain optimality criterion. The linear quadratic regulator (LQR) has the advantage of providing a systematic way of computing the state feedback control gain matrix. When designing an optimal control system, it is required the definition of a control decision, subjected to certain constraints, so as to minimize some measure of the deviation from ideal behavior (14 p. 566). In the LQR problem, given the system equation it is determined the gain matrix control vector so as to minimize the performance index (3.6) of the optimal (3.7). To find the values for the gain matrix in the control input, it is necessary to solve the algebraic Riccati equation. The P-D and LQR controls were implemented in the control of mathematical and multibody anklefoot model with the goal of performing reference following, where the reference consists of ankle angle during gait. Both models were considered with rehabilitation purposes, where the mathematical model would simulate the rehabilitation without ground contact, and the multibody model to simulate the rehabilitation with ground contact. The performance specifications in the control of both models, the desire was to have a following error inferior to three degrees Gait Cycle (%) Figure 3.7: Ankle angle of simulated and controlled multibody ankle-foot model during gait cycle. In general, the reference following was acceptable, not showing abrupt changes during the gait, even having parameters change during the states. Although the value of the angle error can have biomechanical acceptance, when analyzing the ankle torque of the controlled models, it is visible that the peak ankle torque was not achieved The ankle torque deficit is visible in the interval from 35% to 55% of GC, which includes the peak torque. In a realistic situation, this ankle torque deficit could cause some unrestrained tibial advancement and failure in propelling the body forward. Little discontinuities are also visible around 22% and 60% of GC in the ankle torque, which are caused by the changing in the parameters of the controllers. The use of same parameters for the entire gait cycle was tested, however, the control action at states 1 and 4 were very oscillatory Impedance Control Simulated Model P-D Controller LQR Controller Impedance control was implemented in the multibody ankle-foot model with the goal of assisting the ankle movement during gait by trying to mimic the human control of ankle joint. Impedance control uses a target reference in the control law in which the system stiffness and damping are related. Since there is no reference following, this controller requires a trigger in order to update the target reference, considering that these triggers cannot rely solely on the ankle angle. Therefore, the impedance control was only implemented with the multibody ankle-foot model, where the contact with the ground could provide the reference for the different states of the gait cycle (GC). 5
6 Amplitude Table 3.1: Parameters and characteristics of implemented impedance control of multibody anklefoot model during GC. States Loading Response ( 1 ) Stance ( 2 ) Pre Swing ( 3 ) Swing ( 4 ) Figure 3.8: The desired effect of impedance control represented by the use of a rotational mass-springdamper system. In the implementation of impedance control, it was necessary the tuning of four parameters: ankle angle target, ankle angular velocity target, ankle stiffness, and ankle damping. Considering the states triggers presented in section 3.4, the ankle angle target was set by the desired ankle angle in the end of the considered state, i.e., if in the end of state 2 (weight acceptance) the ankle is expected to be the neutral position, then zero degrees will be the ankle angle target. The same procedure was applied to the ankle angular velocity target. The other two parameters were set by trial and error, in order to achieve the following goals: State 1: Controlled plantar flexion to avoid foot slap; State 2: Avoid unrestrained tibial advancement and initiate the propulsion; State 3: Provide final propulsion, moving to peak angle plantar flexion; State 4: Provide toe clearance to avoid toe drag and finalize the swing period with the ankle smoothly dorsiflexed; Rotational Damping B (Nms/rad) Rotational Stiffness K (Nm/rad) Target ankle angle (deg) Target ankle angular velocity - (deg/s) Natural frequency (rad/s) Damping ratio In the overall, impedance control strategy presented good results in the control of multibody ankle-foot model. Disregarding some discontinuities in the states transitions, the controller proved to be capable of avoiding foot slap, provide a controlled tibial advancement and propel the body forward. Although a large ankle angle error occurred in the initial swing phase, the toe drag was avoided and the swing period ended with the foot slightly dorsiflexed State 1 State 2 State 3 State Time (s) Figure 3.10: Responses to a unit step input of a closed-loop system with mathematical ankle-foot model and impedance control. Figure 3.9: Ankle angle during gait cycle from gait data and controlled multibody ankle-foot model with impedance control. In basic second-order systems, a damping ratio superior to the unity correspond to overdamped systems, verifying no overshoot on the step response. However, in this particular system, the controller adds a zero to the system which causes the overshoot in the step responses (Figure 3.10), even for damping ratios superior to the unity. This event, present when the system is in the second, third, and fourth states, allows a 6
7 decrease in either in the rise time as in the overshoot, increasing the control possibilities. In a physical implementation of this controller, the chosen parameters may not lead to the same type of responses, since it depends on the characteristics of the physical actuator in use. In a general comparison between the gains of the three control strategies, the impedance control strategy required less control effort. However, the ankle angle error in impedance control was substantially larger than in the other two control strategies. 4. ACTIVE ANKLE-FOOT ORTHOSIS Provide a full assistance during different gait phases cannot be provided by a common anklefoot orthosis (AFO). These common orthoses are passive systems, acting like energy storing systems, which generally take the foot back to its neutral position. Aiming for a system capable of assisting the ankle movement during gait led to the development of an active ankle-foot orthosis (AAFO) AAFO Design As design parameter, it was defined that the AFO would be actuated by system based on linear motion. In the calculation of the linear quantities, it was take in account the fact that the arm does not have a constant value, because the line of action of the actuator is practically vertical and point of force application rotates through the ankle axis. The corresponding linear quantities were calculated considering that the arm between the ankle axis and point of force application,, had 0.08m of length, with the results presented in Table 4.1. Table 4.1: Linear quantities required for an actuator to assist the ankle movement. Quantity Linear Displacement - (mm) Linear Velocity - (mm.s -1 ) Linear Acceleration - (mm.s -2 ) Maximum negative Maximum positive Linear Force - (N) Power - (W) Components of the AAFO Figure 4.1: Active ankle-foot orthosis 3D model: (a) left view, (b) right view. AFO The AFO chosen for the system was a standard polypropylene AFO, with approximately 5 millimeters of thickness, and articulated aluminum joints. This joints allow motion in the sagittal plane and restrict the motion in the others planes. The motion in the sagittal plane is limited to the ankle angle range relative to the leg during gait, acting as a safety device. Some modifications on the AFO are required for the adaptation of the ankle angle sensor and fixation of the SEA. Ankle Angle Sensor The selected rotary potentiometer was a Bourns 6639S kω. To ensure accurate measures of the ankle between the leg and the foot (ankle angle), the potentiometer rotation axis has must agree with the AFO joints rotation axis. Footswitches Footswitches, often called by event switches, are generally used for acquiring the timing of gait. The data from footswitches allows determining the time in stance period, as also the transition between phases. The placement of the foot sensors is crucial for detecting correctly the desired states transition. Series Elastic Actuator (SEA) The SEA consists of a brushless DC motor coupled laterally to a ball screw shaft by a gear drive. The nut of the ball screw shaft is connected to a set of springs placed in series with carbon bars that transmit the forces to the output. These springs are responsible for the low impedance of the actuator. Further details of the actuator are presented in next section. 7
8 Input and Output devices Communicating and controlling with the sensors and actuator in a physical prototype of the AAFO requires the use of data acquisition unit (DAQ) and controller for the rotary motor. The DAQ unit establishes the communication between the sensors and actuator, and the overall processing unit, the laptop. The motor controller, is a dedicate controller for the rotary DC motor and also communicates with the main controller by the DAQ unit. This is a basic DAQ unit with 8 analog inputs, 2 analog outputs, 12 digital I/O, and a 32-bit counter. Power Supply Aiming for an autonomous system, the energy to provide the system cannot be external. Two elements in the system require the majority of the energy: laptop and actuator. As laptop has its own battery, it was necessary to choose a battery to provide energy to the actuator. A LiPo battery was chosen. With the three pack configuration, the total energy capacity, kJ, has around three times the required energy for 12,000 steps in normal cadence. The main goal of this work is presented in Figure 4.2, an autonomous AAFO assisting an individual during gait. The rest of the unit includes wires, batteries, controller, DAQ, and processing unit. This unit is expected to have approximately 6kg, by considering a processing unit (laptop) with 2.5kg of mass, wires with a total mass of 1.5kg, batteries with a total mass of 1.6kg, controller with 0,25kg of mass, and the DAQ with 0,08kg of mass. 5. ACTUATING UNIT The demanding task of providing power to the ankle joint during gait requires an actuating unit with high power density. The fact of being coupled to an ankle-foot orthosis (AFO) and thus to human leg, implies the actuating unit to be smallest, and lightest as possible. The main idea is to have a system capable of supplying enough energy to provide the ankle movement during gait, without neglecting the size and weight Series Elastic Actuator Design A linear series elastic actuator (SEA) is an actuator that has an elastic element in series with the motor and the ball screw. A sensor measures the displacement of the elastic element and force is implied by Hooke s Law. By placing a spring in series with the output of an electric motor, the force control performance is improved. The motor is isolated from shock loads, and the effects of torque ripple, friction, and backlash are filtered by the elastic element (15 p. 77) Components Selection The design possibilities for a SEA are very large. Besides topology and geometry, there are six major components to take in account for the design: motor, amplifier, transmission, elasticity, sensor, and controller. Figure 4.2: Autonomous AAFO with the individual carrying the batteries and processing unit in a backpack. As a physical prototype, the proposed AAFO has the sensor-actuating unit in the leg-ankle-foot, and the controlling unit, with the respective power supply in a backpack. As a physical prototype, the proposed AAFO has the sensor-actuating unit in the leg-ankle-foot, and the controlling unit, with the respective power supply in a backpack. It is expected that the sensor-actuating unit of the AAFO will have approximately 1.3kg of mass. Figure 5.1: Series Elastic Actuator three dimensional model. DC Motor and Encoder The motor choice fell on the maxon EC-4pole W, due to its compact size and low weight. This rotary motor can develop a peak power of 8
9 Amplitude near 400W, satisfying the peak power occurred during gait cycle. Ball Screw When choosing the ball screw, the choice was made on the ball screw with the overall low peak angular velocity and low rotational inertia, leading to the ball screw with the nut BD 10x4 R Gears To have a compact actuator, the motor was coupled laterally to the screw, requiring the use of gears to transmit the power from the motor to the screw. This choice relies on the commitment between the actuator efficiency and its compactness. Motor Controller Amplifier To ensure compatibility between the motor and the controller, only controllers recommended by the motor manufacturer (16) were considered. With the interest of driving the system in current control, the controller choice fell on the EPOS2 50/5 Positioning Controller. Springs The spring stiffness is related with the mechanical impedance of the SEA, as also with the desired force output. Facing this, three different springs were chosen, differing on the stiffness. Linear Sensor For measuring the spring displacement, a linear potentiometer was chosen, having the sensor approximately 10g of mass SEA Control The close-loop transfer function for the control of the SEA is given by (5.1) where is the proportional gain, is the derivative gain, is the damping term, is the lumped mass, and is the total spring stiffness. The implementation of the SEA in the control of the ankle joint did not affect those systems. However, the selection of parameters for the SEA controller can be improved so the effect of the SEA in the human body control can be present better results SEA Characteristics With the parameters present in Table 5.1, the closed-loop transfer function of the SEA was subjected to a unitary step, with the response presented in Figure 5.2. As expected, the step response presents a considerable overshoot, representing the low impedance of the system. Table 5.1: Properties of the modeled actuator used in the simulation control. Some of the values are calculated from motor, and screw literature. Parameter Value Units Maximum Force 1515 N Maximum Speed 0.31 m/s Intermittent Power 476 W Actuator Mass 0.75 kg Dynamic Mass kg Spring Constant kn / m Damping Ns / m Operational bandwidth Hz Natural frequency Hz Damping ratio No units Nominal Voltage U 48 V Maximum current (peak) 10 A Gear reduction screw-nut - Gear reduction motor-nut No units 5495 No units Time (s) Figure 5.2: Unit step response of the closed-loop transfer function of SEA. The implementation of the SEA in the control of the ankle joint did not affect those systems. However, the selection of parameters for the SEA controller can be improved so the effect of the SEA in the human body control can be present better results. The proposed design for the SEA is expected to have a total mass of 0.75kg, provide a maximum force of 1515 N, and a maximum velocity of 9
10 0.31m/s. Although the losses in gear reductions have not been taken in account, it is expected a great potential from the designed SEA. 6. CONCLUSIONS With the mathematical ankle-foot model it was not possible to extract the dynamics involved in the movement of the ankle. By contrast, the multibody ankle-foot model exhibits an acceptable behavior when comparing to the data. With the multibody model, to maintain the following error, the control effort was much higher. A general comparison between the gains of the three control strategies, the impedance control strategy required less control effort. However, the ankle angle error in impedance control was substantially larger than in the other two control strategies. All control strategies presented high parameters values, which in a physical implementation may not be possible to achieve. The designed AAFO and SEA are expected to provide a full assistance during gait in an autonomous way. With the selected parts for measuring the gait and provide energy, as the redesign of the SEA that made it more compact, light and with more power output, the construction of the prototype is the next step Future Work It would be good to use a more realistic foot contact model so that the dynamics through the ankle joint could be more close to the gait tables. Thus, with full modeling and control of the locomotor unit, it would be possible to study of functional errors of the ankle joint affect the gait. In the design of AAFO, a further study in systems capable of absorbing external forces to output later during the peak torque would allow having smaller motor and thus, smaller battery. For instance, coupling parallel rotational springs in the ankle joint could absorb the energy during loading response phase and output the energy during the mid stance phase. A solution for having a lighter and compact system for the AAFO could pass by connecting the ankle joint and the actuator application force point with a beam. By setting gages in the beam, the deflection of the beam could be obtained and thus the corresponding force applied by the actuator. 7. ACKNOWLEDGMENTS This work is inserted in the FCT DACHOR project Multibody Dynamics and Control of Hybrid Orthoses (MIT-Pt/BS-HHMS/0042/2008). 8. REFERENCES 1. Pons, J. Wearable Robots: Biomechatronic Exoskeletons. s.l. : John Wiley & Sons, Ltd, Rose, J. and Gamble, J. Human Walking, 3rd Edition. s.l. : Lippincott Williams & Wilkins, Cooper, G, [ed.]. Essencial Physical Medicine and Rehabilitation. New York : Humana Press, Össur. Össur. Össur UK. [Online] [Cited: August 16, 2010.] 5. Winter, D. Biomechanics and Motor Control of Human Movement. Hoboken, NJ, USA : John Wiley & Sons, Ltd, Whittle, M. Gait Analysis: An Introduction. Philadelphia : Elsevier, Harris, G., Smith, P. and Marks, R. Foot and Ankle Motion Analysis: Clinical Treatment and Technology. New York : Taylor & Francis Group, Nise, N. Control Systems Engineering. 4th Edition. Hoboken, NJ, USA : John Wiley & Sons, Inc, Ogata, K. Modern Control Engineering. New Jersey : Prentice Hall, Bishop, Robert H. Mechatronic Systems, Sensors, and Actuators: Fundamentals and Modeling. Texas, Austin : CRC Press, Tipler, P. and Mosca, G. Physics for Scientists and Engineers, 5th edition. New York : W. H. Freeman and Componany, MathWorks. MathWorks - MATLAB and Simulink for Technical Computing. [Online] [Citação: 18 de August de 2010.] Levine, W. The Control Handbook. New York : CRC Press, Inc, Vol. I. 14. Ogata, K. Discrete-time control systems, 2nd edition. New Jersey : Prentice Hall, Williamson, M. M. Series Elastic Actuators. Master's thesis. Cambridge : Massachusetts Institute of Technology, maxon motor ag. maxon global. [Online] [Cited: May 20, 2010.] 10
Motion Control of a Bipedal Walking Robot
Motion Control of a Bipedal Walking Robot Lai Wei Ying, Tang Howe Hing, Mohamed bin Hussein Faculty of Mechanical Engineering Universiti Teknologi Malaysia, 81310 UTM Skudai, Johor, Malaysia. Wylai2@live.my
More informationBiomechanics and Models of Locomotion
Physics-Based Models for People Tracking: Biomechanics and Models of Locomotion Marcus Brubaker 1 Leonid Sigal 1,2 David J Fleet 1 1 University of Toronto 2 Disney Research, Pittsburgh Biomechanics Biomechanics
More informationComputer Aided Drafting, Design and Manufacturing Volume 26, Number 2, June 2016, Page 53. The design of exoskeleton lower limbs rehabilitation robot
Computer Aided Drafting, Design and Manufacturing Volume 26, Number 2, June 2016, Page 53 CADDM The design of exoskeleton lower limbs rehabilitation robot Zhao Xiayun 1, Wang Zhengxing 2, Liu Zhengyu 1,3,
More informationKochi University of Technology Aca Study on Dynamic Analysis and Wea Title stem for Golf Swing Author(s) LI, Zhiwei Citation 高知工科大学, 博士論文. Date of 2015-03 issue URL http://hdl.handle.net/10173/1281 Rights
More informationLab 4: Root Locus Based Control Design
Lab 4: Root Locus Based Control Design References: Franklin, Powell and Emami-Naeini. Feedback Control of Dynamic Systems, 3 rd ed. Addison-Wesley, Massachusetts: 1994. Ogata, Katsuhiko. Modern Control
More informationAn investigation of kinematic and kinetic variables for the description of prosthetic gait using the ENOCH system
An investigation of kinematic and kinetic variables for the description of prosthetic gait using the ENOCH system K. OBERG and H. LANSHAMMAR* Amputee Training and Research Unit, University Hospital, Fack,
More informationHumanoid Robots and biped locomotion. Contact: Egidio Falotico
Humanoid Robots and biped locomotion Contact: Egidio Falotico e.falotico@sssup.it Outline What is a Humanoid? Why Develop Humanoids? Challenges in Humanoid robotics Active vs Passive Locomotion Active
More informationEXPERIMENTAL STUDY OF EXOSKELETON FOR ANKLE AND KNEE JOINT
EXPERIMENTAL STUDY OF EXOSKELETON FOR ANKLE AND KNEE JOINT PROJECT REFERENCE NO. : 37S0925 COLLEGE : NEW HORIZON COLLEGE OF ENGINEERING, BANGALORE BRANCH : MECHANICAL ENGINEERING GUIDES : DR GANESHA PRASAD
More informationToward a Human-like Biped Robot with Compliant Legs
Book Title Book Editors IOS Press, 2003 1 Toward a Human-like Biped Robot with Compliant Legs Fumiya Iida a,b,1, Yohei Minekawa a Juergen Rummel a and Andre Seyfarth a a Locomotion Laboratory, University
More informationManaging and Recycling Human Energy: A Mechanical Redesign of the UCSC Lower Limb Exoskeleton. Rachel Rieger, Jacob Rosen
Managing and Recycling Human Energy: A Mechanical Redesign of the UCSC Lower Limb Exoskeleton Overview Rachel Rieger, Jacob Rosen University of California Santa Cruz Lower limb exoskeletons are a staple
More informationSimulation of the Hybtor Robot
Simulation of the Hybtor Robot Pekka Aarnio, Kari Koskinen and Sami Salmi Information and Computer Systems in Automation Helsinki University of Technology ABSTRACT A dynamic rigid body simulation model
More informationREPORT DOCUMENTATION PAGE
REPORT DOCUMENTATION PAGE Form Approved OMB NO. 0704-0188 The public reporting burden for this collection of information is estimated to average 1 hour per response, including the time for reviewing instructions,
More informationMicroprocessor Technology in Ankle Prosthetics
Microprocessor Technology in Ankle Prosthetics Arizona State University Dr. Thomas Sugar Former Students LTC Joseph Hitt, PhD Dr. Kevin Hollander Dr. Matthew Holgate Dr. Jeffrey Ward Mr. Alex Boehler Mr.
More informationDevelopment of Fish type Robot based on the Analysis of Swimming Motion of Bluefin Tuna Comparison between Tuna-type Fin and Rectangular Fin -
Development of Fish type Robot based on the Analysis of Swimming Motion of Bluefin Tuna Comparison between Tuna-type Fin and Rectangular Fin - Katsuya KUGAI* Abstract The swimming motion of Tuna type fishes
More informationIn memory of Dr. Kevin P. Granata, my graduate advisor, who was killed protecting others on the morning of April 16, 2007.
Acknowledgement In memory of Dr. Kevin P. Granata, my graduate advisor, who was killed protecting others on the morning of April 16, 2007. There are many others without whom I could not have completed
More informationInertial compensation for belt acceleration in an instrumented treadmill
Inertial compensation for belt acceleration in an instrumented treadmill Sandra K. Hnat, Antonie J. van den Bogert Department of Mechanical Engineering, Cleveland State University Cleveland, OH 44115,
More informationUsing GPOPS-II to optimize sum of squared torques of a double pendulum as a prosthesis leg. Abstract
Using GPOPS-II to optimize sum of squared torques of a double pendulum as a prosthesis leg Abstract Milad Zarei MCE 593 Prosthesis Design & Control A two-dimensional, two links pendulum is developed to
More informationSample Solution for Problem 1.a
Sample Solution for Problem 1.a 1 Inverted Pendulum Model (IPM) 1.1 Equations of Motion and Ground Reaction Forces Figure 1: Scheme of the Inverted Pendulum Model (IPM). The equations of motion of this
More informationSpeed Control System Design in Bicycle Robot by Low Power Method. Abstract
The 2 nd RMUTP International Conference 2010 Page 195 Speed Control System Design in Bicycle Robot by Low Power Method Sunthorn Wiriya, Nikom Distaklu and Suppachai Howimanporn*. Department of Electrical
More informationA NEW GOLF-SWING ROBOT MODEL UTILIZING SHAFT ELASTICITY
Journal of Sound and Vibration (1998) 17(1), 17 31 Article No. sv981733 A NEW GOLF-SWING ROBOT MODEL UTILIZING SHAFT ELASTICITY S. SUZUKI Department of Mechanical System Engineering, Kitami Institute of
More informationDynamically stepping over large obstacle utilizing PSO optimization in the B4LC system
1 Dynamically stepping over large obstacle utilizing PSO optimization in the B4LC system QI LIU, JIE ZHAO, KARSTEN BERNS Robotics Research Lab, University of Kaiserslautern, Kaiserslautern, 67655, Germany
More informationFunctional Outcomes of a Custom, Energy Harvesting "Bullfrog" AFO
Functional Outcomes of a Custom, Energy Harvesting "Bullfrog" AFO Principal Investigator Géza F. Kogler, Ph.D., C.O. Co-Principal Investigator Young-Hui Chang, Ph.D. Co-Investigators Hosna Sharafi, BME
More informationDevelopment of an end-effector to simulate the foot to ball interaction of an instep kick in soccer
Available online at www.sciencedirect.com Procedia Engineering 34 (2012 ) 284 289 9 th Conference of the International Sports Engineering Association (ISEA) Development of an end-effector to simulate the
More informationCHAPTER IV FINITE ELEMENT ANALYSIS OF THE KNEE JOINT WITHOUT A MEDICAL IMPLANT
39 CHAPTER IV FINITE ELEMENT ANALYSIS OF THE KNEE JOINT WITHOUT A MEDICAL IMPLANT 4.1 Modeling in Biomechanics The human body, apart of all its other functions is a mechanical mechanism and a structure,
More informationvideo Purpose Pathological Gait Objectives: Primary, Secondary and Compensatory Gait Deviations in CP AACPDM IC #3 1
s in CP Disclosure Information AACPDM 71st Annual Meeting September 13-16, 2017 Speaker Names: Sylvia Ounpuu, MSc and Kristan Pierz, MD Differentiating Between, Secondary and Compensatory Mechanisms in
More informationKinematic Differences between Set- and Jump-Shot Motions in Basketball
Proceedings Kinematic Differences between Set- and Jump-Shot Motions in Basketball Hiroki Okubo 1, * and Mont Hubbard 2 1 Department of Advanced Robotics, Chiba Institute of Technology, 2-17-1 Tsudanuma,
More informationFriction properties of the face of a hand-held tennis racket
Available online at www.sciencedirect.com Procedia Engineering 34 (2012 ) 544 549 9 th Conference of the International Sports Engineering Association (ISEA) Friction properties of the face of a hand-held
More informationBody Stabilization of PDW toward Humanoid Walking
Body Stabilization of PDW toward Humanoid Walking Masaki Haruna, Masaki Ogino, Koh Hosoda, Minoru Asada Dept. of Adaptive Machine Systems, Osaka University, Suita, Osaka, 565-0871, Japan ABSTRACT Passive
More informationINTERACTION OF STEP LENGTH AND STEP RATE DURING SPRINT RUNNING
INTERACTION OF STEP LENGTH AND STEP RATE DURING SPRINT RUNNING Joseph P. Hunter 1, Robert N. Marshall 1,, and Peter J. McNair 3 1 Department of Sport and Exercise Science, The University of Auckland, Auckland,
More informationGait analysis for the development of the biped robot foot structure
Preprints of the 9th World Congress The International Federation of Automatic Control Cape Town, South Africa. August 4-9, 4 Gait analysis for the development of the biped robot foot structure Yusuke OGAWA
More informationJoint Torque Evaluation of Lower Limbs in Bicycle Pedaling
11th conference of the International Sports Engineering Association, ISEA 216 Delft University of Technology; July 12 th Joint Torque Evaluation of Lower Limbs in Bicycle Pedaling Hiroki Yamazaki Akihiro
More informationWalking Simulator Mechanism
The Downtown Review Volume 2 Issue 2 Article 4 2015 Walking Simulator Mechanism Titus Lungu Cleveland State University Igor Tachynskyy Cleveland State University Omri Tayyara Cleveland State University
More informationToward a Human-like Biped Robot with Compliant Legs
Book Title Book Editors IOS Press, 23 1 Toward a Human-like Biped Robot with Compliant Legs Fumiya Iida a,b,1, Yohei Minekawa a Juergen Rummel a and Andre Seyfarth a a Locomotion Laboratory, University
More informationControl Strategies for operation of pitch regulated turbines above cut-out wind speeds
Control Strategies for operation of pitch regulated turbines above cut-out wind speeds Helen Markou 1 Denmark and Torben J. Larsen, Risø-DTU, P.O.box 49, DK-4000 Roskilde, Abstract The importance of continuing
More informationITTC Recommended Procedures and Guidelines
Page 1 of 6 Table of Contents 1. PURPOSE...2 2. PARAMETERS...2 2.1 General Considerations...2 3 DESCRIPTION OF PROCEDURE...2 3.1 Model Design and Construction...2 3.2 Measurements...3 3.5 Execution of
More informationLQG Based Robust Tracking Control of Blood Gases during Extracorporeal Membrane Oxygenation
2011 American Control Conference on O'Farrell Street, San Francisco, CA, USA June 29 - July 01, 2011 LQG Based Robust Tracking Control of Blood Gases during Extracorporeal Membrane Oxygenation David J.
More informationOptimization of an off-road bicycle with four-bar linkage rear suspension
Proceedings of MUSME 2008, the International Symposium on Multibody Systems and Mechatronics San Juan (Argentina), 8-12 April 2008 Paper n. 02-MUSME08 Optimization of an off-road bicycle with four-bar
More informationAnalysis of ankle kinetics and energy consumption with an advanced microprocessor controlled ankle foot prosthesis.
Analysis of ankle kinetics and energy consumption with an advanced microprocessor controlled ankle foot prosthesis. D.Moser, N.Stech, J.McCarthy, G.Harris, S.Zahedi, A.McDougall Summary This study reports
More informationAvailable online at Prediction of energy efficient pedal forces in cycling using musculoskeletal simulation models
Available online at www.sciencedirect.com Engineering 2 00 (2010) (2009) 3211 3215 000 000 Engineering www.elsevier.com/locate/procedia 8 th Conference of the International Sports Engineering Association
More information+ t1 t2 moment-time curves
Part 6 - Angular Kinematics / Angular Impulse 1. While jumping over a hurdle, an athlete s hip angle was measured to be 2.41 radians. Within 0.15 seconds, the hurdler s hip angle changed to be 3.29 radians.
More informationBUILDING A BETTER PASSIVE WALKER
BUILDING A BETTER PASSIVE WALKER Abstract - A passive dynamic walker is a mechanism which uses gravitational energy to walk down an incline with a periodic gait. Simple passive dynamic walkers have an
More informationNormal and Abnormal Gait
Normal and Abnormal Gait Adrielle Fry, MD EvergreenHealth, Division of Sport and Spine University of Washington Board Review Course March 6, 2017 What are we going to cover? Definitions and key concepts
More informationRELIABILITY ASSESSMENT, STATIC AND DYNAMIC RESPONSE OF TRANSMISSION LINE TOWER: A COMPARATIVE STUDY
RELIABILITY ASSESSMENT, STATIC AND DYNAMIC RESPONSE OF TRANSMISSION LINE TOWER: A COMPARATIVE STUDY Yusuf Mansur Hashim M. Tech (Structural Engineering) Student, Sharda University, Greater Noida, (India)
More informationDYNAMIC POSITIONING CONFERENCE October 7-8, New Applications. Dynamic Positioning for Heavy Lift Applications
Return to Session Directory DYNAMIC POSITIONING CONFERENCE October 7-8, 2008 New Applications Dynamic Positioning for Heavy Lift Applications John Flint and Richard Stephens Converteam UK Ltd. (Rugby,
More informationFail Operational Controls for an Independent Metering Valve
Group 14 - System Intergration and Safety Paper 14-3 465 Fail Operational Controls for an Independent Metering Valve Michael Rannow Eaton Corporation, 7945 Wallace Rd., Eden Prairie, MN, 55347, email:
More informationThe Starting Point. Prosthetic Alignment in the Transtibial Amputee. Outline. COM Motion in the Coronal Plane
Prosthetic Alignment in the Transtibial Amputee The Starting Point David C. Morgenroth, MD, Department of Rehabilitation Medicine University of Washington VAPSHCS Outline COM Motion in the Coronal Plane
More informationAN31E Application Note
Balancing Theory Aim of balancing How an unbalance evolves An unbalance exists when the principle mass axis of a rotating body, the so-called axis of inertia, does not coincide with the rotational axis.
More informationPERCEPTIVE ROBOT MOVING IN 3D WORLD. D.E- Okhotsimsky, A.K. Platonov USSR
PERCEPTIVE ROBOT MOVING IN 3D WORLD D.E- Okhotsimsky, A.K. Platonov USSR Abstract. This paper reflects the state of development of multilevel control algorithms for a six-legged mobile robot. The robot
More informationGROUND REACTION FORCE DOMINANT VERSUS NON-DOMINANT SINGLE LEG STEP OFF
GROUND REACTION FORCE DOMINANT VERSUS NON-DOMINANT SINGLE LEG STEP OFF Sara Gharabaghli, Rebecca Krogstad, Sara Lynch, Sofia Saavedra, and Tamara Wright California State University, San Marcos, San Marcos,
More informationRanger Walking Initiation Stephanie Schneider 5/15/2012 Final Report for Cornell Ranger Research
1 Ranger Walking Initiation Stephanie Schneider sns74@cornell.edu 5/15/2012 Final Report for Cornell Ranger Research Abstract I joined the Biorobotics Lab this semester to gain experience with an application
More informationA CONTINOUS ROTARY ACTUATION MECHANISM FOR A POWERED HIP EXOSKELETON
University of Massachusetts Amherst ScholarWorks@UMass Amherst Masters Theses Dissertations and Theses 2015 A CONTINOUS ROTARY ACTUATION MECHANISM FOR A POWERED HIP EXOSKELETON Matthew C. Ryder University
More informationby Michael Young Human Performance Consulting
by Michael Young Human Performance Consulting The high performance division of USATF commissioned research to determine what variables were most critical to success in the shot put The objective of the
More informationA New Approach to Modeling Vertical Stiffness in Heel-Toe Distance Runners
Brigham Young University BYU ScholarsArchive All Faculty Publications 2003-12-01 A New Approach to Modeling Vertical Stiffness in Heel-Toe Distance Runners Iain Hunter iain_hunter@byu.edu Follow this and
More informationSteffen Willwacher, Katina Fischer, Gert Peter Brüggemann Institute of Biomechanics and Orthopaedics, German Sport University, Cologne, Germany
P01-3 ID126 SURFACE STIFFNESS AFFECTS JOINT LOADING IN RUNNING Steffen Willwacher, Katina Fischer, Gert Peter Brüggemann Institute of Biomechanics and Orthopaedics, German Sport University, Cologne, Germany
More informationApplication of pushover analysis in estimating seismic demands for large-span spatial structure
28 September 2 October 2009, Universidad Politecnica de Valencia, Spain Alberto DOMINGO and Carlos LAZARO (eds.) Application of pushover analysis in estimating seismic demands for large-span spatial structure
More informationCurrent issues regarding induced acceleration analysis of walking using the integration method to decompose the GRF
Current issues regarding induced acceleration analysis of walking using the integration method to decompose the GRF George Chen May 17, 2002 Stanford Neuromuscular Biomechanics Lab Group Muscle contribution
More informationArtifacts Due to Filtering Mismatch in Drop Landing Moment Data
Camenga et al. UW-L Journal of Undergraduate Research XVI (213) Artifacts Due to Filtering Mismatch in Drop Landing Moment Data Elizabeth T. Camenga, Casey J. Rutten, Brendan D. Gould, Jillian T. Asmus,
More informationDecentralized Autonomous Control of a Myriapod Locomotion Robot
Decentralized utonomous Control of a Myriapod Locomotion Robot hmet Onat Sabanci University, Turkey onat@sabanciuniv.edu Kazuo Tsuchiya Kyoto University, Japan tsuchiya@kuaero.kyoto-u.ac.jp Katsuyoshi
More informationAuthor s Name Name of the Paper Session. Positioning Committee. Marine Technology Society. DYNAMIC POSITIONING CONFERENCE September 18-19, 2001
Author s Name Name of the Paper Session PDynamic Positioning Committee Marine Technology Society DYNAMIC POSITIONING CONFERENCE September 18-19, 2001 POWER PLANT SESSION A New Concept for Fuel Tight DP
More informationDesign of a double quadruped for the Tech United soccer robot
Design of a double quadruped for the Tech United soccer robot M.J. Naber (0571509) DCT report number: 2009.134 Master Open Space project Eindhoven, 21 December 2009 Supervisor dr.ir. P.C.J.N. Rosielle
More informationPosture influences ground reaction force: implications for crouch gait
University of Tennessee, Knoxville From the SelectedWorks of Jeffrey A. Reinbolt July 14, 2010 Posture influences ground reaction force: implications for crouch gait H. X. Hoang Jeffrey A. Reinbolt, University
More informationLesson 14: Simple harmonic motion, Waves (Sections )
Circular Motion and Simple Harmonic Motion The projection of uniform circular motion along any ais (the -ais here) is the same as simple harmonic motion. We use our understanding of uniform circular motion
More informationWalking with coffee: when and why coffee spills
Walking with coffee: when and why coffee spills Hans C. Mayer and Rouslan Krechetnikov Department of Mechanical Engineering University of California at Santa Barbara February 20-24, 2012 Page 1/25 Motivation
More informationLimit Cycle Walking and Running of Biped Robots
Tokyo Institute of Technology Yamakita Lab. Limit Cycle Walking and Running of Biped Robots Masaki Yamakita Tokyo Institute of Technology Introduction of Yamakita Lab. 1/14 Other Research Topics State
More informationTHE ANKLE-HIP TRANSVERSE PLANE COUPLING DURING THE STANCE PHASE OF NORMAL WALKING
THE ANKLE-HIP TRANSVERSE PLANE COUPLING DURING THE STANCE PHASE OF NORMAL WALKING Thales R. Souza, Rafael Z. Pinto, Renato G. Trede, Nadja C. Pereira, Renata N. Kirkwood and Sérgio T. Fonseca. Movement
More informationA MODIFIED DYNAMIC MODEL OF THE HUMAN LOWER LIMB DURING COMPLETE GAIT CYCLE
Int. J. Mech. Eng. & Rob. Res. 2013 S M Nacy et al., 2013 Research Paper ISSN 2278 0149 www.ijmerr.com Vol. 2, No. 2, April 2013 2013 IJMERR. All Rights Reserved A MODIFIED DYNAMI MODEL OF THE HUMAN LOWER
More informationDesign of a Microcontroller-Based Pitch Angle Controller for a Wind Powered Generator
Journal of Engineering and Science Research 1 (2): 133-138, e-issn RMP Publications, DOI: Design of a Microcontroller-Based Pitch Angle Controller for a Wind Powered Generator Glenn V. Magwili, Michael
More informationC-Brace Orthotronic Mobility System
C-Brace Orthotronic Mobility System You ll always remember your first step Information for practitioners C-Brace Orthotics reinvented Until now, you and your patients with conditions like incomplete spinal
More informationA Biomechanical Approach to Javelin. Blake Vajgrt. Concordia University. December 5 th, 2012
A Biomechanical Approach to Javelin Blake Vajgrt Concordia University December 5 th, 2012 The Biomechanical Approach to Javelin 2 The Biomechanical Approach to Javelin Javelin is one of the four throwing
More informationHermetic Compressor Manifold Analysis With the Use of the Finite Element Method
Purdue University Purdue e-pubs International Compressor Engineering Conference School of Mechanical Engineering 2008 Hermetic Compressor Manifold Analysis With the Use of the Finite Element Method Rinaldo
More informationCharacterizers for control loops
Characterizers for control loops By: F. G. Shinskey (May 1999) Introduction Commercial controllers such as the PID series (proportional, integral, derivative, and their combinations) are linear devices
More informationGait. Kinesiology RHS 341 Lecture 12 Dr. Einas Al-Eisa
Gait Kinesiology RHS 341 Lecture 12 Dr. Einas Al-Eisa Definitions Locomotion = the act of moving from one place to the other Gait = the manner of walking Definitions Walking = a smooth, highly coordinated,
More informationASSESMENT Introduction REPORTS Running Reports Walking Reports Written Report
ASSESMENT REPORTS Introduction Left panel Avatar Playback Right Panel Patient Gait Parameters Report Tab Click on parameter to view avatar at that point in time 2 Introduction Software will compare gait
More informationDynamic analysis and motion measurement of ski turns using inertial and force sensors
Available online at www.sciencedirect.com Procedia Engineering 6 ( 213 ) 355 36 6th Asia-Pacific Conference on Sports Technology Dynamic analysis and motion measurement of ski turns using inertial and
More informationABSTRACT PATTERNS USING 3D-DYNAMIC MODELING. Kaustav Nandy, Master of Science, Department of Electrical And Computer Engineering
ABSTRACT Title of Thesis: IDENTIFICATION OF HUMAN WALKING PATTERNS USING 3D-DYNAMIC MODELING Kaustav Nandy, Master of Science, 26 Thesis Directed By: Professor. Rama Chellappa Department of Electrical
More informationApplication Block Library Fan Control Optimization
Application Block Library Fan Control Optimization About This Document This document gives general description and guidelines for wide range fan operation optimisation. Optimisation of the fan operation
More informationOPTIMAL TRAJECTORY GENERATION OF COMPASS-GAIT BIPED BASED ON PASSIVE DYNAMIC WALKING
OPTIMAL TRAJECTORY GENERATION OF COMPASS-GAIT BIPED BASED ON PASSIVE DYNAMIC WALKING Minseung Kim Dept. of Computer Science Illinois Institute of Technology 3201 S. State St. Box 2082 Chicago IL 60616
More information1. A tendency to roll or heel when turning (a known and typically constant disturbance) 2. Motion induced by surface waves of certain frequencies.
Department of Mechanical Engineering Massachusetts Institute of Technology 2.14 Analysis and Design of Feedback Control Systems Fall 2004 October 21, 2004 Case Study on Ship Roll Control Problem Statement:
More informationHIP-KNEE control for gait assistance with Powered Knee Orthosis
Loughborough University Institutional Repository HIP-KNEE control for gait assistance with Powered Knee Orthosis This item was submitted to Loughborough University's Institutional Repository by the/an
More informationKintrol Instructions for Use Product Number: VS4
Kintrol Instructions for Use Product Number: VS4 Introduction The Kintrol foot/ankle combines hydraulics and fiberglass to provide K2 ambulators an exceptionally normal walking gait regardless of surface
More informationPower Assessment of the Human Ankle during the Stance Phase of Walking for Designing a Safe Active Prosthesis in Below-Knee Amputees
Applied and Computational Mathematics 2015; 4(2-1): 7-11 Published online February 27, 2015 (http://www.sciencepublishinggroup.com/j/acm) doi: 10.11648/j.acm.s.2015040201.12 ISSN: 2328-5605 (Print); ISSN:
More informationAnalysis of Pressure Rise During Internal Arc Faults in Switchgear
Analysis of Pressure Rise During Internal Arc Faults in Switchgear ASANUMA, Gaku ONCHI, Toshiyuki TOYAMA, Kentaro ABSTRACT Switchgear include devices that play an important role in operations such as electric
More informationStress Analysis of Four-Bar Linkage Transfemoral Prosthetic in Gait Cycle
Stress Analysis of Four-Bar Linkage Transfemoral Prosthetic in Gait Cycle Sugiyanto 1, B.P. Alhakim, B. Setiana 2, R. Ismail 3 and M. Tauviqirrahman 4 * Department of Mechanical Engineering, Faculty of
More informationWaves. harmonic wave wave equation one dimensional wave equation principle of wave fronts plane waves law of reflection
Waves Vocabulary mechanical wave pulse continuous periodic wave amplitude wavelength period frequency wave velocity phase transverse wave longitudinal wave intensity displacement wave number phase velocity
More informationIn this course you will learn the following
Module 11 : Example study of robots Lecture 40 : NATARAJ a case study of a 6-legged robot Objectives In this course you will learn the following Mobile Robots Legged Robots Nataraj Robot Nataraj Development
More informationRUNNING SHOE STIFFNESS: THE EFFECT ON WALKING GAIT
RUNNING SHOE STIFFNESS: THE EFFECT ON WALKING GAIT Stephen N Stanley, Peter J M c Nair, Angela G Walker, & Robert N Marshall Auckland Institute of Technology, Auckland, New Zealand University of Auckland,
More informationA Pilot Study on Electromyographic Analysis of Single and Double Revolution Jumps in Figure Skating
Journal of Exercise Science and Physiotherapy, Vol. 5, No. 1: 14-19, 2009 A Pilot Study on Electromyographic Analysis of Single and Double Revolution Jumps in Figure Skating Taylor¹, C. L. and Psycharakis²,
More informationBasketball free-throw rebound motions
Available online at www.sciencedirect.com Procedia Engineering 3 () 94 99 5 th Asia-Pacific Congress on Sports Technology (APCST) Basketball free-throw rebound motions Hiroki Okubo a*, Mont Hubbard b a
More informationAN ISOLATED SMALL WIND TURBINE EMULATOR
AN ISOLATED SMALL WIND TURBINE EMULATOR Md. Arifujjaman Graduate Student Seminar: Master of Engineering Faculty of Engineering and Applied Science Memorial University of Newfoundland St. John s, NL, Canada
More informationA Bio-inspired Behavior Based Bipedal Locomotion Control B4LC Method for Bipedal Upslope Walking
1 A Bio-inspired Behavior Based Bipedal Locomotion Control B4LC Method for Bipedal Upslope Walking JIE ZHAO, QI LIU, STEFFEN SCHUETZ, and KARSTEN BERNS Robotics Research Lab, University of Kaiserslautern,
More informationAnemometry. Anemometry. Wind Conventions and Characteristics. Anemometry. Wind Variability. Anemometry. Function of an anemometer:
Anemometry Anemometry Function of an anemometer: Measure some or all of the components of the wind vector In homogeneous terrain, vertical component is small express wind as -D horizontal vector For some
More informationUsing sensory feedback to improve locomotion performance of the salamander robot in different environments
Using sensory feedback to improve locomotion performance of the salamander robot in different environments João Lourenço Silvério Assistant: Jérémie Knüsel Structure of the presentation: I. Overview II.
More informationYAN GU. Assistant Professor, University of Massachusetts Lowell. Frederick N. Andrews Fellowship, Graduate School, Purdue University ( )
YAN GU Assistant Professor, University of Massachusetts Lowell CONTACT INFORMATION 31 University Avenue Cumnock 4E Lowell, MA 01854 yan_gu@uml.edu 765-421-5092 http://www.locomotionandcontrolslab.com RESEARCH
More informationAn Innovative Solution for Water Bottling Using PET
An Innovative Solution for Water Bottling Using PET A. Castellano, P. Foti, A. Fraddosio, S. Marzano, M.D. Piccioni, D. Scardigno* DICAR Politecnico di Bari, Italy *Via Orabona 4, 70125 Bari, Italy, scardigno@imedado.poliba.it
More informationIncorporating 3D Suction or Discharge Plenum Geometry into a 1D Compressor Simulation Program to Calculate Compressor Pulsations
Purdue University Purdue e-pubs International Compressor Engineering Conference School of Mechanical Engineering 2012 Incorporating 3D Suction or Discharge Plenum Geometry into a 1D Compressor Simulation
More informationEfficiency Improvement of a New Vertical Axis Wind Turbine by Individual Active Control of Blade Motion
Efficiency Improvement of a New Vertical Axis Wind Turbine by Individual Active Control of Blade Motion In Seong Hwang, Seung Yong Min, In Oh Jeong, Yun Han Lee and Seung Jo Kim* School of Mechanical &
More informationModeling of Hydraulic Hose Paths
Mechanical Engineering Conference Presentations, Papers, and Proceedings Mechanical Engineering 9-2002 Modeling of Hydraulic Hose Paths Kurt A. Chipperfield Iowa State University Judy M. Vance Iowa State
More informationPurpose. Outline. Angle definition. Objectives:
Disclosure Information AACPDM 69 th Annual Meeting October 21-24, 2015 Speaker Names: Sylvia Õunpuu, MSc and Kristan Pierz, MD Gait Analysis Data Interpretation: Understanding Kinematic Relationships Within
More informationZIPWAKE DYNAMIC TRIM CONTROL SYSTEM OUTLINE OF OPERATING PRINCIPLES BEHIND THE AUTOMATIC MOTION CONTROL FEATURES
ZIPWAKE DYNAMIC TRIM CONTROL SYSTEM OUTLINE OF OPERATING PRINCIPLES BEHIND THE AUTOMATIC MOTION CONTROL FEATURES TABLE OF CONTENTS 1 INTRODUCTION 3 2 SYSTEM COMPONENTS 3 3 PITCH AND ROLL ANGLES 4 4 AUTOMATIC
More informationA Chiller Control Algorithm for Multiple Variablespeed Centrifugal Compressors
Purdue University Purdue e-pubs International Compressor Engineering Conference School of Mechanical Engineering 2014 A Chiller Control Algorithm for Multiple Variablespeed Centrifugal Compressors Piero
More information