Exoskeleton robots are mechanical constructions attached to human body parts, containing actuators for influencing human motion. One important application area for exoskeletons is human motion support, for example, for disabled people, including rehabilitation training, and for force enhancement in healthy subjects. This paper surveys two exoskeleton systems developed in our laboratory. The first system is a lower-extremity exoskeleton with one actuated degree of freedom in the knee joint. This system was designed for motion support in disabled people. The second system is an exoskeleton for a human hand with 16 actuated joints, four for each finger. This hand exoskeleton will be used in rehabilitation training after hand surgeries. The application of EMG signals for motion control is presented. An overview of the design and control methods, and first experimental results for the leg exoskeleton are reported.

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This paper introduces a novel type of actuator for force-reflection to haptic master interfaces. The actuator is based on a DC motor that is relocated from the mechanism joint by means of bowden cable transmissions. After an introduction and formulation of the project goals, the paper highlights some important bowden cable transmission characteristics that influence the design of the necessary hardware. Next, a hardware prototype is presented that has been built to analyze the transmis-sion characteristics of the bowden cable transmissions between actuator and robotic joint. The prototype was used next to investigate achievable actuator performance in force-feedback control with a slave. Results are presented, which show good performance and contact stability in a 4 channel control scheme. The actuator has low movement resistance in free motion and can reflect high torques during hard contact situations with a slave.

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Techniques are provided for controlling a human-exoskeleton system including an ankle-foot orthosis by receiving system parameters for the human-exoskeleton system, receiving generalized coordinates such as an orientation of the foot, and determining a joint torque for controlling the ankle-foot orthosis to compensate for one or more components of forces acting on the foot. Forces selected for compensation include gravitational forces as well as external forces such as ground reaction forces. Techniques are provided for determining an ankle joint torque for partial or complete compensation of forces acting on the foot about an axis of rotation. The provided techniques mitigate the amount of interference between voluntary control and assist control, thereby allowing humans to quickly humans adapt to an exoskeleton system.

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A lower extremity exoskeleton, configurable to be coupled to a person, comprises two leg supports configurable to be coupled to the person’s lower limbs and configured to rest on the ground during their stance phases. Each leg support comprises a thigh link, a shank link, and two knee joints. Each knee joint is configured to allow flexion and extension between the respective shank link and the respective thigh link. The lower extremity exoskeleton also comprises an exoskeleton trunk configurable to be coupled to the person’s upper body. The exoskeleton trunk is rotatably connectable to the thigh links of the leg supports allowing for the flexion and extension between the leg supports and the exoskeleton trunk. In this exemplary embodiment, the energy required for flexion and extension movement between the shank link and the respective thigh link of a leg support over a cyclic knee motion is provided by the person.

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[Problem to be solved] The problem to be solved by the present invention is to reduce the load applied to the wearer by correcting a parameter in correspondence with detectivity of biosignals. [Means to solve problem] The calibration controlling part 162 of the movement assisting apparatus 10 enables the power amplifying part 158 to apply a driving force of the driving source 140 as a load (input torque) from the load generating part 164 to the wearer 12 when the wearer 12 wears the movement assisting wearing device. Then, the wearer 12 applied with the driving force of the driving source 140 generates power from the skeletal muscles by performing a predetermined calibration operation. Accordingly, the physical phenomenon detecting part 142 detects joint angle along with the calibration operation, and the biosignal detecting part 144 detects myoelectric signals. In the parameter correction part 156, a parameter K is corrected based on the difference between the load (input torque) and the driving force (muscular strength) being calculated by the difference deriving part 154 with respect to the phase identified by the phase identifying part 152.

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