Patent Grant
10278883
The present concepts are generally directed to methods and systems for developing motion in humans. More particularly, aspects of the present disclosure are directed to systems, methods, and devices for developing motion by passively and/or actively adding assistive energy or resistive energy to one or more movements, and for providing cues for the movements, as appropriate, in developmentally-delayed and/or impaired toddlers.
Newly walking toddlers face difficult challenges in learning to walk. Such challenges result from the high number of degrees-of-freedom of individual body segment rotations and the inherent variability of body motion during bipedal gait in a gravitational field.
In learning to walk, toddlers may take up to 9000 steps per day. For the average toddler, this is equivalent to traversing the length of more than 20 football fields. During these first steps, and throughout the learning process, newly walking toddlers may be assisted in their exploratory behavior by adults who stabilize their body motion by holding one or both hands, or supporting the toddler's trunk at the hips. Adults assisting toddlers learning to walk provide ever-changing postural support that provides the toddlers the opportunity to safely explore the forces acting on their bodies.
A fundamental challenge in learning to walk is that stepping attempts result in simultaneous body motion in two planes, anterior-posterior and medial-lateral. However, with an abundance of body degrees-of-freedom (DOF) to control, toddlers appear to be able to learn to control body motion in only one plane at a time. As most toddlers learn to walk, the toddlers learn to reduce variability in one plane of motion while relaxing motion variability in another other. However, there are limits to the toddlers' abilities to use their muscles to control motion variability. Therefore, learning may be a continuously modulated process, rather than a fixed or absolute freezing in one plane and relaxation in the other.
Adding to the complexity and challenges in learning to walk for some toddlers can be developmental delays caused by injury (e.g., brain injury or other bodily injury). Premature birth remains a major public health problem despite recent advances. By way of example, in 2008 alone, 1.5% of the more than 4.25 million births (i.e., more than 63,000 infants) were born at a very low birth weight (VLBW) (≤1500 g). Of the 90% of surviving VLBW infants, 25-50% experienced a brain injury that accounts for delays in locomotive development. The long-term consequences of early brain injury (e.g., in children born prematurely) constitute a major health problem and a significant emotional and financial burden for families and society.
Therefore, a need exists for developing locomotive motion in developmentally-delayed toddlers to relieve the physical, emotional and financial burdens such development delay causes.
The present concepts are directed to methods, systems, and devices configured to promote locomotive motion to overcome developmental delays and/or regression in bodily control caused by injuries (e.g., developmental delays caused by premature birth and regression in bodily control caused by strokes and/or spinal cord injuries).
In at least some aspects of the present concepts, a multi-robot cyber-physical system is disclosed for assisting developmentally delayed toddlers in learning to walk. The modular system is a tight conjoining of and coordination between computational and physical resources by multiple robotic devices (or modules) that each address a subtask of motion. The modular system help toddlers lacking in mobility to learn or regain abilities related to motion (e.g., walking).
In at least some aspects of the present concepts, a method of enabling rehabilitation of bodily control of a user comprises the acts of integrating the user within a multi-module robotic system comprising a plurality of interrelated modules. In some aspects, this multi-module robotic system comprises at least one of a flexible exosuit, a support module, and a mobile base. The flexible exosuit is worn on the user and is configured to modify motion of the user at one or more joint- and/or limb-specific locations. The support module is configured to dynamically influence the center-of-mass (COM) of the user according to one or more influences to one or more body segments and/or the entire body. The mobile base provides a structural support for one or more of the flexible exosuit, the support module, and the user. The method further includes applying one or more forces, cues, or a combination thereof on the user, based on one or more subtask-specific functions of the modules, to cause a developing of one or more subtasks of the bodily control. The method further includes managing control of one or more remaining subtasks of the bodily control by the modules in place of, at least in part, the user, while applying the one or more forces, cues, or a combination thereof in a coordinated matter.
In at least some other aspects of the present concepts, disclosed is a modular robotic system configured to therapeutically assist a mobility-challenged user. The system includes a flexible exosuit configured to be worn on the user and to apply forces, cues, or a combination thereof to provide assistance to gait. The system further includes a support module configured to modulate a center-of-mass (COM), one or more positions of one or more body segments, or a combination thereof of the user with respect to an anterior-posterior direction, a medial-lateral direction, or a combination thereof. The system further includes a mobile base comprising a structural support for one or more elements of the flexible exosuit, one or more elements of the support module, and the user. The system also includes a controller configured to, from a predetermined plurality of different walking parameters, selectively vary one or more of the plurality of walking parameters through control inputs to one or more of the flexible exosuit, the support module, or the mobile base, while maintaining remaining ones of the plurality of the walking parameters, to assist the user to learn bodily control with respect to the plurality of walking parameters.
In at least some other aspects of the present concepts, a method of using a modular robotic system to enable rehabilitation of a user with respect to stance and/or mobility comprises the acts of equipping the user with the modular robotic system. The modular robotic system includes at least one of a flexible exosuit, a support module, a mobile base, or combination thereof. The modular robotic system being configured to apply forces, cues, or a combination thereof to the user to assist at least one of limb movement and balance. The support module being configured to dynamically influence a position of the center-of-mass (COM) of the user and/or one or more positions of one or more body segments and/or limbs of the user. The mobile base providing a structural support connected to one or more of the flexible exosuit, the support module, and the user. The method further includes developing a first subset of parameters with respect to stance and/or mobility of the user based on one or more operations of the modular robotic system on the user. Further, the method includes determining whether the first subset of parameters of the stance and/or mobility satisfies a first rehabilitative progression threshold. The method further includes modifying the modular robotic system at or following satisfaction of the first rehabilitative progression threshold for the first subset of parameters of the stance and/or mobility by removing a component of the modular robotic system, the component comprising the flexible exosuit or the support module. In addition, the method includes developing a second subset of parameters of the stance and/or mobility of the user based on one or more operations of the modified modular robotic system.
In at least some other aspects of the present concepts, a method of providing feedback to a user of a therapeutic multi-module robotic system comprises the acts of integrating the user within a multi-module robotic system. In some aspects, the multi-module robotic system comprises a flexible exosuit, a support module, or a mobile base, or a combination thereof. The flexible exosuit is worn on the user and configured to modify motion of the user at one or more joint- and/or limb-specific locations. The support module is configured to influence a center-of-mass (COM), one or more body segments, or a combination thereof of the user. The mobile base provides a structural support for one or more of the flexible exosuit, the support module, and the user. The method further includes applying one or more forces, cues, or a combination thereof on the user, based on one or more subtask-specific functions of the multi-module robotic system, to cause a developing of one or more subtasks of the bodily control. The method further includes managing control of one or more remaining subtasks of the bodily control by the multi-module robotic system in place of, at least in part, the user, while applying the one or more forces, cues, or a combination thereof.
The above summary is not intended to represent each embodiment or every aspect of the present disclosure. Rather, the foregoing summary merely provides an exemplification of some of the novel aspects and features presented herein. The above features and advantages, and other features and advantages of the present disclosure, will be readily apparent from the following detailed description of exemplary embodiments and modes for carrying out the present invention when taken in connection with the accompanying drawings and the appended claims.
While the disclosed aspects are susceptible to various modifications and alternative forms, specific embodiments have been shown by way of example in the drawings and will be described in detail herein. It should be understood, however, that the disclosure is not intended to be limited to the particular forms disclosed. Rather, the invention is to cover all modifications, equivalents, and alternatives falling within the spirit and scope of the disclosure and the appended claims, without limitation.
Concepts disclosed herein are directed to a multi-robot (e.g., modular) cyber-physical system, also referred to as a modular system, for assisting mobility-challenged or developmentally challenged persons (e.g., developmentally delayed toddlers, persons suffering from strokes and/or spinal cord injuries undergoing rehabilitation to regain bodily control, etc.) in learning to walk or, in some instances, re-learning to walk. The modular system is a tight conjoining of and coordination between computational and physical resources. The modular system includes multiple robotic devices (or modules) that each address a subtask of motion (e.g., balance, forward propulsion, etc. with respect to walking) As discussed in detail below, disclosed configurations of the modular system help persons lacking in mobility to learn or regain abilities related to motion (e.g., walking) The modular system provides opportunities for a user to explore the body's stability and instability under controlled and safe conditions to explore how the body is used during locomotion (e.g., walking). In part to solve the above-discussed issues for developmentally delayed toddlers, the present disclosure introduces a modular system for assisting a user (e.g., a toddler) in learning to control his or her body to promote and/or develop the ability to walk, preferably with less and less intervention by the modular system over time. The modular system includes a plurality of modules that interoperate both physically and computationally with respect to control of each module to assist a person in exploring how the body is used during locomotion, such as in the context of training and/or re-training a user how to walk, which encompasses the coordination, the stabilization, and the propulsion required to be able to walk. Although a focus in the following disclosure is on promoting and assisting a toddler with walking, the modular system is scalable for use with infants through adults. Further, although a focus of the present disclosure is on a developmental delay, the modular system is applicable to other bases for assisted development, such as a brain injury (e.g., stroke) or other bodily injury unrelated to birth or delayed maturity.
Adults assisting toddlers learning to walk provide various forms of postural support that give the toddlers the opportunity to safely explore the forces acting on their bodies. According to this approach, the modular system provides an explorative safe space in which toddlers can learn and practice to walk. Through a gradual release of support, the modular system provides a toddler with learning opportunities in a manner similar to how the toddler would receive support from adult caregivers, and encourages the toddler to harness the natural passive dynamics of walking (e.g., stance inverted pendulum and swing pendulum). Simultaneously, the modular system provides quantitative longitudinal data on the development of the toddler that can provide guidance on the development of walking.
The modular system includes multiple robotic systems (or modules), with each specific module tailored to address one or more specific subtasks of bodily control relating to stance and/or movement (e.g., walking) Such subtasks include functions and/or acts performed by a user that, in combination, result in the task of walking and/or the ability to be able to walk (e.g., standing upright, under control). The subtasks can pertain to one or more of propulsion, coordination, and stabilization. By way of example, and without limitation, subtasks of propulsion for walking include movement and/or control of the body, and/or elements thereof, that relate to propelling and stopping the body, such as plantar flexion and dorsiflexion moments about the ankle, hip extension and hip flexion moments about the hip, the use of these moments to move the limbs against gravity, harnessing the passive dynamics of gait for more efficient walking, movements of the upper extremities that create complimentary inertia moments for the lower extremities, and the control over the center of mass (COM) during the standing to walking and walking to standing transitions.
Further, by way example, and without limitation, subtasks of coordination include timing of gait events, activating correct muscle groups for specific movements, accounting for the forces and moments that the motion of one body segment causes on other segments, and synchronizing the timing of the loading and unloading of weight to the movements of extremities.
Further, by way of example, and without limitation, subtasks of stabilization include stabilizing the body, and/or elements thereof, about one or more bodily planes, such as controlling medial-lateral stability and posterior-anterior stability and range of sway/oscillation in each plane, and controlling the COM during the standing to walking and walking to standing transitions. For limbs, stabilization subtasks include co-contraction of muscles to modulate joint stiffness.
The modular system leverages a division of labor for the learning of, for example, two tasks: (1) guiding the behavior of the body (e.g., legs) in a gravitational field to harness the mechanical properties of the body (e.g., legs as pendula during walking), and (2) redirecting the body's center of mass (COM) so that the COM moves forward while maintaining medial-lateral and anterior-posterior stability. Each module can interoperate in close collaboration with the other modules via a high-level, shared control system that ensures that the assistance from each module is coordinated such as to maximize the benefit to the user. Additionally, each module can operate independent of the other modules depending on the desired assistance and level of control.
According to the above principles, the modular system can be used to supplement and/or inform clinical therapy, and the modular nature of the system means that at any time, a human (such as a physical therapist or a parent) may substitute for one or more modules of the modular system to provide therapeutic interventions, while the modules continue to perform specific module-based tasks (e.g., gait assistance, sensing, etc.). Moreover, specific modules of the system are able to mimic specific functions of what a human (such as a physical therapist or a parent) would do in helping the user to learn to walk. The use of the modular system allows for therapeutic interventions to be provided with less effort and in a more controlled manner, as compared to human intervention, both within a clinical and a home environment. The use of the modular system can also allow therapeutic interventions typically available only in clinical settings to be continued in a home environment. Further, the quantitative data (e.g., information) gathered by the modular system not only aids control, but also provides a log of information that can be used to assess performance during a therapeutic session and track the progress of the user across various timescales to compare performance over time and inform further decisions regarding therapy or rehabilitation.
Adverting to
The modular system 100a further includes a soft, flexible exosuit 107 worn by the toddler 103. The flexible exosuit 107 includes embedded actuation and sensing functionality that can monitor and assist movement of the toddler 103. By way of example, and as described in detail below, such assistance includes forces promoting stance push off and swing flexion with respect to the legs of the toddler 103. The embedded actuation and sensing functionality also allows the flexible exosuit 107 to provide information for the development of timing of body movements, and to provide resistive or antagonistic moments for further development of stabilization and propulsion. The flexible exosuit may comprise, for example, the flexible exosuit disclosed in PCT/US2013/060225, PCT/US2014/040340, and PCT/US2014/068462, which are each incorporated by reference herein in its entirety.
The modular system 100a further includes a mobile base 109 that carries the components of the modular system 100a so that the user (e.g., toddler 103) does not have to carry the additional weight of the modular system 100a. The mobile base 109 carries the top-level controller for the modular system 100a. According to some embodiments, the mobile base 109 also carries the control systems for each separate module (e.g., support module 101a, flexible exosuit 107, and mobile base 109); however, in alternative embodiments, each module can separately carry the respective controller. The mobile base 109 can include further elements, such as batteries to power the system, one or more power sources for the flexible exosuit 107, such as a pressure source for pneumatic actuators or an electrical power source (AC or DC) for electro-mechanical actuators, in addition to one or more sensors, such as proximity sensors, motion sensors, etc. According to some embodiments, the mobile base 109 is configured to passively or actively move with the toddler 103 as the toddler walks forward. Accordingly, the mobile base 109 includes one or more controllers and one or more sensors (e.g., proximity sensor) that determine the location and movement of the toddler 103 so that the mobile base 109 can actively follow the toddler 103 independent of sensors associated with other modules that may be on the mobile base 109.
Although the mobile base 109 is illustrated by way of example herein as a wheeled cart, the mobile base 109 may comprise any form of mobile base including, but not limited to a rail-based, gantry-based or supported structure. In at least some aspects, the mobile base 109 can be configured to provide additional support for the toddler 103, or the potential for additional support to the toddler 103, such as in the form of a structure or members surrounding the toddler 103 that the toddler 103 may grasp for leverage and support.
According to another embodiment,
Based on the modularity, the modular systems 100a, 100b, and 201 (referred to generally as modular system 100) can direct the toddler's attention to one specific task at a time, such as stabilization or forward propulsion, while reducing the demands for other tasks, which is in accord with the natural progression of learning to walk. That is, learning to walk is simplified for the toddler because one or more modules may provide a set threshold or percentage of support (e.g., maximum support) for one task (e.g., by providing maximum medial-lateral stability) while different or the same one or more modules provide a different set threshold or percentage of support (e.g., minimal support) for another task, which allows the child to focus on the other task (e.g., learning to step for forward propulsion). Based on this specific-task focus, a toddler can develop and master a task prior to working on other tasks, rather than having to develop all tasks simultaneously. The assistance provided by the modular system can be tailored to each individual by removing one or more modules, as well as tuned by continuous, periodic, or on demand adjustments of the assistance provided by each module. The assistance provided by each module can also progress at different rates from one another, which allows for the modular system 100 to be tailored for an individual's needs.
The modular system 100 works on several timescales for the development of motion (e.g., walking) of the toddler. According to one timescale, the modular system 100 receives real-time inputs from sensors located throughout the various modules and/or sensors disposed externally thereto (as well as the modular system 100 as a whole) and controls the system to stabilize and/or propel the toddler to develop the toddler's motion. According to a second timescale, the modular system 100 stores longitudinal data regarding the toddler's development for analysis by a user (e.g., physician, clinician, technician, caregiver, parent, guardian, etc.) to monitor and adjust performance characteristics of the modular system 100 for continued progression and development of the toddler.
The choice of module(s) used is typically based on the requirements of the toddler to provide tailored assistance, as needed. According to some embodiments, maximum assistance utilizing all three modules can be provided. Alternatively, partial support utilizing only one or two of the modules can be provided. Different toddlers with different levels of debility and/or ability may use different configurations of the modular system 100. In addition, as the user improves his or her walking, modules of the modular system 100 can be individually adjusted over time to scale back assistance and match the user's developmental progress. The adjustments or tuning can be automatic or manual. Manual adjustments may be made by a user monitoring the progress, such as a physician, clinician, technician, parent, or guardian. Automatic adjustments may be made by the controllers within the modular system 100. The automatic adjustments can be based on sensors within the modular system 100 monitoring in real-time, or over the course of therapeutic treatment, the state of the system 100 and determining if the behavior of the user is correct or not based on threshold parameter values that relate to normal or typical walking or subtasks of walking Such parameters are based on, for example, gait kinematics during locomotion, which include joint angle and acceleration measurements, as well as spatial-temporal measures such as step length, step width, and cadence, and are determined based on, for example, gyroscopes, inertial measurement units (IMUs), encoders, foot switches, and/or hyper-elastic soft strain sensors across joints. Based on the parameter values, the modular system 100 instructs the actuation appropriately.
By way of example, based on the information from sensors within the modular system 100, controllers within the modular system 100 respond to developmental changes in behavior of the body's COM, behaviors in one or more limbs and/or body segments, and in gait parameters by allowing greater relaxation of media-lateral and/or anterior-posterior sway, and by reducing, and eventually eliminating, forces provided by the modular system 100, such as from the flexible exosuit for hip and/or ankle torques. Moreover, based on the dynamic nature of the modular system 100, at any time a human (such as a physical therapist or a parent) may substitute for one or more functions of the modular system 100 to provide therapeutic interventions. The modules of the modular system 100 can dynamically respond to the interventions by continuing to provide and modify therapeutic intervention with respect to the other functions.
Alternatively, or in addition, as the user develops one or more subtasks of walking, the user may no longer need the assistance provided by one or more modules. For example, the user may have developed medial-lateral and anterior-posterior stability control such that assistance provided by the support module is no longer required. The user may be able to walk independently from the support module while wearing the soft exosuit for support and propulsion, as needed. Based on the user's development, one or more modules are removed from the modular system 100.
As the toddler progresses in the development of walking, the modular system 300 can be tailored to match the toddler's progression and promote further progression.
As shown in
Modification of the modular system 300 is based on progression of the user in developing the ability to walk. Such progression is evidenced based on data collected during the course of therapeutic assistance provided by the modular system 300 indicating improvement in one or more subtasks of walking. The data can be collected with respect to one or more parameters that quantify the subtasks of walking, or walking in general. By way of example, and without limitation, the one or more parameters include cadence (e.g., steps per minute), stride time, stride length, step width, duration of double support (e.g., both feet contacting ground), joint angles and accelerations, the overall forward walking speed achieved by the toddler, the ratio of weight the user is placing on the support module vs. supporting themselves, the frequency of the toddler's coordination “errors” detected by the system, etc.
By way of example, after several successive assisted steps in which propulsive force is added at heel strike, the pattern of accelerations and decelerations within the footpath boundaries may become increasingly stable. Further, gait parameters may exhibit greater stride length and narrower step width, which indicate more controlled, mature walking. These changes in the walking behavior of the user evidence the user's development and can result in the tuning and/or removal of one or more modules of the modular system 300.
As discussed above, the mobile base of a modular system 100 is configured to be passive, such that the mobile base follows the toddler under power provided by the toddler (e.g., pulling the mobile base). Alternatively, the mobile base is configured to actively follow the toddler under self-powered assistance. In doing so, the mobile base is configured to dynamically estimate the relative position, velocity, and acceleration between the mobile cart and the toddler. In at least some other aspects of the present concepts, a controller of the mobile base further utilizes the sensor(s) of the modular system 100 to ascertain predictive signals corresponding to movement (i.e., sensing the toddler's intent to actively control one or more motion systems (e.g., sensing of muscle activation, etc.)) to follow the toddler. In the case of the modular system 100a being actively powered to follow the toddler 103,
Operation of the motor 401 drives the drive wheels 405 to move the mobile base 109 and the modular system 101a forward to actively and dynamically follow the movement of the toddler 103. In at least some aspects, the mobile base 109 includes one or more sensors, such as a proximity sensor and a motion sensor, to determine the position and motion of the toddler. Alternatively, information from one or more elements located throughout the modular system 100a, or external to the modular system, is fed to a controller of the mobile base 109 to dynamically follow the toddler.
A focus for control of the modular system 100a and, indeed, a modular system 100 in general, is the toddler's COM. The COM can be considered a compression of the many biomechanical degrees of freedom of the toddler's body into a single lower dimensional form. As such, the COM of the toddler's body is information available to both the child and the modular system 100 for the stabilization and coordination of body movement. By way of example, the modular system 100 can model COM behavior as the toddler learns to walk by considering each leg during a single support phase of the gait cycle as an inverted spring-pendulum system. During a double support phase, the modular system 100 models the COM behavior as a redirection of body motion as a consequence of transitions between single-support phases. Sensors within the modular system 100 detect information that is processed to determine and monitor the state of the toddler and understand if the behavior of the toddler is correct or not and instruct the actuation appropriately in a closed-loop manner.
According to a single support phase of posterior-anterior oscillations, the toddler can be considered as an inverted pendulum and during the swing phase the leg can be considered as a pendulum. The potential and kinetic energy can be monitored and used as part of the control scheme to help guide the user to a more natural human walking pattern that leverages the natural passive dynamics of the body and limb. During walking, each transition to a new stance leg requires redirection of the COM velocity from one inverted pendulum to the next. In other words, walking consists of an inverted pendulum phase for one leg, a step-to-step-transition phase, and an inverted pendulum phase for the other leg. By using sensors to monitor the movement of the body and limbs, a top-level controller of the modular system 100 interoperates with and directs controllers of one or more of the modules (e.g., flexible exosuit, support module, and mobile base) to assist in the manipulations of the COM, while promoting stabilization and support.
Within the modular system 100, a focus of specific body motion and control of self-propelled forward motion is with respect to the flexible exosuit (e.g., flexible exosuit 107). As discussed above, the flexible exosuit is a soft, lightweight, flexible, and wearable garment worn by the toddler, which serves as an interface for the modular system 100 to apply forces and/or torques to the toddler's body. Application of these forces and/or torques can be at (or across) various different joints of the toddler, such as at the hip, the knee, the ankle, etc. At each one of the locations, various forces and/or torques can be applied for different orientations/functions (e.g., flexion, extension, abduction, adduction, etc. with respect to the hip).
The benefits of the forces and/or torques applied by the flexible exosuit are multifold. In at least some aspects, the forces and/or torques applied by the flexible exosuit are used to provide an instructive and/or coordinating cue for the toddler to move a limb. In at least some aspects, the forces and/or torques applied by the flexible exosuit are used to provide assistance to movement if the toddler lacks the strength, or enough strength, to perform the movement without assistance. In at least some aspects, the forces applied by the flexible exosuit are used to modulate joint stiffness to help the toddler achieve correct limb behavior.
Specific applications of forces and/or torques by the flexible exosuit can affect limb behavior in different ways. According to one application, the flexible exosuit can create a moment about one or more joints by applying a force across a joint between a limb segment on one side of the joint (e.g., a distal segment) and a limb segment on another side of the joint (e.g., a proximal segment). The moments assist a motion when the moments compliment the natural moments created by the user for the motion. The moments can also resist or modulate joint stiffness when the moments oppose the natural moments created by the user. With respect to antagonistic moments, the flexible exosuit is configured to control the joint stiffness through co-contraction of one or more actuation units within the flexible exosuit that create antagonistic moments that resist natural moments created by the user. The flexible exosuit selectively achieves these various results by transferring forces and/or torques along load paths emulating real-life arrangements of muscles, tendons, and ligaments.
According to one embodiment, the flexible exosuit is worn on the toddler's legs like clothing. In some aspects, the flexible exosuit can be anchored at the hips and/or waist of the toddler, and extend to above, at, or below the toddler's knees. Alternatively, the flexible exosuit can include a lower leg and/or ankle component, which extends past the knee and interfaces with the lower calf and/or ankle.
When actuated, the flexible exosuit can provide forces (e.g., assistive and/or resistive) to help the toddler learn, for example, that a leg can either serve to propel the COM forward like an inverted pendulum, or swing the leg forward like a pendulum in anticipation of redirecting the COM with another ground contact.
In addition to the above-described actuation, the flexible exosuit acts as a sensory platform. That is, the flexible exosuit can have integrated sensing to monitor toddler motion with respect to, for example, joint angles, gait events, etc. The information collected by the sensors about the flexible exosuit can be used both for control and for monitoring performance (e.g., longitudinal data with respect to development and growth), in addition to detecting and avoiding abnormal joint motions that could cause sprain or other injury.
By way of example, the flexible exosuit can contain integrated sensing that provides information, such as joint angle measurements, that can be inputted into the top-level controller of the modular system for the control of the system, in addition to being a source of quantitative longitudinal data that can be provided to a user (e.g., physician, clinician, technician, etc.) to evaluate the toddler's walking.
Like the flexible exosuit itself, the sensor(s) can comprise flexible or unobtrusive sensors, such as elastomer-based hyper-elastic strain sensors. By way example and without limitation, some exemplary sensors are disclosed in publications WO 2013/044226 A2, WO 2012/103073 A2, WO 2012/050938 A2, and U.S. Pat. No. 8,316,719 B2, and applications PCT/US2014/068462 and PCT/US13/66034, each of which is hereby incorporated by reference in its entirety. For example, one or more hyper-elastic strain-sensors may comprise a stretchable silicone rubber sheet with one or more conductive-liquid-filled micro-channels provided to measure a change in electrical resistance when the sheet is stretched. In addition, or alternatively, the sensors can include gyroscopes, which can detect certain peaks that correspond to specific gait events, foot switches which detect heel strike, toe-off, or other foot contact events, encoders or potentiometers on the joints that give joint angle measurements, and/or inertial measurement units (IMUs) that provide absolute coordinate measurements. Information provided by strain sensors and IMUs, such as strain and inertial data, can be used, alone or in combination, to further refine the estimation of joint kinematics during locomotion.
Actuation within the flexible exosuit can be achieved according to one or more different techniques. According to a first technique, the flexible exosuit includes soft actuators that utilize soft elastomeric synthetic muscles and sensors. By way example and without limitation, some exemplary soft actuators are disclosed in publication WO 2013/033669 A2, which is hereby incorporated by reference in its entirety. According to some embodiments, the soft actuators include miniaturized pneumatic muscles, artificial tendons and/or ligaments, and hyper-elastic strain sensors in successive layers. Multiple pneumatic muscles within a single soft actuator allow the actuator to behave according to specific contractions, such as simultaneous contraction, sequential contraction, or bending. The artificial tendons and ligaments can constrain motion of the soft actuators according to specific directions that can be aligned to biological muscles and tendons to create the same muscle contraction effects. The soft actuators can be lightweight, flexible, and impact-resistant so as to not weigh down or impede the natural motion of a toddler. Such properties make the soft actuators particularly applicable to wearable application for toddlers.
The soft actuators can be configured and located about the flexible exosuit to apply the above-described forces and/or pressures. According to some embodiments, the soft actuators can be shaped to conform to one or more body segments, such as the leg, the hip, the thigh, the arm, the elbow, the calf, the ankle, etc. According to some embodiments, a combination of modular soft actuators can be configured and located about the user to form the flexible exosuit. Such soft actuators may be bending soft actuators, such as those placed at a joint and configured to bend according to the natural movement of the joint. Such soft actuators may alternatively, or in addition, be linear soft actuators that apply forces at distal and/or proximal ends of limbs.
The soft actuators can be actuated by a fluid, such as by increases/decreases in the pressure of a gas or a liquid. The pressure source that drives the fluid is advantageously located off of the flexible exosuit, such as on the mobile base, and may comprise, for example, an air pump or a compressed air tank. Alternatively, the pressure source that drives the actuators of the flexible exosuit can be integrated on the flexible exosuit, or on a standalone component worn by the user or pulled alongside the toddler (e.g., pressurized tank). In applications of toddlers, the pressure source is located off board on the mobile base to minimize the added weight on the toddler.
One possible method of actuation is to place bending soft actuators on the joint to induce flexion when actuated. An alternative to bending actuators are linear actuators, such as pneumatic artificial muscles (PAMs), which contract/shorten in length when pressurized.
With respect to PAMs, as an example, PAMs allow for the flexible exosuit to create moments about selected joints. These moments can be used to create perturbations and/or impulses that act as cues for the toddler as they progress through the gait cycle. The moments can also provide power assistance for developmentally-delayed toddlers who lack the motor strength for normal walking. If the PAMs are placed in an antagonistic configuration, the moments generated by the flexible exosuit can also modulate joint stiffness through co-contraction.
Upon actuation, a fluid causes the inflatable material to inflate. Inflation of the inflatable material causes the inextensible sheet 501 to contract lengthwise as it expands radially at the center, as shown in
In a non-actuated state, the PAM 500 is in a straight configuration, as illustrated in
The forces generated by the PAM 500 are transferred through the fabric of the flexible exosuit 601 to the toddler 603 according to anchor points within the fabric and the configuration of the fabric. In
By way of example, PAMs 705a-705d provide hip flexion assistance and/or cues about the hips, PAMs 705e-705g provide hip extension assistance and/or cues about the hips, PAMs 705h and 705i provide plantar flexion assistance and/or cues about the ankles, and PAMs 705j and 705k provide dorsiflexion assistance and/or cues about the ankles. The PAMs 705h-705j connect at one end to anchor points 707 on one or more straps 703 and at the opposite end to anchor point 707s at the foot of the toddler, such as on a shoe, a sock, or a foot plate. According to the illustrated and described arrangement, a variety of assistance and cues can be applied to the toddler during the development of walking.
Rather than applying forces and/or cues with PAMs, according to some embodiments of the present concepts, assistance and/or cues can be provided by cables, such as Bowden cables. Based on a force being transmitted from an off-board power source, such as a drive motor, to an attachment point on the flexible suit, a flexible exosuit may be configured differently than the flexible exosuit of
The straps 801 are connected to Bowden cable 803 (or any other type of force transmission element). The Bowden cable transmits a force generated by an off board power source (e.g., drive motor, not shown) to the flexible exosuit. The drive motor can provide a third of the biological torque required for movement. For a two-year old toddler, exemplary torque may be 2.3 Newton-meters (Nm) for 100 rotations-per-minute. By way of example, a drive motor can be a Maxon EC60 motor, overdriven at 20 amperes (A) with a built-in 1024 CPT encoder and an integrated ESCON controller from Maxon. The Bowden cable 803 includes a cable 805 that is surrounded along at least part of the length of the Bowden cable 803 by a sheath 807. The sheath 807 is attached to one or more of the straps 801 to provide support for and dissipate transmission of the forces on the toddler's body. The cable 805 attaches to a foot attachment 809, such as a shoe, a sock, or a footplate. The foot attachment 809 may include one or more sensors 811, such as a footswitch, an IMU, and/or a gyroscope to detect contact between the foot and the ground or other obstacle.
According to the flexible exosuit 800 illustrated in
In accordance with additional concepts of the present disclosure,
The flexible exosuit power unit 903 drives a force transmission element 905. An exemplary force transmission element can be a Bowden cable, which includes a cable within an outer sheath. Within the flexible exosuit power unit 903, a pulley (not shown) can be mounted on the shaft of a motor (not shown). When the motor turns in one direction, the motor applies a force through the force transmission element 905 (e.g., the Bowden cable) and to the flexible exosuit 901. The motor of the flexible exosuit power unit 903 can also rotate in the other direction to feed out slack. According to one embodiment, a slip clutch (not shown) can be between the pulley and motor to provide a safety limit to the force transmission element 905.
In the case of actuating the hip joint, the force transmission element 905 connects to a hip drive unit 907. The hip drive unit 907 converts the linear force applied by the force transmission element 905 to a rotational toque. The rotational torque is applied to the user through a multi-contact, flexible shaft 909 connected to the hip drive unit 901. According to one arrangement, the rotational torque causes hip flexion and/or hip flexion depending on the capabilities and characteristics of the driving arrangement of the force transmission element 905. The linear force of the force transmission element 905 is converted to a rotational torque to avoid a shearing force on the user's skin.
The flexible shaft 909 has a branched multi-contact structure for even and comfortable force distribution along the thigh, rather than a point application of force. The flexible shaft 909 is embedded within a thigh attachment 911. The thigh attachment can be a flexible piece of fabric that further spreads and dissipates the applied force from the flexible shaft 909. The rotational torque of the hip drive unit 907 applied through the flexible shaft 909 and the thigh attachment 911 causes a hip flexion moment at the user's hip, which can provide assistance and/or a cue in developing the user's walking. Alternatively, or in addition, the hip flexion moment can provide resistance, such as in an antagonistic arrangement, during hip extension to modulate joint stiffness. To passively accommodate abduction and adduction motion of the hip, the proximal section of the shaft can have a thin but wide section (not shown) which can easily bend laterally but remain rigid in the flexion/extension direction.
The drive arrangement 900 of the flexible exosuit 901 can be completely transparent to the user when needed to avoid impeding the natural motion of the user.
To provide assistance or a cue for the toddler,
Adverting to
The pulley 1101 includes a protruding peg 1109 that engages the thigh shaft 1103 if the pulley 1101 rotates far enough counterclockwise. The peg 1109 provides a predictable engagement between the movement and engagement of the pulley 1101 with the shaft 1103. Within the pulley 1101 is a torsional spring 1111. When the force transmission element 1203 (
The pulley 1101 further includes a slot 1113 and a recess 1115 that accept an end of a force transmission element (e.g., force transmission element 1203). Specifically in the example of a Bowden cable, the slot 1113 accepts the cable, and the recess 1115 accepts a cable stop to lock the Bowden cable within the pulley 1101.
Adverting to
According to some embodiments, the peg 1109 can include an integrated sensor (not shown). The integrated sensor can detect the force applied to the shaft 1103. Alternatively, or in addition, the cable 1205 can be routed around an additional pulley 1207 (
In addition to one or more sensory fail safes, the arrangement of the hip drive unit 1100 in combination with the force transmission element 1203 can include one or more mechanical fail safes to prevent injury to the user. By way of example, and without limitation, the connection between the cable 1205 and the recess 1115 can include a breakpoint, the end 1201 of the cable 1205 can include a breakpoint, the post 1105 can include a breakpoint, and the shaft 1103 can include a breakpoint at one or more positions along its length. The described breakpoints are configured to sustain normal loads transmitted to the user through the force transmission element 1203 and the hip drive unit and break to stop transmitting the loads, if the loads exceed a threshold (e.g., harmful) level.
In the arrangement of the hip drive unit 1100, the center of rotation of the thigh shaft 1103 may not be co-located with the center of rotation of the physical hip joint of the toddler, leading to an offset link/compression effect during movement. To compensate for the offset link/compression effect, the thigh shaft 1103 can include a prismatic joint.
As illustrated, the center of rotation 1303 can be above the center of rotation 1309 of the toddler's hip, which causes a compressive force about the center of rotation 1309 of the toddler's hip during actuation of the shaft 1301 and/or movement of the leg. That is, the distance D1 between the center of rotation 1303 and the termination point 1307 with the leg straight (
To accommodate this, the prismatic joint 1401 of
Although the end 1301a of the shaft 1301 is illustrated as being within the pulley 1403 in a non-actuated state, the end 1301a may alternatively extend beyond the opening 1405b in the non-actuated state. Additionally, the end 1301a may include a stop (not shown) that prevents the end 1301a from passing into the pulley 1403 or out of the opening 1405a of the pulley.
In a non-actuated state, the shaft 1511 extends a length L4 into the shaft 1501 through the opening 1509. In an actuated state, the shaft 1511 extends a length L5 into the shaft 1501, in which L3 is greater than L2. The shaft 1511 extending farther into the shaft 1501 in an actuated state reduces or eliminates the compressive forces about the center of rotation 1505 on the hip of the toddler 1507.
Throughout the flexible exosuit are sensors to determine the positions and actuation statuses of the actuator and flexible exosuit. As previously noted, one or more of the sensors can advantageously be hyper-elastic strain sensors. Such hyper-elastic strain sensors can be integrated with, for example, the PAMs discussed above. In particular,
Adverting to
As discussed above, the flexible exosuit is one of several components of the modular system that acts to develop propulsion, coordination, and stabilization of a toddler. The focus of the flexible exosuit is the application of forces and/or torques at various different joints and/or limbs of the toddler to provide assistance and/or cues for developing walking in a toddler. To mimic the assistive forces provided by an adult caregiver, the modular system may include a support module. That is, as discussed above, the support module is inspired in part by supported walking provided by adults to the exploratory walking of young children. The support module mimics adult assistance by modulating the toddler's center of mass (COM), as required, to facilitate walking, similar to the manner in which adults support exploratory walking of young children.
The support module is configured to apply three-dimensional forces and/or torques to the toddler to perform several functions, including stabilizing medial-lateral and/or anterior-posterior sway, purposely de-stabilizing the toddler to initiate the standing to walking transition, and providing body weight support, if needed. The requirements of the overall medial-lateral and anterior-posterior control will provide a desired three-dimensional force and moment to be applied to the child. The support module can further provide body weight support, if needed. The support module relies on integrated sensing to detect the toddler's COM position, status, balance, and intent, and prevents the toddler from injury by detecting a fall or imminent fall and limiting applied motions/forces.
With respect to the support module being in the form of an arm (such as support module 101a with arm 105), the arm is an actuated arm with a body attachment on the end that grasps the toddler's torso from behind. The arm is designed to be behind the toddler for ease of engaging/disengaging the toddler from the modular system, and also so that the toddler has a clear and unobstructed view of the path forward. The body attachment acts as the interface between the toddler and the support module, securely but comfortably holding the toddler and allowing the application of forces/torques by the support module onto the toddler. The body attachment is designed to be easy to don and doff, like a vest, as well as simple to adjust to fit tightly to the wearer.
The body attachment 1801 further includes an adjustable mechanism 1805 for easily placing the body attachment 1801 on the toddler, closing the body attachment 1801 until it firmly grabs the toddler with the appropriate force, then locking the body attachment 1801. According to some embodiments, the mechanism can be a rack and pinion gear to keep the body attachment 1801 centered. The mechanism 1805 can be manually set and locked by a user (e.g., physician, clinician, technician, parents, guardian, etc.), or the mechanism 1805 can be automated. According to some embodiments, the mechanism 1805 can be manually set according to a manual knob (not shown). Alternatively, or additionally, according to some embodiments, the body attachment 1801 can include an integrated load cell 1807 for detecting grasping force. The hands 1803 close until the load cell 1807 detects a threshold level of grip, which automatically stops and maintains the grasping force. According to some embodiments (not depicted), the adjustment mechanism can consist of more flexible and lower profile structures (as compared to a rack and pinion embodiment), such as laces, ratchets, textile straps, etc., to make the body attachment 1801 as wearable like a garment as possible.
Once the toddler is “wearing” the body attachment 1801 the body attachment 1801 is connected to the rest of the modular system (e.g., the support module and mobile base). The connection is secure during normal operation, but also allows for safe and easy disconnecting if the toddler needs to be quickly removed from the modular system. To this end, the body attachment 1801 has a connector 1815 on the back, with a complementary connector (e.g., connector 2115 of
With respect to the flexible joint specifically, the flexible joint has flexibility to allow some freedom of motion out of plane by the toddler. In addition, the flexible joint can contain sensing for detecting the status of the toddler's COM, balance, and intent, and preventing the toddler from injury, such as detecting falling or an imminent fall, and limiting the applied motions/forces. According to some aspects of the present concepts, the flexible joint can be the primary component of the modular system that determines the toddler's intent.
The plate 2103 is attached to one or more springs 2105. The springs 2105 provide small rotational flexibility and reduce resistance to torso motion. The flexible joint 2101 further includes a ball joint 2107 that provides the center of rotation mechanically limiting flexibility in rotation only.
The flexible joint 2101 further includes a sensor 2109 between two horizontal plates 2111. The sensor 2109 is configured to detect all directional (6 DOF) loads from the toddler that are transmitted through the flexible joint 2101. The sensor 2109 can be an ATI Mini 40 (US-10-20E) sensor that can detect 40 Newtons (N) of horizontal force and 133 N of vertical force. The sensor 2109 is installed so that its vertical (Z) axis aligns with the weight force of the toddler. At the end of the flexible joint 2101 is a base 2113 for connecting the flexible joint 2101 to a mobile base.
Adverting to
The bases 2111 and 2155 of the flexible joints 2101 and 2151 can attach to or constitute actuators that attach the arms to a mobile base and provide movement of the arm relative to the mobile base. According to one embodiment, the bases 2111 and 2155 can be an XY table actuating the arm in the horizontal plane, with a passive mechanism for vertical motion and body weight support. By way of example, the XY table can be a Velmex XY table, model number MAXY4009W1-S4, manufactured by Velmex, Inc., of Bloomfield, N.Y., with a workable envelope of 18.5 inches in both directions and a capacity of 25 pounds of load. According to another embodiment, the bases 2111 and 2155 can be an XYZ table (or equivalent 3 DOF actuator) that actively actuates in the vertical degree of freedom.
Adverting to
The above-described elements of the support module describe a support module that provides active support in the form of medial-lateral and/or anterior-posterior sway assistance and/or cues for developing toddlers through an arm. In addition, or in the alternative, to the above-discussed support structures, the modular system can include an active tether/scaffold-based support module, as discussed above with respect to
Tension in the individual tethers generates a desired force-moment at the pelvis. Each tether will have a cable in series with a spring, with the ability to modulate the tension within the cable. Modulation can be achieved by a DC motor to provide three-dimensional support to the pelvis both in position and orientation. The configuration of the tether/scaffold-based support module provides full or partial gravity balancing of the trunk as a toddler ambulates on the ground. The active modulation of tension in tethers further provides medial-lateral and/or anterior-posterior support to the toddler during motion. Although discussed above with respect to an active tether/scaffold-based support module being attached to the mobile base, according to some embodiments, the active tether/scaffold-based support module can be independent from (separate from) the mobile base. By way of example, the active tether/scaffold-based support module can be a separate, movable structure, such as a self-supported structure on the ground, suspended from the ceiling, suspended from a gantry crane, etc.
According to some aspects of the present concepts, the support module can be passive, rather than active. Such a support module can passively support the user (e.g., the COM and/or one or more limbs of the user) while the user explores the stability and instability of stance and motion. By way of example, a passive support module can passively support the user while one or more other modules (e.g., flexible exosuit, mobile base) dynamically perform one or more functions on the user to modulate the user's stance and/or movement.
According to one embodiment, a passive support module can include a passive arm. The passive arm can passively function according to one or more of the functions described herein with respect to the arm of an active support module. By way of example, a passive arm can support the full or partial weight of the user, while the flexible exosuit and the mobile base dynamically modify the user's stance and/or motion.
The structure of the passive arm can correspond substantially to the active arm disclosed herein, but may exclude the one or more controllers, one or more actuators, and/or one or more sensors of the active arm. According to some embodiments, an active arm, as disclosed herein, can be dynamically changed to an active mode and a passive mode. Whether the arm is set to an active mode or a passive mode configures the arm to actively interoperate with the other modules within the modular system (e.g., active mode), or passively interoperate (or not interoperate) with the other modules, such as being fixed according to one function.
According to some embodiments, a passive support module can include a suspension harness to catch the toddler in case of a fall. A suspension harness can be used alone or in combination with the above-described elements of the support modules. By way of example, although an arm of a support module is capable of safely supporting the full weight of the toddler, the support module can also include a suspension harness to support the entire weight or partial weight of the toddler. The suspension harness can be mounted so that it is slightly slack and does not bear any load during normal operation, and only bears load if the toddler falls, collapses, or tries to sit down.
According to some embodiments, one or more passive support modules include, by way of example, a gantry crane, a rail-based support, and a cart. Such passive support modules can be a designed to include a passive spring system to provide some support. The flexible exosuit, the mobile base, and/or an active support module can be used in combination with such a passive support module. Alternatively, or in addition, a passive support module can include upper-limb based support such as crutches/walking sticks.
As discussed above, the support structure, auxiliary components of the flexible exosuit (e.g., pump, compressor, and/or motors), and other control and power hardware are mounted on the mobile base. Placing these components on the mobile base prevents the toddler's natural motion from being hindered by the added inertia of these components. The mobile base and its components move along with the toddler as the toddler walks forward. As discussed above, the mobile base also has the potential to act as a support surface that the toddler can grasp and use as a source of tactile feedback that helps the toddler maintain a stable posture.
By way of example, in an assistive embodiment, the mobile base can have a top speed of 4 miles per hour (mph) powered by a 24 volt (V), 270 Watt (W), 4700 rotations per minute (rpm) motor. With respect to powering hip actuation, power can be provided by an EC60 flat 100 Watt motor from Maxon, operating at 48V, which has a maximum torque of 5.01 Newton meters. Normal applied torque can be 2.3 Nm, which is ⅓ of the biological hip flexion moment in a normal (e.g., 2-year-old) toddler. However, specific such values can vary depending on the user and the amount of assistance needed. In at least some aspects of the present concepts, the system is powered off a set of at least four 12V batteries, wired in series to provide the various voltages needed to power a variety of different actuators (e.g., mobile base motor runs on 24V, exosuit motors are 48V). The capacity of the batteries can also be selected to provide desired run times (e.g., 30 minutes of continuous use, 1 hour of continuous use, etc.). According to some embodiments, the controllers and sensors are on a separate power circuit to electrically isolate the user from high currents of the motor circuit, to reduce the risk of electric shock. However, the above-described specifications are exemplary and will vary depending on the size and type of the user and the type of therapy or assistance being provided to the user.
Each module of the modular system can function independently so that the support provided by the overall modular system can be scaled back. According to one embodiment, each module of the modular system can have its own controller. At the same time, the modules are capable of interoperability and integrate/coordinate with each other. To this end, the modular system includes a hierarchical control approach that includes a top-level controller that determines in real-time the dynamic reconfigurations required for the mobile base, support module, and flexible exosuit in order to perform the desired assistive functions. This top-level controller sends the appropriate commands to each module. The hierarchical system works together to behave cooperatively with the toddler, rather than forcibly overriding the toddler's natural motion. To this end, all modules of the modular system have integrated sensing for gathering information about the toddler's motion.
When all of the modules are in use, the modules function to achieve three specific goals to help toddlers with the transition from assisted to unassisted walking: coordination, propulsion, and stabilization.
With respect to coordination, a toddler or other user explores joint angle rotations and discovers how to coordinate rotations to preserve whole limb kinematics. For example, a toddler discovers how to allow a leg to behave like a mass-spring pendulum system. With respect to the goal of coordination, the support module provides partial loading and unloading with respect to gravity balancing. In combination with the flexible exosuit, the loading and unloading can be timed to coincide with actuations of the flexible exosuit, such as actuations at the hip and ankle joints. The flexible exosuit can provide hip and ankle actuations that maintain whole limb behavior.
With respect to propulsion, a toddler or other user can explore the forward propulsive behavior of the body's COM during swing phase, stance phase, and the footfall/load acceptance/COM redirection that occurs in the transition between the two phases. During this exploration, the support module can provide fine movement in conjunction with coarse movement of the mobile base and/or the toddler. The fine movement can maintain invariant position with respect to the child's assisted forward motion. The support module can further provide partial loading and unloading with respect to gravity balancing. In combination with the flexible exosuit, the loading and unloading can be timed to coincide with actuations of the flexible exosuit, such as actuations at the hip and ankle joints. The flexible exosuit can provide hip and ankle actuation that maintains whole limb behavior and remains within the stability region of the body's COM.
With respect to stabilization, the toddler can explore the medial-lateral motion and/or the forward component of anterior-posterior behavior of the body's COM during single and double support phases. During this exploration, the support module can modulate the equilibrium and tension/stiffness of the medial-lateral motion. The flexible exosuit can provide actuation, such as at the hip and ankle, and/or modulate the stiffness of the joints. The support module can further provide partial loading and unloading with respect to gravity balancing. In combination with the flexible exosuit, the loading and unloading can be timed to coincide with actuations of the flexible exosuit, such as actuations at the hip and ankle joints.
Adverting to
As the toddler 2203 begins to move according to arrow 2201a, the support module 2205 can move forward according to arrow 2201b to match the velocity of the toddler 2203. The graphs 2211a and 2211b match during the period 2213a. According to some embodiments, for safety, the mobile base accelerates slowly and then follows at a constant speed. More rapid movements can be performed by the support module.
As the modular system determines from one or more sensors that the toddler 2203 continues to move in the direction 2201a, the coarse movement control of the mobile base 2207 begins in the direction of arrow 2201c and complements the fine movement control of the support module 2205. During periods 2213b and 2213c, the combination of the graphs 2211b and 2211c matches the movement of the toddler 2203 within the graph 2211a. For a smooth transition between control of movement by the mobile base 2207 and the support module 2205, both can operate to match the movement of the toddler 2203 prior to the total control of the movement being handled by the mobile base 2207, as illustrated by the graphs 2211b and 2211c in
The same configuration may occur as above, in reverse, to stop the modular system 2200 when the toddler 2203 comes to rest. As toddler 2203 begins to slow down, fine movement control by the support module 2205 can decelerate the modular system 2200, as illustrated by period 2213e in graphs 2211a through 2211c. As the modular system determines that the toddler 2203 is further slowing down, the mobile base 2207 may begin to decelerate and complements the movement control of the support module 2205, as illustrated in period 2213f in graphs 2211a through 2211c. Once the toddler 2203 stops moving, the support module 2205 and the mobile base 2207 may continue to move to reset to a default configuration and position relative to the toddler 2203, as illustrated in period 2213g in graphs 2211a through 2211c.
Adverting to
Kinematic element 2301b represents the manual vertical movement 2303b to adjust the vertical position of a support module. According to other embodiments, the vertical movement 2303b can be automated, such as being based on a vertical load sensor within the support module.
Kinematic element 2301c represents the passive vertical movement 2303c of, for example, the connection of the arm of the support module to the mobile base, with passive vertical movement capability. Such passive vertical movement 2303c may be according to a vertical range of motion allowed in the support module for vertical variations in a toddler's posture.
Kinematic element 2301d represents the active medial-lateral movement 2303d of the arm of the support module, and kinematic element 2301e represents the active anterior-posterior movement 2303e of the arm of the support module. The active medial-lateral movement 2303d and the active anterior-posterior movement 2303e provide sway support and triggers imbalances to, for example, initiate forward motion of the toddler. By way of example and without limitation, the ranges of both movements 2303d and 2303e can be 100 millimeters (mm) at a speed of 0.5 m/s.
Kinematic element 2301f represents the passive range of motion allowed between the body attachment and the flexible joint of the arm of the support module, which allows for a limited range of motion in two or more planes.
Kinematic element 2301g represents the manual range of motion 2303g of the body attachment attached to the arm. The range of motion 2303g can provide a toddler with a limited degree of freedom at the end of the support module.
Adverting to
The top-level controller 2501 communicates with the flexible exosuit controller 2503, the support module controller 2505, and the mobile base controller 2507 based on wired or wireless two-way or one-way communication paths, represented generally by arrows 2511. According to some embodiments, the flexible exosuit controller 2503, the support module controller 2505, and the mobile base controller 2507 communicate directly with each other based on wired or wireless two-way or one-way communication paths, represented generally by arrows 2513. Further, the top-level controller 2501, the flexible exosuit controller 2503, the support module controller 2505, and the mobile base controller 2507 communicate with the sensors of the sensor groups 2509a-2509c based on wired or wireless two-way or one-way communication paths, represented generally by arrows 2515. Although illustrated as separate and distinct communication paths, one of more of the communications paths 2511-2515 can be integrated into a single communication path.
The top-level controller 2501, the flexible exosuit controller 2503, the support module controller 2505, and the mobile base controller 2507 can be hardware-based controllers and/or software-based controllers. For software-based controllers, the controllers can be one or more processors that execute specific computer-readable instructions stored on one or more transitory and/or non-transitory computer-readable storage mediums that, when executed, cause the controllers to perform one or more functions and/or cause the controllers to cause one or more elements within the modular system to perform one or more functions. The mobile base can include one or more computer-readable storage mediums that store the computer-readable instructions, such as optical discs, random access memory (RAM), read only memory (ROM), flash drives, solid state drives, magnetic storage drives, etc.
According to a software-based controller approach, and by way of example, and without limitation, a system software architecture can be divided into two main layers: System Services Layer (SSL), and Application Layer (AL). The SSL implements fundamental components that manage local resources and provides primitives to support algorithms at the AL. The SSL implements a clock-driven scheduler, handles inter-module communication, accesses sensor information, and sets configuration and actuation parameters. The AL can specify application goals using the services provided by the SSL. The clock-driven scheduling provides predictable execution of specific tasks at individual modules, allowing simplification of control of timing of sensing, processing, and actuation tasks.
According to a hardware-based controller approach, by way of example, and without limitation, hardware-based controllers can be implemented based on a PC-104 stack, which can consist of, for example, one or more processors (e.g., an Aurora Single Board Computer with 1.6 GHz processor), one or more power supplies (e.g., a Jupiter-MM-LP DC/DC power supply), and one or more input/output modules (e.g., a Diamond-MM-32DX-AT Analog I/O module). The input/output modules can have analog and/or digital inputs and outputs (e.g., 32 single-ended analog inputs, 4 analog outputs, and 24 digital inputs/outputs), and can also include automatic calibration for temperature changes.
Modeling within the control arrangement 2500 to execute the functionality of the control arrangement 2500 can be accomplished according to various methods without departing from the spirit and scope of the present concepts. According to some embodiments, and without limitation, functionality within the control arrangement 2500 can be based on Simulink® models, and the models can be run based on dedicated hardware controllers. By way of example, one or more of the controllers of the control arrangement 2500 are designed as a Simulink® model containing both standard modeling blocks as well as xPC target-specific blocks that allow input/output with supported hardware.
One or more models executed within the control arrangement 2500 can be configured external to the control arrangement 2500 (e.g., on a host computer) and subsequently transferred to one or more of the controllers within the control arrangement 2500, such as by a wired or wireless connection (e.g., Wi-Fi, Bluetooth, Ethernet, serial connection, etc.). The controller(s) within the control arrangement 2500 can then operate independent of, for example, the host computer. Alternately, according to some embodiments, the connection between, for example, the host computer and the one or more controllers can be maintained for real-time parameter tuning while the model(s) are being executed within the control arrangement 2500. Maintaining a real-time connection also allows real-time interfacing with a graphical user interface (GUI), such as MATLAB, which can serve as the basis for allowing user input during operation.
Within the arrangement 2500 of
According to the control arrangement 2500 of
The top-level controller 2501, the flexible exosuit controller 2503, the support module controller 2505, and the mobile base controller 2507 together form and are controlled as a cyber-physical system of collaborating computational elements controlling physical entities. Specific techniques for modeling and controlling cyber-physical systems can be found in the following publications: “High-Confidence Medical Devices: Cyber-Physical Systems for 21st Century Health Care,” High Confidence Software and Systems Coordinating Group of the Networking and Information Technology Research and Development Program, February 2009; “Body Sensor Networks: A Holistic Approach From Silicon to Users,” Calhoun, B. H. et al., Proceedings of the IEEE, Vol. 100, No. 1, January 2012; “Toward a Science of Cyber—Physical System Integration,” Sztipanovits, J. et al., Proceedings of the IEEE, Vol. 100, No. 1, January 2012; and “Special Issue on Cyber-Physical Systems,” Poovendran, R. et al., Proceedings of the IEEE, Vol. 100, No. 1, January 2012, the entirety of each of which is herein incorporated by reference.
The control arrangement 2500 of
During a standing mode, the control arrangement 2500 controls the modules to provide a safe environment for the user to explore stability and instability while standing. As opposed to a rigid structure that restricts movements according to forced corrective motions, during a standing mode, the modular system allows a user to learn by doing, such as by exploring and/or experimenting with motion (e.g., walking) However, the modular system provides a limited and directed environment so that the user can focus on experiencing and learning the subtasks of standing as a precursor to walking.
By way of example, and without limitation, the control arrangement 2500 operates according to the following acts during the standing mode. Initially, the user is integrated into the modular system in a “zero” position. The user's weight is initially fully supported by the support module (e.g., such as the arm or tether/scaffold). The user can be wearing the flexible exosuit in an entirely passive state.
Upon integrating the user within the modular system, the control arrangement 2500 of the modular system operates to perform one or more acts with respect to allowing the user to explore standing in the vertical and horizontal planes. With respect to the vertical plane, according to one act, the user's weight is slowly loaded onto the user. That is, support of the user's weight by the support module is reduced by vertically lowering the support module so that the user supports more weight through his or her legs, rather than through the support module. Concurrently, one or more additional acts can occur.
By way of example, according to one additional act, sensor readings from the flexible exosuit may indicate that the user is not accepting the additional load. Instead, the user may be collapsing under the increased load. Such indications can be based on, for example, joint angle measurements from the flexible exosuit in comparison to weight load measurements from the support module. In response, one or more antagonistic forces to the collapsing joint are applied through the flexible exosuit to stiffen the flexible exosuit and help the user support his or her weight with their legs. The forces can be variable and dynamic. For example, as the user moves upwards, as detected by, for example, support module force sensors and/or joint angles measurement by IMUs in the flexible exosuit, the flexible exosuit will dynamically relax. As the user moves back downwards (detected by the same sensors or different sensors), the flexible exosuit can again stiffen to aid with the weight acceptance. The adjustments by the support module and the flexible exosuit can be finely tuned to allow the user to determine the maximum level of relaxation before collapse, while maintaining the user within a safe and secure environment.
By way of an additional example, according to another additional act, while loading the weight of the user onto the user's legs, the support module can lock the user's horizontal position while keeping the vertical position unlocked. Under these conditions, the user can move his or her body up and down against gravity, while stiffening, relaxing, or pushing with certain muscles, and experiencing how different muscles and coordinated movements correspond to vertical oscillation/bouncing.
With respect to the horizontal plane, upon integrating the user within the modular system, the control arrangement 2500 of the modular system can operate to perform another act. According to the other act, the support module can operate to allow motion in one of the anterior-posterior plane or medial-lateral plane, while leaving the other of the anterior-posterior plane or medial-lateral plane locked. According to this operation, the support module provides little to no resistance against the user's motion within the unlocked plane when the user is upright or near upright. However, if the user leans past a threshold of the COM stability or balance (e.g., forwards/backwards or side-to-side, depending on the plane), the support module provides more resistance to prevent uncontrolled falling towards the boundaries of the user's balance. Whether the user leans past the threshold of the COM stability or balance can be detected by, for example, position feedback of the actuator within the support module, such as the arm's actuator.
Rather than swaying within the stable boundaries of stability in the anterior-posterior plane, the user may become stuck at the boundary or beyond and be unable to restore himself or herself to an upright position. The support module can actively push or pull the user back to an upright position. Alternatively, or in addition, the flexible exosuit can apply one or more restorative forces to help the user reach an upright position. Alternatively, or in addition, the mobile base may actively move (e.g., forward/backward or left/right, depending on the plane) with the user's legs pivoting on the ground to restore the user to an upright position.
Control of the modular system to allow anterior-posterior or medial-lateral movement can occur until the user can stably oscillate/sway in the particular plane without falling towards boundaries, and until the user can restore himself or herself to an upright position. Upon the user being stable within one plane, the modular system can be controlled to focus on the other plane. Further, upon being stable in both planes, the modular system can be controlled to unlock both planes with respect to the support module and allow the user to move in a 3D upside down cone of stability.
Upon completion of one of the above-described acts, the control arrangement 2500 can control the modular system to perform one or more remaining acts. At the end of performing the above-described acts, the user has learned bodily control with respect to standing.
With respect to a walking mode, the control arrangement 2500 controls the modules to provide a safe environment for the user to explore stability and instability while walking. The walking mode consists of, for example, destabilizing the toddler to go from standing to stepping, and eventually achieving sustained forward walking.
According to one act, the control arrangement 2500 controls the modular system to induce an imbalance in the user to induce walking. The imbalance can be applied to the user through the support module. The imbalance moves the user sideways slightly to trigger a shift in weight to one leg (the stance leg in gait). Subsequently, the un-weighted leg (the swing leg) moves forward and accepts the weight of the user. According to some embodiments, for the first step, the forward motion is small so the mobile base does not move. Rather, the forward motion can be achieved by the support module and the flexible exosuit coordinating with each other.
Stepping involves all joints. However, with respect to toddlers, in particular, the hip, knee, and ankle are the most prominent. Toddlers generally do not have developed/strong hip extension, hip flexion, or ankle plantar flexion, which are the primary sources of propulsion in adults. According to some aspects of the present concepts, during and/or subsequent to triggering imbalance, the flexible exosuit can apply forces and/or cues with respect to hip flexion.
Based on the above, the control arrangement 2500 of the modular system operates to perform one or more acts with respect to allowing the user to explore the locomotion of walking According to one act, through a combination of the position information of the support module, such as the amount the user is leaning on the arm (as indicated by a force sensor), as well as the position of the leg (from joint angle measurements in the flexible exosuit), the modular system can detect when the user leans sideways and shifts his or her weight to one leg. Subsequently, the support module can provide a forward propulsive force to push the user forward, which induces the forward fall over the weight-bearing stance leg (like an inverted pendulum). Simultaneously, the flexible exosuit can support the stance leg and actuate a hip flexion moment in the swing leg. The flexible exosuit can subsequently stop actuating hip flexion, and become transparent to the wearer, allowing the swing leg to come back down and hit the ground. According to some embodiments, the flexible exosuit can also stiffen the swing leg to help with load acceptance immediately prior to this contact. The above actions can be repeated for alternating the left and right legs as the swing leg and the stance leg until the user is flexing his or her hip independently with the correct timing. This information can be detected according to a progression of measurements of one or more of the sensors within the flexible exosuit and/or the modular system as a whole.
Once going from standing to stepping progresses, control of the modular system can shift to the operation of continuous walking Continuous walking involves the rapid transition from one stance leg to the other over successive steps (e.g., left leg is stance leg, fall forward over left leg like an inverted pendulum, right leg flexes, steps forward, then becomes new stance leg, repeat inverted pendulum motion) and redirecting the COM velocity accordingly.
Toddlers have a relatively fast gait frequency so motion during continuous walking can be rapid. Accordingly, in some aspects of the present concepts, the support module follows the trajectory of the hip, torso, pelvis, or COM according to that of a typical/normal user (e.g., normally developing toddler), but the trajectory is scaled temporally to match the user's step frequency. The step frequency can be measured in real-time by, for example, gait sensors in the flexible exosuit. The step frequency can also be scaled spatially to match anthropometric parameters of the user. Such anthropometric parameters can be, for example, measured before integrating the user in the modular system, and can be entered into the modular system as controller parameters.
According to some embodiments, the support module can behave such that the motion of following the trajectory is freely permitted, while motion in other directions is met with some resistance. According to some aspects, the amount of resistance is scaled up the further the user goes from the “desired” motion. In one embodiment, if the user is providing a lot of resistance, the system will stop operation for safety.
The control arrangement 2500 can continue the above acts with respect to the walking mode as the user explores the motions of the body with respect to walking. As the user develops the correct motions, and at the end of performing the above-described acts, the user has learned to control his or her body with respect to walking.
The control discussed above with respect to the acts occurs according to, for example, two timescales. A first timescale occurs in real-time and pertains to inputs and outputs that dynamically control the modules of the modular system, such as the measurements force sensors of the support module and the IMUs in the flexible exosuit. A second timescale logs information that can be used by the modular system and/or a user (e.g., physician, clinician, technician) to modify to the control of the modular system over time as bodily control of the user progresses.
By way of example, information logged with respect to the second timescale allows the system to modify control as the user develops the various subtasks of walking, which include subtasks related to being able to stand. According to the logged information with respect to the second timescale, the modular system modifies control to continue development and the ability for the user to explore different aspects of locomotion, such as the modular system switching from unlocking movement in the medial-lateral plane to unlocking movement in the anterior-posterior plane.
Although the above-described acts include all three modules, one or more of the modules can be omitted either from the beginning, or during the progression, depending on the needs and/or capabilities of the user.
By way of example, in the case where a toddler has normal limb strength and muscle coordination, but needs assistance with balance, the flexible exosuit can be removed while the support module and mobile base can remain. In this example, sensors for limb motion and joint angles can be kept on the user's limbs (despite the user not wearing a flexible exosuit) to continue informing one or more controllers (e.g., top-level controller 2501, mobile base controller 2507, support module controller 2505) of the overall state of the system. Alternatively, or in addition, information acquired from one or more remaining sensors can be used to determine limb motion and joint angles in the absence of sensors on the flexible exosuit. Alternatively, the user may continue wearing the flexible exosuit, but the flexible exosuit can be disengaged from any power source, such as removing force transmission elements, disconnecting the force transmission elements from the power sources, etc. The above-described function with respect to the control aspects of the modular system can be the same, except for excluding the flexible exosuit operations.
By way of another example, in the case where the user has a well-developed sense of balance but is lacking the muscle strength to walk, the support module can be removed while the flexible exosuit and the mobile base remain. Such an example may be when a toddler suffers from abnormal joint alignments and motions because of conditions such as cerebral palsy. In this example, the flexible exosuit can be configured to provide corrective motion. In the absence of the support module, the mobile base can include proximity sensors to detect and maintain a safe distance of the mobile base from the user. According to an actively powered embodiment of the mobile base, the mobile base can follow the user from behind. Further, without the support module, according to some embodiments, a smaller or different mobile base can be used based on the smaller dimensional requirements of the flexible exosuit components on the mobile base as compared to the support module.
According to some concepts of the present disclosure, and without limitation or exclusion of various other control methods, the control arrangement 2500 can be modeled and controlled as a finite-state machine. By way of example, and without limitation or exclusion of various other control methods, the flexible exosuit controller 2503, the support module controller 2505, and the mobile base controller 2507 control the modular system as a six-state machine. Exemplary states of the six-state machine are safety, comfort, initialization, ready/stop, directed exploration, and repetition. At all times during operation, the state(s) of safety and/or comfort can be active. The safety state functions to provide physical safety of the toddler interfacing with the modular system, and the comfort state functions to minimize unnatural forces and/or sensations during operation.
During the safety state, the top-level controller 2501, the flexible exosuit controller 2503, the support module controller 2505, and/or the mobile base controller 2507 function to prevent falling and/or dragging of the toddler by the modular system, limit speed and/or acceleration of the modular system, maintain a threshold grasping force, and/or limit cable displacement. One or more sensors within the control arrangement 2500 provide information during the safety state can include a pressure sensor on the body attachment for indicating vertical security of the body attachment, a force sensor to detect leaning, encoders, an accelerometer, a DOF pressure sensor, and a cable range bracket.
During the comfort state, the top-level controller 2501, the flexible exosuit controller 2503, the support module controller 2505, and the mobile base controller 2507 control the modular system to provide passive vertical motion, allow rotational flexibility, provide soft contact, monitor gripping force, and minimize suit joint resistance.
The initialization state is for positing the toddler within the modular system. The role of the initialization state is to engage the toddler and zero or initialize the modular system. During the initialization state, the top-level controller 2501, the flexible exosuit controller 2503, the support module controller 2505, and/or the mobile base controller 2507 control the modular system to check that the toddler is positioned correctly, initiate a flexible exosuit position default or configuration, hold the toddler's torso, provide the correct holding force, minimize vertical load on the toddler, and initiate actuator positions.
The ready/stop state is for readying the modular system to move initially and between times of exploration (e.g., when the exploration state is disengaged). The role of the ready/stop state is to provide support and stability during no motion, and release during times of motion. During the ready/stop state, the top-level controller 2501, the flexible exosuit controller 2503, the support module controller 2505, and/or the mobile base controller 2507 control the modular system to stabilize the toddler (e.g., adjust the arm of the support module to minimize leaning force), sense forces/torques applied by the toddler, and provide a “stop” state that locks the modular system (e.g., support module, flexible exosuit) until it is stable release the toddler.
The directed exploration state directs the toddler according to specific motions by purposefully de-stabilizing the toddler in a specific direction (e.g., forward), and then stabilizing the toddler with respect to that direction. The role of directed exploration is to provide controlled recoverable instability and direction correction. During the directed exploration state, the top-level controller 2501, the flexible exosuit controller 2503, the support module controller 2505, and/or the mobile base controller 2507 control the modular system to sense the toddler's leaning force, guide the leaning forward, determine a threshold leaning force to initiate hip joint actuation on the flexible exosuit, and relocate the toddler's arms by the flexible exosuit to return to a threshold leaning force.
The repetition state trains the toddler in walking forward. Accordingly, the role of the repetition state is to provide repeated steps forward. During the repetition state, the top-level controller 2501, the flexible exosuit controller 2503, the support module controller 2505, and/or the mobile base controller 2507 control the modular system to simultaneously recover arm relocation, monitor the toddler's inertia with a leaning force, and synchronize hip joint manipulation.
According to some embodiments, during the above-described states, the control arrangement 2500 works to integrate control over the available modules according to the top-level controller 2501, while distributing control functions and tasks to specific modules. According to additional embodiments, the top-level controller 2501 can be considered a distributed controller that is embodied in one or more other controllers within the control arrangement 2500, such that any one of the flexible exosuit controller 2503, the support module controller 2505, and/or the mobile base controller 2507 can function according to the top-level controller 2501. The modular system takes a hierarchical approach, with the top-level controller 2501 determining in real-time the dynamic configurations for the mobile base, the support module, and the flexible exosuit to perform the desired assistive function. According to control provided by the top-level controller 2501, each controller functions according to known tasks based on task-specific parameters that are detected and/or derived from the specific module and/or the modular system as a whole. As discussed above, and without limitation, the parameters are, for example, cadence (steps/min), stride time (s), stride length, step width, duration of double support.
With respect to the flexible exosuit controller 2503, a specific task for control is to provide torque at joints (e.g., hip and/or ankle joints) at appropriate points in the gait cycle. This control results in the toddler's gait parameters exhibiting greater stride length and/or narrower step width, which indicate a more mature walking gait. This applied torque can serve an assistive function, particularly in toddlers lacking the muscle strength or control to move their limbs appropriately, or simply can act as an impulse to induce the toddler to step with the correct timing in the gait cycle.
Within the domain of the flexible exosuit controller 2503, control also can be based on a state-machine formulation. The discrete states represent the various phases of the gait cycle of typically developing toddlers, and sensors can determine the transitions between these states. Sensors can detect information with respect to joint angles and/or kinematics via the use of inertial measurement units (IMUs), encoders, and/or hyper-elastic soft strain sensors across joints. IMUs and foot switches can also sense gait events.
When used in conjunction with the support module, the gait information can be used to synchronize the COM motion as modulated by the support module with the toddler's limb motion(s) modulated by the flexible exosuit. The support module can actively guide the COM to follow a typical trajectory of a developed user that is in sync with assisted limb motion provided by the flexible exosuit. By way of example, such control is directed by the support module controller 2505 and the flexible exosuit controller 2503 through force control that impedes incorrect motion while admitting correct motion. Further, measurements from sensors throughout the flexible exosuit (e.g., IMUs) can be combined to provide absolute orientation of multiple limb segments with sufficient accuracy for kinematic estimation. Further, raw angular velocity and acceleration data, combined with accurate a priori estimates of limb moments of inertia, can be used to calculate joint torques and forces.
By way of example, each state of the state-machine formulation within the flexible exosuit controller 2503 includes a relationship between the current state of the flexible exosuit and the toddler's legs and the required torques for the actuation. The relationship can be based on an impedance control. Such assistive actuation provided by the flexible exosuit allows the child to explore the properties of the leg, as an example, in a gravitational field based on the commands from the top-level level controller 2501.
With respect specifically to the mobile base controller 2507, the mobile base may be operated under a passive, a hybrid, or an active state. In a passive state, the mobile base may include no control. The mobile base may include wheels that allow the mobile base to move according to forces applied by the toddler on the mobile base. In a hybrid state, the mobile base may have control only to prevent the mobile base from impacting the toddler. For the hybrid state, the mobile base may include a sensor that detects the proximity of the toddler and relays this information to the mobile base controller 2507. The mobile base may further include a motion sensor, such as an IMU or an accelerometer, to detect whether the mobile base is in motion. Depending on information from these sensors, the mobile base controller 2507 can operate a break to prevent the mobile base from continuing into a toddler in the event that the toddler stops moving forward.
In the active embodiment of the mobile base, the mobile base controller 2507 coordinates the forward motion of the mobile base with the forward motion of the toddler and/or the support module to achieve a forward trajectory of the toddler. As discussed above, given the larger inertia of the cart, small, rapid motions of the COM can be controlled by the support module, and coarse or overall forward speed of the toddler's walk can be matched by the mobile base according to control by the mobile base controller 2507.
In a configuration with the support module included, the support module on the mobile can maintain a minimum distance between the child and the mobile base. However, in cases without the support module (e.g., exosuit only), integrated sensors can detect the distance between the mobile base and the toddler to make sure a safe margin is maintained. Such proximity sensors can include string potentiometers, infrared, and/or ultrasonic sensors. Such sensors can further include the motion sensors discussed above with respect to the hybrid passive state.
The support module controller 2505 can implement various functions. By way of example, the support module can be actuated vertically at certain points in a toddler's gait cycle—based on sensory information acquired from the flexible exosuit—to provide partial unloading of body weight. The support module can additionally, or in the alternative, lock movement in one direction (e.g., anterior-posterior or medial-lateral) while allowing the toddler to freely move and explore in other directions. Additionally, or in the alternative, the support module can lock movement in all but one direction to allow the toddler to freely explore in the one direction without being burdened by stabilization and support within the other directions. The support module can actively guide the toddler's COM to follow a normal trajectory in sync with limb motion. Such guidance can be provided, by way of example, through force control that impedes incorrect motion while admitting correct motion.
In the arm embodiment of the support module, all loads are transmitted through the 6DOF sensor in the arm. This enables the support module controller 2505 and/or the top-level controller 2501 to detect the toddler's balance, and possibly intent. In the scaffold embodiment, the support module controller 2505 can execute a lower level control algorithm that determines the tensions in individual tethers to generate the desired force-moment at the pelvis.
Within the modular system and the six states discussed above, the top-level controller 2501 determines the dynamic configurations required for the support module and the flexible exosuit to assist children in stabilizing medial-lateral and anterior-posterior sway, forward propulsion, and the coordination of body movements. The top-level controller 2501 ensures interoperability of all the modules. The top-level controller 2501 also enables tuning the levels of assistance provided by the modular system depending on the child's ability. The tuning can be performed by a user, such as a physician, clinician, and/or technician analyzing the performance of the toddler, such as within a medical and/or clinical environment, or by one of the toddler's parents and/or guardians, such as within the home environment.
The top-level controller 2501 integrates sensor information obtained from all the different modules. Such sensor information can include COM information and body weight support levels from the support module, joint kinematics and spatial-temporal gait information such as stride time from the flexible exosuit, and overall velocity information from the mobile base. Based on a totality of the available sensory information from the modules, the top-level controller 2501 can determine the gait cycle state of the toddler. According to the gait cycle state of the toddler, the modular system can take action to facilitate progression through the gait cycle. This can occur according several different ways depending on the individual.
By way of example, according to some embodiments, the support module controller 2505 controls stabilization of the medial-lateral and anterior-posterior body sway during the addition of hip and ankle torques via the flexible exosuit. Concurrently, the flexible exosuit controller 2503 adjusts the magnitudes of hip and ankle torques to maintain forward propulsion as the support module and support module controller 2505 stabilize body sway.
By way of another example, according to some embodiments, a more active control approach can be taken. The more active control approach can purposely create imbalance in, for example, the medial-lateral plane to induce a weight-bearing shift and subsequent stepping. This more active control approach of purposeful destabilization is an automated robotic approach that is similar to what adults do when they lift the toddler's hands and pivot the toddler on one foot/leg as the other foot/leg swings in a forward stepping motion.
Integrated within the control of promoting the development of movement, and to enforce the safety of the modular system for the toddler, the top-level controller 2501 can further detect the instability of the toddler and control one or more of the modules accordingly to prevent and/or compensate for the instability. The control and compensation for instability prevents injury of the toddler from, for example, the toddler falling down or impacting an element of the modular system or other obstacle. Thus, in addition to falling, the modular system further monitors for other dangers, such as obstacles and/or abnormal joint motions that can lead to injury.
By way of example, control techniques that prevent and/or compensate for the instability can include the support module applying one or more forces to re-stabilize the toddler or allow the toddler to fall in a controlled manner. Additionally, or in the alternative, a control technique can include the support module going slack to allow the toddler to fall safely. Approaches of detecting instability can include concepts of bipedal walking, such as zero moment point/center of pressure, and biomechanical concepts, such as the inverted “cone of stability.”
Based on the modularity of the modular system, according to some embodiments of the present concepts, the top-level controller 2501 determines the presence of the additional modules based on, for example, signals provided by the controllers of the other modules (e.g., heart beat signals). Based on the detected presence of the additional modules, the top-level controller 2501 can automatically and dynamically adjust the control of the modular system. Additionally, or in the alternative, the top-level controller 2501 can receive one or more inputs from a user (e.g., physician, clinician, technician, parent, etc.) that instructs the top-level controller 2501 regarding the modules that are present. Based on the received one or more inputs, the top-level controller 2501 adjusts the control of the modular system. Accordingly to some exemplary embodiments, a combined approach can be taken. The top-level controller 2501 can automatically detect the present modules. The modules detected by the top-level controller 2501 can then be presented to a user, such as being presented on a graphical user interface, for confirmation of the present modules and/or selective enablement/disablement. According to aspects of the present concepts, indicators (e.g., visual, audio, tactile) on the modules indicate operation (e.g., power indicator), connectivity (e.g., in communication with the other modules), and/or readiness (e.g., sensor initialization) of each module. By way example, one or more LED indicators on the modules can indicate that the modules are powered on and in communication with the top-level controller 2501 and/or one or more controllers of one or more other modules.
At act 2610, one or more subtask-specific functions of the modules apply one or more forces, cues, or a combination thereof on the user to cause a developing of one or more subtasks of the walking motion. The forces and/or cues can be any of the above-described forces and/or cues, such as applications of force and/or torque about a joint or to a limb, and stabilization and/or de-stabilization about the medial-lateral and/or anterior-posterior directions.
At act 2620, the modules manage control of one or more remaining subtasks of the walking motion, in place of, at least in part, the user, while applying the one or more forces, cues, or a combination thereof. By the modules managing control of the one or more remaining subtasks of the walking motion, the user is able to develop the one or more subtasks of the walking motion by being able to focus on the one or more subtasks. Acts 2610 and 2620 can be repeated for various different subtasks to develop the user's ability to walk. Thus, in the application of a developmentally-delayed toddler, the toddler can be integrated within the multi-module robotic system and have directed development of various subtasks of walking Each development progresses the toddler towards proper motion to overcome the developmental delay.
Based on the acts of the method of
It should be understood that any and all combinations and permutations of the features, functions and concepts discussed in detail herein are contemplated as being part of the inventive subject matter (provided such concepts are not explicitly disclaimed or mutually inconsistent). For example, although differing in appearance, the individual systems and devices and functional componentry depicted and discussed herein can each take on any of the various forms, optional configurations, and functional alternatives described above and below with respect to the other disclosed embodiments, unless explicitly disclaimed or otherwise logically prohibited. Also, the technology described herein may be embodied as various methods, of which numerous examples have been provided. The acts performed as part of any method may be ordered in any suitable way. Accordingly, embodiments may be constructed in which acts are performed in an order different than illustrated, even though shown as sequential acts in illustrative embodiments, in which some acts are performed simultaneously, in which some acts are omitted, and/or in which some acts are adopted from other illustrated embodiments.
Each of these embodiments and obvious variations thereof is contemplated as falling within the spirit and scope of the claimed invention, at least some aspects of which are set forth in the following claims. Moreover, the present concepts expressly include any and all combinations and sub combinations of the preceding elements and aspects.
The present application is a U.S. national phase application of PCT International Patent Application No. PCT/US2015/014672, filed on Feb. 5, 2015, titled, “Systems, Methods, and Devices for Assisting Walking for Developmentally-Delayed Toddlers,” which claims priority to U.S. Provisional Patent Application No. 61/936,162, titled “Multi-Robot Cyberphysical System for Assisting Walking in Developmentally-Delayed Toddlers,” filed Feb. 5, 2014, each of the preceding applications being incorporated herein by reference in its entirety.
Some aspects of the present disclosure were made with government support under NSF Grant No. CNS-1329363 awarded by the National Science Foundation, and the government shares rights to such aspects of the present disclosure.
| Filing Document | Filing Date | Country | Kind |
|---|---|---|---|
| PCT/US2015/014672 | 2/5/2015 | WO | 00 |
| Publishing Document | Publishing Date | Country | Kind |
|---|---|---|---|
| WO2015/120186 | 8/13/2015 | WO | A |
| Number | Name | Date | Kind |
|---|---|---|---|
| 3387305 | Shafer | Jun 1968 | A |
| 3411511 | Marino | Nov 1968 | A |
| 3831467 | Moore | Aug 1974 | A |
| 4023215 | Moore | May 1977 | A |
| 4252112 | Joyce | Feb 1981 | A |
| 4370977 | Mauldin et al. | Feb 1983 | A |
| 4682776 | Mitchell et al. | Jul 1987 | A |
| 4697808 | Larson et al. | Oct 1987 | A |
| 4724827 | Schenck | Feb 1988 | A |
| 4760850 | Phillips et al. | Aug 1988 | A |
| 5020790 | Beard et al. | Jun 1991 | A |
| 5282460 | Boldt | Feb 1994 | A |
| 5584799 | Gray | Dec 1996 | A |
| 5667461 | Hall | Sep 1997 | A |
| 5865714 | Marlowe | Feb 1999 | A |
| 5865770 | Schectman | Feb 1999 | A |
| 6123649 | Lee | Sep 2000 | A |
| 6129691 | Ruppert | Oct 2000 | A |
| 6168634 | Schmitz | Jan 2001 | B1 |
| 6213922 | Afanasenko et al. | Apr 2001 | B1 |
| 6500138 | Irby et al. | Dec 2002 | B1 |
| 6517503 | Naft et al. | Feb 2003 | B1 |
| 6633783 | Dariush et al. | Oct 2003 | B1 |
| 6635024 | Hatton et al. | Oct 2003 | B2 |
| 6666831 | Edgerton | Dec 2003 | B1 |
| 6689075 | West | Feb 2004 | B2 |
| 6741911 | Simmons | May 2004 | B2 |
| 6783555 | Kuhn et al. | Aug 2004 | B2 |
| 6790165 | Huang | Sep 2004 | B2 |
| 6796926 | Reinkensmeyer | Sep 2004 | B2 |
| 6812624 | Pei et al. | Nov 2004 | B1 |
| 6955692 | Grundei | Oct 2005 | B2 |
| 6989669 | Low et al. | Jan 2006 | B2 |
| 7034432 | Pelrine et al. | Apr 2006 | B1 |
| 7034527 | Low et al. | Apr 2006 | B2 |
| 7049732 | Pei et al. | May 2006 | B2 |
| 7056297 | Dohnu et al. | Jun 2006 | B2 |
| 7064472 | Pelrine et al. | Jun 2006 | B2 |
| 7090650 | Ou et al. | Aug 2006 | B2 |
| 7153242 | Goffer | Dec 2006 | B2 |
| 7153246 | Koscielny et al. | Dec 2006 | B2 |
| 7166953 | Heim et al. | Jan 2007 | B2 |
| 7190141 | Ashrafiuon et al. | Mar 2007 | B1 |
| 7199501 | Pei et al. | Apr 2007 | B2 |
| 7211937 | Kornbluh et al. | May 2007 | B2 |
| 7224106 | Pei et al. | May 2007 | B2 |
| 7229390 | Fujii et al. | Jun 2007 | B2 |
| 7233097 | Rosenthal et al. | Jun 2007 | B2 |
| 7252644 | Dewald et al. | Aug 2007 | B2 |
| 7259503 | Pei et al. | Aug 2007 | B2 |
| 7259553 | Arns, Jr. et al. | Aug 2007 | B2 |
| 7307418 | Low et al. | Dec 2007 | B2 |
| 7331906 | He | Feb 2008 | B2 |
| 7341295 | Veatch et al. | Mar 2008 | B1 |
| 7367958 | McBean et al. | May 2008 | B2 |
| 7368862 | Pelrine et al. | May 2008 | B2 |
| 7378878 | Pelrine et al. | May 2008 | B2 |
| 7390309 | Dariush | Jun 2008 | B2 |
| 7410471 | Campbell et al. | Aug 2008 | B1 |
| 7411332 | Kornbluh et al. | Aug 2008 | B2 |
| 7429253 | Shimada et al. | Sep 2008 | B2 |
| 7436099 | Pei et al. | Oct 2008 | B2 |
| 7445606 | Rastegar et al. | Nov 2008 | B2 |
| 7456549 | Heim et al. | Nov 2008 | B2 |
| 7476185 | Drennan | Jan 2009 | B2 |
| 7494450 | Solomon | Feb 2009 | B2 |
| 7521840 | Heim | Apr 2009 | B2 |
| 7521847 | Heim | Apr 2009 | B2 |
| 7537573 | Horst | May 2009 | B2 |
| 7549969 | van den Bogert | Jun 2009 | B2 |
| 7567681 | Pelrine et al. | Jul 2009 | B2 |
| 7578799 | Thorsteinsson et al. | Aug 2009 | B2 |
| 7595580 | Heim | Sep 2009 | B2 |
| 7598651 | Kornbluh et al. | Oct 2009 | B2 |
| 7598652 | Kornbluh et al. | Oct 2009 | B2 |
| 7626319 | Heim | Dec 2009 | B2 |
| 7650204 | Dariush | Jan 2010 | B2 |
| 7652386 | Donelan et al. | Jan 2010 | B2 |
| 7654973 | Firsov | Feb 2010 | B2 |
| 7679267 | Heim | Mar 2010 | B2 |
| 7684896 | Dariush | Mar 2010 | B2 |
| 7705521 | Pelrine et al. | Apr 2010 | B2 |
| 7737685 | Low et al. | Jun 2010 | B2 |
| 7750532 | Heim | Jul 2010 | B2 |
| 7758481 | Drennan | Jul 2010 | B2 |
| 7774177 | Dariush | Aug 2010 | B2 |
| 7775999 | Brown | Aug 2010 | B2 |
| 7785279 | Sankai | Aug 2010 | B2 |
| 7785656 | Pei et al. | Aug 2010 | B2 |
| 7787646 | Pelrine et al. | Aug 2010 | B2 |
| 7804227 | Pelrine et al. | Sep 2010 | B2 |
| 7857774 | Sankai | Dec 2010 | B2 |
| 7860562 | Endo et al. | Dec 2010 | B2 |
| 7883546 | Kazerooni et al. | Feb 2011 | B2 |
| 7887471 | McSorley | Feb 2011 | B2 |
| 7897168 | Chen et al. | Mar 2011 | B2 |
| 7911761 | Biggs et al. | Mar 2011 | B2 |
| 7915790 | Heim et al. | Mar 2011 | B2 |
| 7918808 | Simmons | Apr 2011 | B2 |
| 7921541 | Pei et al. | Apr 2011 | B2 |
| 7923064 | Pelrien et al. | Apr 2011 | B2 |
| 7923902 | Heim | Apr 2011 | B2 |
| 7947004 | Kazerooni et al. | May 2011 | B2 |
| 7952261 | Lipton et al. | May 2011 | B2 |
| 7985193 | Thorsteinsson et al. | Jun 2011 | B2 |
| 7977923 | Pelrine et al. | Jul 2011 | B2 |
| 7981508 | Sharma et al. | Jul 2011 | B1 |
| 7990022 | Heim | Aug 2011 | B2 |
| 7998040 | Kram | Aug 2011 | B2 |
| 8048007 | Roy | Nov 2011 | B2 |
| 8057410 | Angold | Nov 2011 | B2 |
| 8058861 | Pelrine et al. | Nov 2011 | B2 |
| 8075633 | Herr et al. | Dec 2011 | B2 |
| 8083644 | Purdy et al. | Dec 2011 | B2 |
| 8096965 | Goffer et al. | Jan 2012 | B2 |
| 8114034 | Ikeuchi et al. | Feb 2012 | B2 |
| 8125755 | Garcia et al. | Feb 2012 | B2 |
| 8127437 | Lipton et al. | Mar 2012 | B2 |
| 8142370 | Weinberg et al. | Mar 2012 | B2 |
| 8147436 | Agrawal et al. | Apr 2012 | B2 |
| 8164232 | Kornbluh et al. | Apr 2012 | B2 |
| 8183739 | Heim | May 2012 | B2 |
| 8222799 | Polyakov et al. | Jul 2012 | B2 |
| 8231687 | Bedard et al. | Jul 2012 | B2 |
| 8235869 | Rastegar et al. | Aug 2012 | B2 |
| 8246559 | Hoffman et al. | Aug 2012 | B2 |
| 8248750 | Biggs et al. | Aug 2012 | B2 |
| 8274244 | Bhugra et al. | Sep 2012 | B2 |
| 8283839 | Heim | Oct 2012 | B2 |
| 8287477 | Herr et al. | Oct 2012 | B1 |
| 8292836 | Matsuoka et al. | Oct 2012 | B2 |
| 8299634 | Donelan et al. | Oct 2012 | B2 |
| 8311623 | Sanger | Nov 2012 | B2 |
| 8316526 | Pei et al. | Nov 2012 | B2 |
| 8316719 | Majidi et al. | Nov 2012 | B2 |
| 8323355 | Latour | Dec 2012 | B2 |
| 8325458 | Prahlad et al. | Dec 2012 | B2 |
| 8348875 | Goffer et al. | Jan 2013 | B2 |
| 8376971 | Herr et al. | Feb 2013 | B1 |
| 8409117 | Cheng et al. | Apr 2013 | B2 |
| 8436508 | Kornbluh et al. | May 2013 | B2 |
| 8438757 | Roser | May 2013 | B2 |
| 8467904 | Dariush | Jun 2013 | B2 |
| 8488295 | Garcia et al. | Jul 2013 | B2 |
| 8508109 | Pelrine et al. | Aug 2013 | B2 |
| 8551029 | Herr et al. | Oct 2013 | B1 |
| 8551184 | Herr | Oct 2013 | B1 |
| 8562691 | Endo et al. | Oct 2013 | B2 |
| 8564926 | Prahlad et al. | Oct 2013 | B2 |
| 8585620 | McBean et al. | Nov 2013 | B2 |
| 8597369 | Hansen et al. | Dec 2013 | B2 |
| 8608479 | Liu | Dec 2013 | B2 |
| 8608674 | Krebs et al. | Dec 2013 | B2 |
| 8622938 | Sankai | Jan 2014 | B2 |
| 8663133 | Johnson et al. | Mar 2014 | B2 |
| 8665578 | Pelrine et al. | Mar 2014 | B2 |
| 8679575 | Biggs et al. | Mar 2014 | B2 |
| 8766925 | Perlin et al. | Jun 2014 | B2 |
| 8764850 | Hansen et al. | Jul 2014 | B2 |
| 8773148 | Sankai et al. | Jul 2014 | B2 |
| 8847611 | Ulmen et al. | Sep 2014 | B2 |
| 8905955 | Goffer et al. | Dec 2014 | B2 |
| 8920517 | Smith et al. | Dec 2014 | B2 |
| 8926534 | McBean et al. | Jan 2015 | B2 |
| 8938289 | Einav et al. | Jan 2015 | B2 |
| 8961439 | Yang et al. | Feb 2015 | B2 |
| 8975888 | Pelrine et al. | Mar 2015 | B2 |
| 8981621 | Pelrine et al. | Mar 2015 | B2 |
| 8986233 | Aoki et al. | Mar 2015 | B2 |
| 9044346 | Langlois et al. | Jun 2015 | B2 |
| 9072941 | Duda et al. | Jul 2015 | B2 |
| 9101323 | Einarsson et al. | Aug 2015 | B2 |
| 9144528 | Agrawal et al. | Sep 2015 | B2 |
| 9149370 | Herr et al. | Oct 2015 | B2 |
| 9195794 | Dariush | Nov 2015 | B2 |
| 9198821 | Unluhisarcikli et al. | Dec 2015 | B2 |
| 9221177 | Herr et al. | Dec 2015 | B2 |
| 9228822 | Majidi et al. | Jan 2016 | B2 |
| 9231186 | Busgen et al. | Jan 2016 | B2 |
| 9266233 | Kornbluh et al. | Feb 2016 | B2 |
| 9333097 | Herr et al. | May 2016 | B2 |
| 9351900 | Walsh et al. | May 2016 | B2 |
| 9387096 | Sverrisson et al. | Jun 2016 | B2 |
| 9403272 | Kornbluh et al. | Aug 2016 | B2 |
| 9427864 | Kornbluh et al. | Aug 2016 | B2 |
| 10115319 | Asbeck et al. | Oct 2018 | B2 |
| 20010007845 | Afanasenko et al. | Jul 2001 | A1 |
| 20030009120 | MacAllister | Jan 2003 | A1 |
| 20030030397 | Simmons | Feb 2003 | A1 |
| 20030064869 | Reinkensmeyer | Apr 2003 | A1 |
| 20030092545 | Koscielny et al. | May 2003 | A1 |
| 20030120183 | Simmons | Jun 2003 | A1 |
| 20030125781 | Dohno et al. | Jul 2003 | A1 |
| 20040043879 | Huang | Mar 2004 | A1 |
| 20040064195 | Herr | Apr 2004 | A1 |
| 20040087418 | Eldridge | May 2004 | A1 |
| 20040106881 | McBean et al. | Jun 2004 | A1 |
| 20040116260 | Drennan | Jul 2004 | A1 |
| 20040147378 | Conklin et al. | Jul 2004 | A1 |
| 20040204294 | Wilkinson | Oct 2004 | A2 |
| 20050010150 | Firsov | Jan 2005 | A1 |
| 20050049865 | Yaxin et al. | Mar 2005 | A1 |
| 20050070834 | Herr et al. | Mar 2005 | A1 |
| 20050101448 | He | May 2005 | A1 |
| 20050157893 | Pelrine et al. | Jul 2005 | A1 |
| 20050288157 | Santos-Munne et al. | Dec 2005 | A1 |
| 20060079817 | Dewald et al. | Apr 2006 | A1 |
| 20060108755 | Smyler et al. | May 2006 | A1 |
| 20060136206 | Ariu et al. | Jun 2006 | A1 |
| 20060192465 | Kornbluh et al. | Aug 2006 | A1 |
| 20060249315 | Herr et al. | Nov 2006 | A1 |
| 20070004570 | Afanasenko et al. | Jan 2007 | A1 |
| 20070004571 | Gonzalez | Jan 2007 | A1 |
| 20070066918 | Dewald et al. | Mar 2007 | A1 |
| 20070111868 | Fujii et al. | May 2007 | A1 |
| 20070123997 | Herr et al. | May 2007 | A1 |
| 20070135279 | Purdy et al. | Jun 2007 | A1 |
| 20080039756 | Thorsteinsson et al. | Feb 2008 | A1 |
| 20080062589 | Drabing | Mar 2008 | A1 |
| 20080071386 | McBean et al. | Mar 2008 | A1 |
| 20080075930 | Kornbluh et al. | Mar 2008 | A1 |
| 20080097269 | Weinberg et al. | Apr 2008 | A1 |
| 20080156363 | Ikeuchi et al. | Jul 2008 | A1 |
| 20080218132 | Pelrine et al. | Sep 2008 | A1 |
| 20080224564 | Pelrine et al. | Sep 2008 | A1 |
| 20080289952 | Pelrine et al. | Nov 2008 | A1 |
| 20080300118 | Wehrell | Dec 2008 | A1 |
| 20090042702 | Toronto et al. | Feb 2009 | A1 |
| 20090221928 | Einav et al. | Sep 2009 | A1 |
| 20090255531 | Johnson et al. | Oct 2009 | A1 |
| 20090256817 | Perlin et al. | Oct 2009 | A1 |
| 20090306548 | Bhugra et al. | Dec 2009 | A1 |
| 20090319054 | Sankai | Dec 2009 | A1 |
| 20100000547 | Johnson et al. | Jan 2010 | A1 |
| 20100007240 | Kornbluh et al. | Jan 2010 | A1 |
| 20100024180 | Pei et al. | Feb 2010 | A1 |
| 20100026143 | Pelrine et al. | Feb 2010 | A1 |
| 20100030343 | Hansen et al. | Feb 2010 | A1 |
| 20100038983 | Bhugra et al. | Feb 2010 | A1 |
| 20100056966 | Toth | Mar 2010 | A1 |
| 20100144490 | Purdy et al. | Jun 2010 | A1 |
| 20100152630 | Matsuoka et al. | Jun 2010 | A1 |
| 20100185259 | Shiba et al. | Jul 2010 | A1 |
| 20100185301 | Hansen et al. | Jul 2010 | A1 |
| 20100204804 | Garrec | Aug 2010 | A1 |
| 20100271051 | Sankai et al. | Oct 2010 | A1 |
| 20100274364 | Pacanowsky | Oct 2010 | A1 |
| 20100280628 | Sankai | Nov 2010 | A1 |
| 20100286796 | Clausen | Nov 2010 | A1 |
| 20100298834 | Hildebrandt | Nov 2010 | A1 |
| 20100319215 | Roser | Dec 2010 | A1 |
| 20100324698 | Sverrisson et al. | Dec 2010 | A1 |
| 20110004322 | Sankai | Jan 2011 | A1 |
| 20110009793 | Lucero | Jan 2011 | A1 |
| 20110033835 | Endo et al. | Jan 2011 | A1 |
| 20110025170 | Rosenthal et al. | Feb 2011 | A1 |
| 20110040216 | Herr et al. | Feb 2011 | A1 |
| 20110062948 | Arns, Jr. et al. | Mar 2011 | A1 |
| 20110071647 | Mahon | Mar 2011 | A1 |
| 20110093089 | Martin | Apr 2011 | A1 |
| 20110150966 | Kazerooni et al. | May 2011 | A1 |
| 20110154641 | Pelrine et al. | Jun 2011 | A1 |
| 20110155307 | Pelrine et al. | Jun 2011 | A1 |
| 20110174524 | Sharma et al. | Jul 2011 | A1 |
| 20110193362 | Prahlad et al. | Aug 2011 | A1 |
| 20110201978 | Jeon et al. | Aug 2011 | A1 |
| 20110209337 | Pei et al. | Sep 2011 | A1 |
| 20110245738 | Agrawal et al. | Oct 2011 | A1 |
| 20110282255 | Nace | Nov 2011 | A1 |
| 20110295384 | Herr et al. | Dec 2011 | A1 |
| 20110295385 | Herr et al. | Dec 2011 | A1 |
| 20110313331 | Dehez | Dec 2011 | A1 |
| 20120019223 | Pelrine et al. | Jan 2012 | A1 |
| 20120023638 | Leicester | Feb 2012 | A1 |
| 20120056903 | Shinohara et al. | Mar 2012 | A1 |
| 20120071797 | Aoki et al. | Mar 2012 | A1 |
| 20120100286 | Sharma et al. | Apr 2012 | A1 |
| 20120109031 | Vollbrecht | May 2012 | A1 |
| 20120120544 | Pelrine et al. | May 2012 | A1 |
| 20120128960 | Busgen et al. | May 2012 | A1 |
| 20120165709 | Goffer et al. | Jun 2012 | A1 |
| 20120169184 | Pelrine et al. | Jul 2012 | A1 |
| 20120177934 | Vogel et al. | Jul 2012 | A1 |
| 20120179075 | Perry et al. | Jul 2012 | A1 |
| 20120181896 | Kronbluh et al. | Jul 2012 | A1 |
| 20120185052 | Lefeber | Jul 2012 | A1 |
| 20120209152 | Cordo | Aug 2012 | A1 |
| 20120238914 | Goldfield et al. | Sep 2012 | A1 |
| 20120248942 | Biggs et al. | Oct 2012 | A1 |
| 20120253234 | Yang et al. | Oct 2012 | A1 |
| 20120271207 | Schoen et al. | Oct 2012 | A1 |
| 20120279175 | Biggs et al. | Nov 2012 | A1 |
| 20120289870 | Hsiao-Wecksler et al. | Nov 2012 | A1 |
| 20120330198 | Patoglu | Dec 2012 | A1 |
| 20130013085 | Smith et al. | Jan 2013 | A1 |
| 20130019749 | Hufton et al. | Jan 2013 | A1 |
| 20130040783 | Duda et al. | Feb 2013 | A1 |
| 20130058001 | Prahlad et al. | Mar 2013 | A1 |
| 20130079686 | Sessions | Mar 2013 | A1 |
| 20130093439 | Ulmen et al. | Apr 2013 | A1 |
| 20130102935 | Kazerooni et al. | Apr 2013 | A1 |
| 20130123672 | Goffer et al. | May 2013 | A1 |
| 20130130866 | Wehrell | May 2013 | A1 |
| 20130158444 | Herr et al. | Jun 2013 | A1 |
| 20130165817 | Horst et al. | Jun 2013 | A1 |
| 20130179154 | Okuno | Jul 2013 | A1 |
| 20130186699 | Prahald et al. | Jul 2013 | A1 |
| 20130211295 | Johnson et al. | Aug 2013 | A1 |
| 20130225371 | Harrer | Aug 2013 | A1 |
| 20130226048 | Unluhisarcikli et al. | Aug 2013 | A1 |
| 20130230667 | Sharma et al. | Sep 2013 | A1 |
| 20130237884 | Kazerooni et al. | Sep 2013 | A1 |
| 20130245512 | Goffer et al. | Sep 2013 | A1 |
| 20130253385 | Goffer et al. | Sep 2013 | A1 |
| 20130261513 | Goffer et al. | Oct 2013 | A1 |
| 20130261766 | Langlois et al. | Oct 2013 | A1 |
| 20130268256 | Dariush | Oct 2013 | A1 |
| 20130274640 | Butters et al. | Oct 2013 | A1 |
| 20130288863 | Yamamoto et al. | Oct 2013 | A1 |
| 20130289452 | Smith et al. | Oct 2013 | A1 |
| 20130296746 | Herr et al. | Nov 2013 | A1 |
| 20130307370 | Jenninger et al. | Nov 2013 | A1 |
| 20130310979 | Herr et al. | Nov 2013 | A1 |
| 20130312541 | Majidi et al. | Nov 2013 | A1 |
| 20130328440 | Kornbluh et al. | Dec 2013 | A1 |
| 20140046455 | Herr et al. | Feb 2014 | A1 |
| 20140194781 | Einarsson et al. | Jul 2014 | A1 |
| 20150173993 | Walsh et al. | Jun 2015 | A1 |
| 20150266180 | Kornbluh et al. | Sep 2015 | A1 |
| 20150266181 | Kornbluh et al. | Sep 2015 | A1 |
| 20150297934 | Agrawal | Oct 2015 | A1 |
| 20150298765 | Golden, Jr. | Oct 2015 | A1 |
| 20150321399 | Hong et al. | Nov 2015 | A1 |
| 20160101516 | Kornbluh et al. | Apr 2016 | A1 |
| 20160101517 | Kornbluh et al. | Apr 2016 | A1 |
| 20160107309 | Walsh et al. | Apr 2016 | A1 |
| 20160220438 | Walsh et al. | Aug 2016 | A1 |
| 20160278948 | Piercy et al. | Sep 2016 | A1 |
| 20160284231 | Walsh et al. | Sep 2016 | A1 |
| 20170027735 | Walsh et al. | Feb 2017 | A1 |
| 20170163435 | Ehsani et al. | Jun 2017 | A1 |
| 20170202724 | Walsh et al. | Jul 2017 | A1 |
| 20180008502 | Asbeck et al. | Jan 2018 | A1 |
| Number | Date | Country |
|---|---|---|
| 1868434 | Nov 2006 | CN |
| 202342034 | Jul 2012 | CN |
| 101175456 | Mar 2013 | CN |
| 102327173 | May 2013 | CN |
| 19944139 | Apr 2001 | DE |
| 0016268 | Oct 1980 | EP |
| 0141640 | Oct 1984 | EP |
| 0302148 | Feb 1989 | EP |
| 0509723 | Oct 1992 | EP |
| 1306792 | May 2003 | EP |
| 1324403 | Jul 2003 | EP |
| 1260201 | Dec 2008 | EP |
| 2226053 | Sep 2010 | EP |
| 1842518 | Sep 2011 | EP |
| 1589059 | Jun 2012 | EP |
| 2497610 | Sep 2012 | EP |
| 2548543 | Jan 2013 | EP |
| 1550689 | Apr 2013 | EP |
| 2649976 | Oct 2013 | EP |
| H07163607 | Jun 1995 | JP |
| 2002301124 | Oct 2002 | JP |
| 2005000500 | Jan 2005 | JP |
| 2007000391 | Jan 2007 | JP |
| 2008067762 | Mar 2008 | JP |
| 4345025 | Oct 2009 | JP |
| 2010042069 | Feb 2010 | JP |
| 2010051416 | Mar 2010 | JP |
| 4424269 | Mar 2010 | JP |
| 2010075656 | Apr 2010 | JP |
| 4582523 | Nov 2010 | JP |
| 2011036375 | Feb 2011 | JP |
| 4848260 | Dec 2011 | JP |
| 2012192013 | Oct 2012 | JP |
| 2013146328 | Aug 2013 | JP |
| 2014018536 | Feb 2014 | JP |
| 2014034145 | Mar 2014 | JP |
| WO2004017890 | Mar 2004 | WO |
| WO2004039292 | May 2004 | WO |
| WO2004047928 | Jun 2004 | WO |
| WO2005102208 | Nov 2005 | WO |
| WO2011008934 | Jan 2011 | WO |
| WO2011026086 | Mar 2011 | WO |
| WO2011030641 | Mar 2011 | WO |
| 2011126985 | Oct 2011 | WO |
| 2012014164 | Feb 2012 | WO |
| WO2012050938 | Apr 2012 | WO |
| WO2012103073 | Aug 2012 | WO |
| WO2012124328 | Sep 2012 | WO |
| WO2012178171 | Dec 2012 | WO |
| WO2013019749 | Feb 2013 | WO |
| 2013033669 | Mar 2013 | WO |
| WO2013033669 | Mar 2013 | WO |
| WO2013044226 | Mar 2013 | WO |
| 2013049658 | Apr 2013 | WO |
| WO2014109799 | Jul 2014 | WO |
| WO2014194257 | Dec 2014 | WO |
| WO2015120186 | Aug 2015 | WO |
| WO2015157731 | Oct 2015 | WO |
| WO2015088863 | Dec 2015 | WO |
| WO2016089466 | Jun 2016 | WO |
| WO2017040669 | Mar 2017 | WO |
| 2017160751 | Sep 2017 | WO |
| 2018017436 | Jan 2018 | WO |
| Entry |
|---|
| Banala, S. K. et al., “Active leg exoskeleton (alex) for gait rehabilitation of motor-impaired patients,” in Proc. 2007 IEEE 10th Int. Conf. Rehabil Robotics, pp. 401-407, Jun. 2007. |
| Browning, R. C. et al., “The effects of adding mass to the legs on the energetics and biomechanics of walking,” Medicine and Science in Sports and Exercise, col. 39, p. 515, Apr. 2007. |
| Chu, A. et al, “On the biomimetric design of the Berkeley lower extremity exoskeleton (BLEEX)”, Proc. 2005 in IEEE Int. Conf. Robotics and Automation (IEEE Press, Barcelona, Spain, pp. 4356-4363 Apr. 2006). |
| Clevertex: Development of Strategic Master Plan for the transformation of the traditional textile and clothing into a knowledge driven industrial sector by 2015, 160 pages, dated prior to Jul. 2014. |
| Collins, S., et al., “Efficient Bipedal Robots Based on Passive-Dynamic Walkers,” Science, vol. 307, Issue 5712, pp. 1082-1085, Feb. 18, 2005. |
| Cool, J.C., “Biomechanics of orthoses for the subluxed shoulder,” Prosthetics & Orthotics International; vol. 13, Issue 2, pp. 90-96, 1989. |
| da Silva, A. F. et al., “FBG Sensing Glove for Monitoring Hand Posture,” IEEE Sensors Journal, vol. 11, Issue 10, pp. 2442-2448, Oct. 2011. |
| De Rossi, D. et al., “Wearable technology for biomechanics: e-textile or micromechanical sensors?” IEEE engineering in medicine and biology magazine, vol. 29, No. 3, pp. 37-43, May/Jun. 2010. [Online]. Available: http://www.ncbi.nlm.nih.gov/pubmed/20659856. |
| Delp, S. L. et al., “OpenSim: open-source software to create and analyze dynamic simulations of movement.” IEEE transactions on bio-medical engineering, vol. 54, No. 11, pp. 1940-1950, Nov. 2007. [Online]. Available: http://www.ncbi.nlm.nih.gov/pubmed/18018689. |
| Dollar, A. M. et al., “Lower extremity exoskeletons and active orthoses: Challenges and state-of-the-art,”, IEEE Transactions on Robotics, vol. 24, No. 1, pp. 144-158, Feb. 2008. |
| Erk, K. A. et al., “Strain stiffening in synthetic and biopolymer networks,” Biomacromolecules, vol. 11, No. 5, pp. 1358-1363, May 2010. |
| Farris D.J., et al., Human medial gastrocnemius force-velocity behavior shifts with locomotion speed and gait. Proc Natl Acad Sci USA. Jan. 2012; 109:977-982. |
| Ferris, D. P. et al., “Robotic lower limb exoskeletons using proportional myoelectric control,” in EMBC 2009, Annual International Conference of the IEEE Engineering in Medicine and Biology Society, 2009. |
| Ferris, D.P. et al., A Physiologist's Perspective on Robotic Exoskeletons for Human Locomotion. Int J HR, 4(3): p. 507-528, 2007. |
| Ghodsi et al., De novo Likelihood-based measures for comparing genome assemblies. In: BMC Research Notes 2013, Aug. 22, 2013—online retrieved on Oct. 25, 2016. |
| Gibbs, P. et al.: Wearable Conductive Fiber Sensors for Multi-Axis Human Joint Angle Measurements. |
| Journal of NeuroEngineering and Rehabilitation, Mar. 2, 2005. |
| Goodvin, C.I.: Development of a Real-time Spinal Motion Inertial Measurement System for Vestibular Disorder Application, University of Victoria, 155 pages, date 2003. |
| Gregorczyk, K. N., et al., The effects of a lower body exoskeleton load carriage assistive device on oxygen consumption and kinematics during walking with loads, in 25th Army Sci. Conf., Florida, USA, 2006. |
| Hallemans, A. et al.: 3D joint dynamics of walking in toddlers. A cross-sectional study spanning the first rapid development phase of walking. Gait & Posture, 22:107-118, 2005. |
| Kadaba, M. P., et al., “Measurement of lower extremity kinematics during level walking.” Journal of orthopaedic research: official publication of the Orthopaedic Research Society, vol. 8, No. 3, pp. 383-392, May 1990. [Online]. Available: http://www.ncbi.nlm.nih.gov/pubmed/2324857. |
| Kawamoto, H., et al., Power assist method for HAL-3 using EMG-based feedback controller. in Systems, Man and Cybernetics, 2003. IEEE International Conference on. 2003. |
| Kim, D.-H. et al., “Epidermal electronics.” Science, vol. 333, No. 6044, pp. 838-843, Aug. 2011. [Online] Available: http://www.sciencemag.org/cgi/doi/10.1126/science.1206157. |
| Kramer, R. K. et al., “Soft curvature sensors for joint angle proprioception,” in 2011 IEEE/RSJ International Conference on Intelligent Robots and Systems. IEEE, pp. 1919-1926, Sep. 2011. [Online]. Available: http://ieeexplore.ieee.org/lpdocs/epic03/wrapper.htm?arnumber=6094701. |
| Kramer, R. K. et al., “Wearable tactile keypad with stretchable artificial skin,” 2011 IEEE International Conference on Robotics and Automation, pp. 1103-1107, May 2011. [Online]. Available: http://ieeexplore.ieee.org/lpdocs/epic03/wrapper.htm?arnumber=5980082. |
| Kulyukin, V. A.: Advances in Human-Robot Interaction, 354 pages, Dec. 2009. |
| Lee, S. W. et al.: Biomimetic Approach Enables Functional Movements of Hand Post Stroke: A Pilot Study, 2 pages, dated 2012. |
| Lipomi, D. J. et al., “Skin-like pressure and strain sensors based on transparent elastic films of carbon nanotubes.” Nature nanotechnology, vol. 6, No. 12, pp. 788-792, Jan. 2011. [Online]. Available: http://www.ncbi.nlm.nih.gov/pubmed/22020121. |
| Majidi, C. et al., “A non-differential elastomer curvature sensor for softer-than-skin electronics,” Smart Materials and Structures, vol. 20, No. 10, p. 105017, Oct. 2011. [Online]. Available: http://stacks.iop.org/0964-1726/20/i=10/a=105017?key=crossref.0cca7e97d6ad7110bcdcaf45f30f3b60. |
| Malcolm, Philippe et al., Fast Exoskeleton Optimization. Science, vol. 356, Issue 6344, pp. 1230-1231, Jun. 23, 2017. |
| Mattila, H. R., Intelligent textiles and clothing, Woodhead Publishing Limited, 525 pages, © 2006. |
| McGeer, T., Passive Bipedal Running. Proceedings of the Royal Society of London. Series B, Biological Sciences, 240(1297): p. 107-134, May 1990. |
| Newman, D. J. et al., Astronaut Bio-Suit System to Enable Planetary Exploration. In International Astronautical Conference, Vancouver, Canada, Oct. 2004. |
| Park, Y. L. et al., Active Modular Elastomer Sleeve for Soft Wearable Assistance Robots, 2012 IEEE/RSJ International Con. On Intelligent Robots and Systems Vilamoura, Algarve, Portugal, 8 pages, Oct. 7-12, 2012. |
| Park, Y.-L., et al., “Design and Fabrication of Soft Artificial Skin Using Embedded Microchannels and Liquid Conductors,” IEEE Sensors Journal, vol. 12, No. 8, pp. 2711-2718, Aug. 2012. [Online]. Available: http://ieeexplore.ieee.org/lpdocs/epic03/wrapper.htm?arnumber=6203551. |
| Park, Y.-L., “Hyperelastic pressure sensing with a liquid-embedded elastomer,” Journal of Micromechanics and Microengineering, vol. 20, No. 12, p. 125029, Dec. 2010. [Online]. Available: http://stacks.iop.org/0960-1317/20/i=12/a=125029?key=crossref.84cffc44789ba7bde0bdfd169e25af91. |
| Park, Y.-L., et al.: Bio-inspired Active Soft Orthotic Device for Ankle Foot Pathologies, 2011 IEEE/RSJ International Conference on Intelligent Robots and Systems, San Francisco, CA, USA, 8 pages, Sep. 25-30, 2011. |
| Pereira da Fonseca, P. F.: Validation of two types of textile electrodes for electrocardiography and electromyography measurement applications, 126 pages, dated Jul. 2012. |
| Polonen et al. Automatic Intensity Quantification of Fluorescence Targets from microscope Images with Maximum Likelihood Estimation. 17th European Signal Processing Conference, Aug. 24-28, 2009—retrieved online Oct. 25, 2016. |
| Pratt, J. et al., The RoboKnee: An exoskeleton for enhancing strength and endurance during walking, in IEEE Int. Conf. Robotics and Automation (ICRA), New Orleans, USA (IEEE Press), pp. 2430-2435, Apr. 2004. |
| Quintero, H. A. et al., “Control and Implementation of a Powered Lower Limb Orthosis to Aid Walking in Paraplegic Individuals,” in IEEE International Conference on Rehabilitation Robotics, Switzerland, pp. 1-6, Jun. 29-Jul. 1, 2011. |
| Ramuz, M. et al., “Transparent, Optical, Pressure-Sensitive Artificial Skin for Large-Area Stretchable Electronics,” Advanced Materials , May 2012. [Online]. Available: http://doi.wiley.com/10.1002/adma.201200523. |
| Reid, S. A. et al., “Biomechanical assessment of rucksack shoulder strap attachment location: effect on load distribution to the torso,” presented at the RTO HFM specialists' Meeting on “Soldier Mobility: Innovations in Load Carriage System Design and Evaluation,” NATO-RTO Meeting Proceedings: MP-056 (Neuilly-sur-Seine: NATO). Jun. 1-6, 2000. |
| Royer, T.D. et al., (2005) 'Manipulations of Leg Mass and Moment of Inertia: Effects on Energy Cost of Walking, Medicine & Science in Sports & Exercise, vol. 37, No. 4: p. 649-656, 2005. |
| Salvendy, G.: Smart Clothing Technology and Applications, Human Factors and Ergonomics, by Taylor and Francis Group, LLC, 290 pages, © 2010. |
| Schiele, A. “Ergonomics of Exoskeletons: Objective Performance Metrics” in Euro Haptics conference and symposium on Haptic Interfaces for Virtual Environmental Teleoperator Systems, Salt Lake City, UT, USA, Mar. 2009. |
| Scilingo, E. P. et al., “Strain-sensing fabrics for wearable kinaesthetic-like systems,” IEEE Sensors Journal, vol. 3, No. 4, pp. 460-467, Aug. 2003. [Online]. Available: http://ieeexplore.ieee.org/lpdocs/epic03/wrapper.htm?arnumber=1226639. |
| Silva, H. R., et al.: Wireless Hydrotherapy Smart-Suit Network for Posture Monitoring, 5 pages, dated 2007. |
| Strauser, K. A. et al., “The development and testing of a human machine interface for a mobile medical exoskeleton” in IEEE Int Conf, Intelligent Robots and Systems, San Francisco, CA. USA, Sep. 2011. |
| Tesconi, M., et al., “Wearable sensorized system for analyzing the lower limb movement during rowing activity,” 2007 IEEE International Symposium on Industrial Electronics, pp. 2793-2796, Jun. 2007. [Online]. Available: http://ieeexplore.ieee.org/lpdocs/epic03/wrapper.htm?arnumber=4375052. |
| Tiwana, M. I., et al., “A review of tactile sensing technologies with applications in biomedical engineering,” Sensors and Actuators A: Physical, vol. 179, pp. 17-31, Jun. 2012. [Online]. Available: http://linkinghub.elsevier.com/retrieve/pii/S0924424712001641. |
| Vogt, D. M., et al., Design and Characterization of a Soft Multi-Axis Force Sensor Using Embedded Microfludic Channels, IEEE Sensors Journal, vol. 13. No. 10, 9 pages, Oct. 2013. |
| Walsh, C. J., et al., A Quasi-Passive Leg Exoskeleton for Load Carrying Augmentation. International Journal of Humanoid Robotics, Special Issue: Active Exoskeletons, 4(3): 487-506, 2007. |
| Wehner, M., 2012 “Man to Machine, Applications in Electromyography,” EMG Methods for Evaluation Muscle and Nerve Functions. Intech Publishing, Sep. 13, 2012 http://intechopen.com/articles/show/title/man-to-machine-applications-in-electromyography. |
| Wehner, M., et al., “Experimental characterization of components for active soft orthotics,” in Proc. IEEE Int. Conf. Biomed. Rob. Biomechatron., Roma, Italy, Jun. 2012. |
| Wehner, M., et al., “Lower Extremity Exoskeleton Reduces Back Forces in Lifting” ASME Dynamic Systems and Control Conference, Hollywood, California, USA pp. 49-56, Oct. 12-14, 2009. |
| Woodman, O.J. “An introduction to inertial navigation,” Technical Report UCAM-CL-TR-696, Aug. 2007. |
| Yamada, T. et al., “A stretchable carbon nanotube strain sensor for human-motion detection.” Nature Nanotechnology, vol. 6, No. 5 pp. 296-301, May 2011. [Online]. Available: http:/ncbi.nlm.nih.gov/pubmed/21441912. |
| Zhang, R. et al., “Carbon nanotube polymer coatings for textile yarns with good strain sensing capability,” Sensors and Actuators A: Physical, vol. 179, pp. 83-91, Jun. 2012. [Online]. Available: http://linkinghub.elsevier.com/retrieve/pii/S0924424712001938. |
| Zhang, Juanjuan et al., Human-in-the-Loop Optimization of Exoskeleton Assistance During Walking, Science, vol. 356, pp. 1280-1284, Jun. 23, 2017. |
| Zoss, A.B., et al., Biomechanical design of the Berkeley lower extremity exoskeleton (BLEEX), IEE/ASME Transactions on Mechatronics, 11(2): p. 128-138, Apr. 2006. |
| PCT International Search Report, issued in International Application No. PCT/EP2003/012123, dated Jun. 22, 2004. |
| PCT International Search Report and Written Opinion, issued in International Application No. PCT/US2013/060225, dated May 27, 2014. |
| PCT International Search Report and Written Opinion, issued in International Application No. PCT/US2014/040340, dated Oct. 31, 2014. |
| PCT International Search Report and Written Opinion, issued in International Application No. PCT/US2014/068462, dated May 22, 2015. |
| PCT International Search Report and Written Opinion, issued in International Application No. PCT/US2015/014672, dated Jul. 6, 2015. |
| PCT International Search Report and Written Opinion, issued in International Application No. PCT/US2015/025472, dated Sep. 4, 2015. |
| PCT International Search Report and Written Opinion, issued in International Application No. PCT/US2015/051107 dated Aug. 5, 2016. |
| PCT International Search Report and Written Opinion, issued in International Application No. PCT/US2016/049706 dated Nov. 29, 2016. |
| Extended European Search Report issued in European Application No. 13871010.8 dated Sep. 2, 2016. |
| PCT International Search Report and Written Opinion, issued in International Application No. PCT/US2017/022150 dated Jun. 9, 2017. |
| Extended European Search Report issued in European Application No. 14803880.5 dated May 19, 2017. |
| PCT International Search Report and Written Opinion, issued in International Application No. PCT/US2017/042286, dated Sep. 28, 2017. |
| Supplementary European Search Report issued in European Application No. 15 77 6544 dated Oct. 20, 2017. |
| USPTO Office Action in U.S. Appl. No. 14/660,704 dated Feb. 7, 2018. |
| Extended European Search Report issued in European Application No. 15746146.8 dated Feb. 27, 2018. |
| USPTO Office Action in U.S. Appl. No. 14/660,704 dated Jun. 28, 2018. |
| USPTO Office Action in U.S. Appl. No. 14/660,704 dated Nov. 8, 2018. |
| Number | Date | Country | |
|---|---|---|---|
| 20160346156 A1 | Dec 2016 | US |
| Number | Date | Country | |
|---|---|---|---|
| 61936162 | Feb 2014 | US |
