The lower extremity exoskeleton comprises two leg supports connectable to person’s lower limbs and configured to rest on the ground during their stance phase. Each leg support comprises a thigh link and a shank link; a knee joint configured to allow flexion and extension between the shank link and the thigh link. The lower extremity exoskeleton further comprises an exoskeleton trunk connectable to the person’s upper body. The exoskeleton trunk is connectable to the thigh links of the leg supports allowing for the flexion and extension between the leg supports and the exoskeleton trunk. Two torque generators are coupled to each of the knee joints. A power unit, capable of providing power, is coupled to the torque generators. In operation when a leg support is in a stance phase and climbing a slope or stairs, the power unit injects power into the respective torque generator thereby extending the respective knee angle. When a leg support is in stance phase and not climbing a slope or stairs, the power unit does not inject any power to the respective torque generator, but without dissipating any stored power in said power unit, it forces the torque generator to resist flexion of the respective knee joint. When a leg support is in a swing phase, the power unit does not inject any power to the respective torque generator, but without dissipating any stored power in said power unit, it forces the torque generator to minimize its resistance to knee flexion and extension.

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A modular exoskeletal device adapted to fit the lower extremities of a patient during rehabilitation. The device has only two actuators during the standing stage of rehabilitation. Two additional actuators can be added, as modules, during the walking stage of rehabilitation. The actuators are affixed to the patient and provide controlled motion to at least one of the joints of the patient. A stationary control unit is separated from the patient. The control unit communicates with and directs the actuators, and has a hybrid control algorithm, such that the actuator forces are adjusted as the patient regains control of some joint motions, which is based upon the sliding-mode control theory. A back brace is affixed to the patient and helps to keep the torso of the patient in a stable, substantially vertical position.

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A quasi-passive leg exoskeleton is presented for load-carrying augmen-tation during walking. The exoskeleton has no actuators, only ankle and hip springs and a knee variable-damper. Without a payload, the exoskeleton weighs 11.7 kg and requires only 2 Watts of electrical power during loaded walking. For a 36 kg payload, we demonstrate that the quasi-passive exoskeleton transfers on average 80% of the load to the ground during the single support phase of walking. By measuring the rate of oxygen consumption on a study participant walking at a self-selected speed, we find that the exoskeleton slightly increases the walking metabolic cost of transport (COT) as compared to a standard loaded backpack (10% increase). However, a similar exoskeleton without joint springs or damping control (zero-impedance exoskeleton) is found to increase COT by 23% compared to the loaded backpack, highlighting the benefits of passive and quasi-passive joint mechanisms in the design of efficient, low-mass leg exoskeletons.

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Technological advances in robotic hardware and software have enabled powered exoskeletons to move from science fiction to the real world. The objective of this article is to emphasize two main points for future research. First, the design of future devices could be improved by exploiting biomechanical principles of animal locomotion. Two goals in exoskeleton research could parti-cularly benefit from additional physiological perspective: reduction in the metabolic energy expenditure of the user while wearing the device,and minimization of the power requirements for actuating the exoske-leton. Second, a reciprocal potential exists for robotic exoskeletons to advance our understanding of human locomotor physiology. Experimental data from humans walking and running with robotic exoskeletons could provide important insight into the metabolic cost of locomotion that is impossible to gain with other methods. Given the mutual benefits of collaboration, it is imperative that engineers and physiologists work together in future studies on robotic exoskeletons for human locomotion.

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We are witnessing an unimaginably intensive development in the field of humanoid robotics. The field of active exoskeletons experiences also its renaissance and attracts an increasing attention of researchers worldwide. The objective of this article was to indicate the beginnings and review the history of the development of active exoskeletons, their original purpose and role in the systems for rehabilitation of severely handicapped persons. The present-day development of active exoskeletons has to a large extent determined their future and applications in both the military and some specific activities that come out of the frame of rehabilitation systems and go deeply into special systems for enhancing power and expanding physical and working capabilities of the man. However, the beginnings of robotics, and especially of humanoid robotics, did not foreshadow such a progress. We take a look back on the beginnings of the development of humanoid robots, especially bipedal locomotion systems and active exoskeletons, whose development marked the beginning of the research in the domain of humanoid robotics. Once more we point out some of our pioneering results in the domain of active exoske-letons that were originally dedicated to supporting locomotion of handicapped persons. We indicated the relationships between the initial research in the field of active rehabilitation techniques and contem-porary humanoid systems and tried to predict the future directions of the development of humanoid robotics and act ive exoskeletal systems and their applications.

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