US20120259430A1 - Controlling powered human augmentation devices - Google Patents
Controlling powered human augmentation devices Download PDFInfo
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- US20120259430A1 US20120259430A1 US13/349,216 US201213349216A US2012259430A1 US 20120259430 A1 US20120259430 A1 US 20120259430A1 US 201213349216 A US201213349216 A US 201213349216A US 2012259430 A1 US2012259430 A1 US 2012259430A1
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
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- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
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- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
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- G—PHYSICS
- G05—CONTROLLING; REGULATING
- G05B—CONTROL OR REGULATING SYSTEMS IN GENERAL; FUNCTIONAL ELEMENTS OF SUCH SYSTEMS; MONITORING OR TESTING ARRANGEMENTS FOR SUCH SYSTEMS OR ELEMENTS
- G05B13/00—Adaptive control systems, i.e. systems automatically adjusting themselves to have a performance which is optimum according to some preassigned criterion
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- G05B13/0205—Adaptive control systems, i.e. systems automatically adjusting themselves to have a performance which is optimum according to some preassigned criterion electric not using a model or a simulator of the controlled system
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Abstract
In a communication system for controlling a powered human augmentation device, a parameter of the powered device is adjusted within a gait cycle by wirelessly transmitting a control signal thereto, whereby the adjusted parameter falls within a target range corresponding to that parameter. The target range is selected and the device parameters are controlled such that the powered device can normalize or augment human biomechanical function, responsive to a wearer's activity, regardless of speed and terrain and, in effect, provides at least a biomimetic response to the wearer of the powered device.
Description
- This application claims priority to and the benefit of U.S. Provisional Patent Application Ser. No. 61/432,093, filed on Jan. 12, 2011, the entire content of which is hereby incorporated by reference in its entirety.
- This invention relates generally to powered human augmentation devices, such as lower-extremity prosthetic orthotic, or exoskelton apparatus, designed to emulate human biomechanics and to normalize function, components thereof, and methods for controlling the same.
- Approximately 65% of service members seriously injured in Iraq and Afghanistan sustain injuries to their extremities. Many of these individuals experience muscle tissue loss and/or nerve injury, resulting in the loss of limb function or substantial reduction thereof. Injuries to the lower leg can be particularly devastating, due to the critical importance of the ankle in providing support for body position and in propelling the body forward economically during common functions, such as level-ground walking and the ascent and descent of stairs and slopes.
- Increasingly, robotic technology is employed in the treatment of individuals suffering from physical disability, either for the advancement of therapy tools or as permanent assistive devices. An important class of robotic devices provides therapy to the arms of stroke patients. Additionally, lower-extremity robotic devices have been developed for the enhancement of locomotor function. Although decades of research has been conducted in the area of active permanent assistive devices for the treatment of lower-extremity pathology, many of these devices are not designed to produce a biomimetic response, generally described in terms of joint torque, joint angle, and other related parameters as observed in a human not having substantial muscle tissue injury and not using any device to assist in ambulation. Therefore, these robotic devices may cause discomfort to the wearer. The commercially available ankle-foot orthotic devices are generally passive, non-adaptive devices.
- Some powered prosthetic and orthotic devices have been described in co-pending U.S. patent application Ser. No. 12/157,727 “Powered Ankle-Foot Prosthesis” filed on Jun. 12, 2008 (Publication No. US2011/0257764 A1); co-pending U.S. patent application Ser. No. 12/552,013 “Hybrid Terrain-Adaptive Lower-Extremity Systems” filed on Sep. 1, 2009 (Publication No. US2010/0179668 A1); co-pending U.S. patent application Ser. No. 13/079564 “Controlling Power in a Prosthesis or Orthosis Based on Predicted Walking Speed or Surrogate for Same” filed on Apr. 4, 2011; co-pending U.S. patent application Ser. No. 13/079571 “Controlling Torque in a Prosthesis or Orthosis Based on a Deflection of Series Elastic Element” filed on Apr. 4, 2011; and co-pending U.S. patent application Ser. No. 13/347443 “Powered Joint Orthosis” filed on Jan. 10, 2012. These powered devices are adopted to provide at least a biomimetic response and can eliminate or mitigate slapping of the foot after heel strike (foot slap) and dragging of the toe during swing (toe drag). In general, a biomimetic response refers to a range of responses from humans and can vary according to the wearer of the powered device and the nature and environment of the wearer's activity. As such, even the powered devices described above need to be tailored or calibrated to the wearer so as to reliably provide a biomimetic response. Therefore, there is a need for systems and methods of controlling permanent assistive devices for the treatment of lower-extremity pathology to achieve optimal wearer comfort and satisfaction.
- In various embodiments, the present invention provides systems and methods that can dynamically control a powered prosthetic/orthotic human augmentation device, such that the device can provide and maintain at least a biomimetic response during the wearer's activity. This is achieved, in part, by recording within a gait cycle typical ranges of various ambulation-related parameters in humans not having substantial muscle tissue injury and not using any device to assist in ambulation. A user interface is provided that enables an operator, the wearer, or another person to adjust various parameters of the powered device such that the response of the powered device, as described in terms of the ambulation-related parameters, is substantially similar to the recorded ranges of those parameters, i.e., at least biomimetic. These adjustments may be carried out in a training mode, during actual use, or both. The parameters of the powered device may also be adjusted or modified according to the wearer's characteristics, such as weight, desired walking speed, etc. and/or according to ambulation patterns, such as slow walking, walking in incomplete steps or shuffling, etc. Moreover, the parameters of the powered device may also be adjusted or modified according to terrain and activity, e.g., walking upslope, downslope, ascending and/or descending stairs, etc. Accordingly, a biomimetic response of the powered prosthetic/orthotic device can be maintained throughout the duration of the wearer's activity, regardless of terrain, walking speed, etc.
- In one aspect, embodiments of the invention feature a method of controlling a powered human augmentation device. The method includes adjusting a parameter of the powered device within a gait cycle by wirelessly transmitting a control signal thereto. After adjustment based on the control signal, the adjusted parameter falls within a target range corresponding to that parameter, providing at least a biomimetic response to a wearer of the powered device. The parameter may be net work, toe-off angle, peak power applied by the powered device, or timing of the peak power relative to the gait cycle. In some embodiments, more than one or even all of these parameters are adjusted. The target range corresponding to the parameter may be a function of ambulation speed and/or ambulation pattern. The adjusting step may also be based, at least in part, on one or more of the ambulation speed, ambulation pattern, terrain, and activity. The activity may include walking on level ground, walking on uneven ground, walking upslope, walking downslope, ascending stairs, and/or descending stairs.
- In some embodiments, the adjusting step is related to one or more of weight of the wearer, early-stance stiffness, power applied by the powered device, timing of application of power, hard-stop sensitivity, and a speed threshold for low-power mode of the powered device. The adjusted parameter may also include a gain in a positive force-feedback control loop that can adjust the power applied by the powered device and/or an exponent in a positive force-feedback that can adjust the timing of the application of power.
- In some embodiments, the method includes the step of receiving a data signal from the powered device, such that adjusting the parameter is based at least in part on the received data signal. The received data signal may be related to one or more of rate of plantar flexion, heel rise, and ambulation-step length. The control signal may be transmitted during a training mode, a use mode, or both. The method may also include the step of storing the transmitted control signal for subsequent retransmission thereof.
- In another aspect, a communication system for interfacing with a powered human augmentation device includes a wireless transmitter for adjusting a parameter of the powered device. The parameter is adjusted within a gait cycle by transmitting a control signal to the powered device, such that the adjusted parameter falls within a target range corresponding to that parameter. This provides at least a biomimetic response to a wearer of the powered device.
- The parameter may be net work, toe-off angle, peak power applied by the powered device, or timing of the peak power relative to the gait cycle. In some embodiments, more than one or even all of these parameters are adjusted. The target range corresponding to the parameter may be a function of ambulation speed and/or ambulation pattern. The adjustment of the parameter may also be based, at least in part, on one or more of the ambulation speed, ambulation pattern, terrain, and activity. The activity may include walking on level ground, walking on uneven ground, walking upslope, walking downslope, ascending stairs, and/or descending stairs.
- In some embodiments, the parameter adjustment is related to one or more of weight of the wearer, early-stance stiffness, power applied by the powered device, timing of application of power, hard-stop sensitivity, and a speed threshold for low-power mode of the powered device. The adjusted parameter may also include a gain in a positive force-feedback control loop that can adjust the power applied by the powered device and/or an exponent in a positive force-feedback that can adjust the timing of the application of power.
- In some embodiments, the communication system includes a receiver for receiving a data signal from the powered device, such that adjusting the parameter is based at least in part on the received data signal. The received data signal may be related to one or more of rate of plantar flexion, heel rise, and ambulation-step length. The control signal may be transmitted during a training mode, a use mode, or both. The communication may also store the transmitted control signal for subsequent retransmission thereof.
- The powered augmentation device may be a prosthetic device or an orthotic device, such as an exoskeleton. In some embodiments, the wireless transmitter is adapted to transmit the control signal to a second powered human augmentation device. The wireless transmitter may include a transmitter of a mobile device, and the mobile device can be a cell phone, a personal digital assistant, or a tablet PC.
- In yet another aspect, various embodiments feature an article of manufacture, including a non-transitory machine-readable medium storing instructions. The instructions, when executed by a processor, configure the processor to adjust a parameter of the powered device within a gait cycle by wirelessly transmitting a control signal thereto. After adjustment based on the control signal, the adjusted parameter falls within a target range corresponding to that parameter, providing at least a biomimetic response to a wearer of the powered device.
- These and other objects, along with advantages and features of the embodiments of the present invention herein disclosed, will become more apparent through reference to the following description, the accompanying drawings, and the claims. Furthermore, it is to be understood that the features of the various embodiments described herein are not mutually exclusive and can exist in various combinations and permutations. As used herein, the term “substantially” means±10% and, in some embodiments, ±5%.
- In the drawings, like reference characters generally refer to the same parts throughout the different views. Also, the drawings are not necessarily to scale, emphasis instead generally being placed upon illustrating the principles of the invention. In the following description, various embodiments of the present invention are described with reference to the following drawings, in which:
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FIG. 1 depicts an exemplary prosthetic device and a communication system according to one embodiment; -
FIGS. 2 a-2 d depict various joint parameters within a gait cycle, describing respective biomimetic responses; -
FIGS. 3 a-3 e depict steps of adjusting various parameters of a powered device according to one embodiment; and -
FIG. 4 shows various parameters of a powered device that may be adjusted, and the ranges of those parameters, according to one embodiment. - The entire contents of each of U.S. patent application Ser. No. 12/157,727 “Powered Ankle-Foot Prosthesis” filed on Jun. 12, 2008 (Publication No. US2011/0257764 A1); U.S. patent application Ser. No. 12/552,013 “Hybrid Terrain-Adaptive Lower-Extremity Systems” filed on Sep. 1, 2009 (Publication No. US2010/0179668 A1); U.S. patent application Ser. No. 13/079564 “Controlling Power in a Prosthesis or Orthosis Based on Predicted Walking Speed or Surrogate for Same” filed on Apr. 4, 2011; U.S. patent application Ser. No. 13/079571 “Controlling Torque in a Prosthesis or Orthosis Based on a Deflection of Series Elastic Element” filed on Apr. 4, 2011; and U.S. patent application Ser. No. 13/347443 “Powered Joint Orthosis” filed on Jan. 10, 2012 are incorporated herein by reference.
FIG. 1 shows aBiOM™ Ankle 102, a powered prosthetic ankle available from iWalk, Inc. (Bedford, Mass.), and asmart phone 104 for controlling/tuning various parameters of theBiOM Ankle 102. Thesmart phone 104 includes atransmitter 106 for sending one or more control signals to theBiOM Ankle 102, whereby one or more parameters of theBiOM Ankle 102 can be adjusted. Thesmart phone 104 also includes areceiver 108 for receiving parameter values as data signals from theBiOM Ankle 102 which has a corresponding transmitter and receiver capability. These data signals can be used to adjust the values of the corresponding and/or other parameters of theBiOM Ankle 102. To facilitate convenient adjustment of various parameters, theBiOM Ankle 102 provides a user interface that includes a software application and firmware. The software application, implemented in Java for the Android 2.1 Operating System, may be run on thesmart phone 104. The software application builds a packet structure that is sent out over Android's Bluetooth hardware interface. Corresponding software on theBiOM Ankle 102, written in C and stored in the firmware of theBiOM Ankle 102, receives commands from the same packet structure, and adjusts the operation of theBiOM Ankle 102 accordingly. - It should be understood that the
BiOM Ankle 102 and thesmart phone 104 are illustrative only and, in general, a powered human augmentation device can be any powered prosthetic, orthotic and/or exoskeleton device that can assist in ankle, knee, and/or hip function. Uses in other joint devices are also contemplated. The communication system, in general, can be any mobile communication device capable of communicating with the powered device. Exemplary mobile communication devices include smart phones, personal digital assistants (PDAs, such as a BlackBerry), tablet computers, etc. The communication between the communication system and the powered device may be established via wireless link such as Bluetooth, WiFi, etc., or via a wired link. The software applications run on theBiOM Ankle 102 and thesmart phone 104 may also be written in any other programming languages and/or may be provided as circuitry. - Various parameters of the BiOM Ankle 102 (or in any powered human augmentation device, in general) are controlled using the
smart phone 104, such that theBiOM Ankle 102 produces at least a biomimetic response. Such a response may enable a wearer of the powered device to ambulate in a natural manner, e.g., in a manner in which a typical human not using a powered device walks (i.e., slowly or briskly), ascends/descends stairs, etc. In addition to enabling ambulation with a natural feel, a powered device producing at least a biomimetic response can also decrease stress on other body parts of the human, e.g., on knees and hips while using theBiOM Ankle 102. As a result, net metabolic cost of transport to the wearer can be minimized. - In one embodiment, a biomimetic response of a human can be characterized by four parameters, namely, net work, toe-off angle, peak power, and peak-power timing. Each of these parameters varies according to the human's ambulation speed. Net work is the time integral of mechanical power applied by the powered device (e.g., the BiOM Ankle 102) during one ambulation step (i.e., gait cycle).
FIG. 2 a shows that for typical humans, who do not have injured muscle tissue and do not use a powered augmentation device, the net work normalized according to the human's weight varies according to the walking speed, but stays within a certain range. For example, at a walking speed of about 1.5 m/s, the normalized net work may be in the range of about 0.1-0.25 J/kg, and at a walking speed of about 2 m/s the normalized net work may be in the range of about 0.2-0.4 J/kg. - A net-work response of a powered augmentation device is biomimetic if the net work produced by the device remains within a range corresponding to the ambulation speed, i.e., substantially within the dashed
lines lines smart phone 104, (as described below), such that the net work is adjusted to fall within a desired range. -
FIG. 2 b depicts a relationship between the toe-off angle and walking speed for a typical human. If the toe-off angle while using a powered augmentation device is not substantially the same as that indicated by the dashedline 206, the foot may not be plantarflexing sufficiently. Therefore, one or more parameters of the powered device (e.g., BiOM Ankle 102) may be tuned using thesmart phone 104. -
FIGS. 2 c and 2 d depict the peak power delivered by a typical human and timing within a gait cycle at which the peak power is delivered, respectively. If the peak power to the ankle (a joint, in general) delivered by a powered augmentation device does not fall within the range indicated by the dashedlines line 212, the peak power may be delivered too early, i.e., significantly before the time at which the powered plantar flexion state of the gait cycle begins. In this case, the wearer might feel that the ankle is lifting up but not pushing/propelling forward sufficiently. On the other hand, if the powered augmentation device delivers the peak power at a time substantially greater than that indicated by theline 212, the peak power may be delivered too late, i.e., significantly after the time at which the powered plantar flexion state of the gait cycle begins. In this case, the wearer might feel that the ankle is pushing forward but not lifting up sufficiently. - In any of the scenarios describe above, unlike a typical human, the wearer may not receive adequate power to the ankle at the time of toe off, resulting in unnatural ambulation. Therefore, one or more parameters of the powered device may be adjusted such that at a certain ambulation speed the peak power applied by the device remains substantially within the range indicated by the dashed
lines line 212. - In general, by tuning one or more parameters of the powered augmentation device using a communication system, each of the net work, toe-off angle, peak power, and peak power timing can be adjusted, such that the powered device delivers at least a biomimetic response to the wearer. In some instances, the parameters such as the peak power and peak power timing can be adjusted directly. In other instances, other related parameters, e.g., heel stiffness, are adjusted using the communication system, which in turn causes an adjustment of the parameters described with reference to
FIGS. 2 a-2 d. - With reference to
FIGS. 3 a-3 e, in anexemplary tuning process 300, a communication system (phone for convenience, hereafter) scans for a powered augmentation device within the phone's range, instep 302. When any such devices are located, one of them may be selected and a Bluetooth connection is established with that device instep 304, pairing the phone with the selected powered device. In general, the phone can be paired with more then one powered devices. Instep 306, the wearer's ID and weight are entered and the transmitter of the phone may supply the weight to the paired power device by sending a control signal thereto. The wearer's weight may range from about 100 lbs up to about 300 lbs. Various parameters of the powered device adjusted subsequently may be adjusted according to the wearer's weight. - In
step 308, a powered ankle device is tuned by selecting “Tune Ankle.” In other embodiments, other joints such as knee or hip may be tuned alternatively or in addition. Instep 310, the wearer walks at a self-selected walking speed (SSWS), and an operator i.e., the wearer himself/herself or another person (clinician, researcher, etc.) adjusts “stiffness,” e.g., by gradually increasing it from zero. In response, the rate of plantar flexion may change, which is observed by the operator, or the wearer may inform it to the operator. In some embodiments, a sensor of the powered device may sense the rate of plantar flexion and may transmit a corresponding data signal to the phone. The phone may then display the sensed rate to the operator. In thestep 308, the operator adjusts the stiffness so as to achieve a desired rate of plantar flexion which, in turn, adjusts one or more of the net work, toe-off angle, peak power, and peak power timing. - In
step 312, the power applied by the powered augmentation device is adjusted by asking the wearer to walk at SSWS. The operator gradually increases the power from an initial value (e.g., zero percent) until the wearer verifies that powered plantar flexion is engaged correctly, i.e., adequate power is received approximately at the time the ankle dorsiflexion is at a maximum level. Increasing (decreasing) the power may include increasing (decreasing) a gain parameter in a positive-feedback system of the powered device that delivers the power. In some embodiments, correct engagement of the powered plantar flexion can be verified by analyzing various sensors signals detected by the powered augmentation device and transmitted to the communication system as data signals. The received data signals may relate to parameters such as heel rise, walking-step length, and tracking performed during the swing phase. The operator may also manually (e.g., visually) compare values of these parameters with their values corresponding to a previous power setting, so as to identify the power setting that results in at least a biomimetic response as described above and/or the wearer's preference. - The timing at which peak power is applied by the powered augmentation device (e.g., the
BiOM Ankle 102 shown inFIG. 1 ) is adjusted instep 314 by asking the wearer to walk at SSWS. The operator adjusts the “Power Trigger” timing such that power is delivered at terminal stance, i.e., approximately at the time the ankle dorsiflexion is at a maximum level. Adjusting the power timing may include adjusting an exponent parameter in a positive-feedback system that delivers the power. Whether the timing is correct may be verified by the wearer. The operator may also verify that gait cycle is balanced and that a desired knee flexion is maintained during stance. Alternatively, or in addition, data signals corresponding to various parameters of the powered device may be received therefrom, and used to guide adjustment of the power trigger. Adjusting the timing of application peak power enables timely powered plantar flexion at toe off. This adjustment can also allow the wearer to take a full step using the leg having any injured muscle tissue. - When a wearer prefers to walk at a speed slower than the SSWS, the parameters of the powered device may be readjusted, to provide a biomimetic response corresponding to the slower speed, in part, and also to conserve battery life, in part. To this end, in
step 316, the wearer is asked to walk at a slower speed, and the power is adjusted down from an initial value (e.g., 100%) which may be the power setting for the SSWS, to a “slow-walk mode” setting. The power may be adjusted according to the wearer's preference and/or according to parameters such as heel rise, walking-step length, and tracking performed during the swing phase. The values of these parameters may be received from the powered device as data signals and/or may be observed by the operator similarly as described in thestep 310. - The slow-walk mode can also be used to adjust parameters according to the wearer's ambulation pattern, e.g., when the wearer does not take full steps or shuffles. In the
step 318, a threshold at which the BiOM Ankle's slow-walk mode, also called “low-power” mode engages can also be adjusted. In addition to conserving battery life, the slow-walk mode setting can increase walking efficiency at a slower speed and can also enhance the real-time response of the ankle. - In
step 320, the hard-stop sensitivity of the powered device can be adjusted. The hard stop corresponds to the wearer's walking speed, and the maximum dorsiflexion angle embodied within the design of the powered device. Generally, the small angular displacements that occur after engagement of the hard-stop are used to estimate ankle torque. This torque is an important input to the positive force feedback. By slightly changing this torque model parameter, an increased or decreased reflex torque adjustment can be made which is particularly useful for slow walking performance. The hard-stop sensitivity can be increased such that the powered device delivers more power (e.g., compared to the power setting for the SSWS) early in the gait cycle, and the hard-stop sensitivity can be decreased such that relatively less power is delivered later in the gait cycle. - The communication device can also facilitate adapting the powered device to terrain and/or the wearer's activity. For example, power and/or timing of peak power can be adjusted to provide additional power when the wearer is walking upslope. These adjustment can be made as described with reference to the
steps - In
step 328, the various device parameters adjusted in any of these steps can be saved for subsequent use. The tuning/adjusting described above may be performed in a training mode in one or more training sessions. More than one sets of settings, each set corresponding to one training session, may be saved for each joint (ankle, knee, hip, etc.), and may be restored during a subsequent use. The tuning/adjusting described above may also be performed during actual use of the powered device. - The ranges of various parameters described above with reference to
FIGS. 3 a-3 e according to one embodiment are shown in a Table inFIG. 4 . The Table shows additional parameters of the powered device that may be adjusted, so as to achieve and maintain at least a biomimetic response, and typical ranges of those parameters. It should be understood that the parameters shown in the Table are illustrative, and that according to some embodiments fewer or additional parameters may be controlled. Some other embodiments may control different parameters, and/or the typical ranges within which the parameters can be set may be different. - Accordingly, various embodiments of the invention may be used to initially set up or tune an augmentation device at the time of manufacture and commissioning to achieve a biomimetic response, on an individual employed as a model for this purpose. The device can then be fitted to the end user and the device further adjusted to tailor the device to that individual. As described, achieving a biomimetic response is a primary objective, in order to order to normalize user function and satisfaction. However, the methods and systems according to various embodiments of the invention may be used to achieve a greater than biomimetic response, or vary one or more of the response parameters as desired by the user or the user's physician, therapist, or clinician. Naturally, as will be understood, changes in a user's weight, strength, endurance or other physical condition may require further monitoring and adjustment of the device over time. Accordingly, the systems and associated methods may be utilized on regular time intervals or whenever a change to user or device occurs that warrants checking.
- While the invention has been particularly shown and described with reference to specific embodiments, it will be understood by those skilled in the art that various changes in form and detail may be made therein without departing from the spirit and scope of the invention as defined by the appended claims. The scope of the invention is thus indicated by the appended claims and all changes that come within the meaning and range of equivalency of the claims are therefore intended to be embraced.
Claims (31)
1. A method of controlling a powered human augmentation device, the method comprising:
adjusting a parameter of the powered device within a gait cycle by wirelessly transmitting a control signal thereto, whereby the adjusted parameter falls within a target range corresponding to that parameter, providing at least a biomimetic response to a wearer of the powered device.
2. The method of claim 1 , wherein the parameter is selected from the group consisting of net work, toe-off angle, peak power applied by the powered device, and timing of the peak power relative to the gait cycle.
3. The method of claim 1 , wherein the target range corresponding to the parameter is a function of at least one of ambulation speed and ambulation pattern.
4. The method of claim 1 , wherein the adjusting step is based at least in part on at least one of ambulation speed and ambulation pattern.
5. The method of claim 1 , wherein the adjusting step is based at least in part on at least one of terrain and activity.
6. The method of claim 5 , wherein the activity is selected from the group consisting of walking on level ground, walking on uneven ground, walking upslope, walking downslope, ascending stairs, and descending stairs.
7. The method of claim 1 , wherein the adjusting step is related to at least one of weight of the wearer, early-stance stiffness, power applied by the powered device, timing of application of power, hard-stop sensitivity, and a speed threshold for low-power mode of the powered device.
8. The method of claim 7 , wherein the adjusted parameter comprises a gain in a positive force-feedback, whereby the power applied by the powered device is adjusted.
9. The method of claim 7 , wherein the adjusted parameter comprises an exponent in a positive force-feedback, whereby the timing of the application of power is adjusted.
10. The method of claim 1 further comprising the step of receiving a data signal from the powered device, whereby adjusting the parameter is based at least in part on the received data signal.
11. The method of claim 10 , wherein the received data signal is related to at least one of rate of plantarflexion, heel rise, and ambulation-step length.
12. The method of claim 1 , wherein the control signal is transmitted during at least one of a training mode and a use mode.
13. The method of claim 1 further comprising the step of storing the transmitted control signal for subsequent retransmission thereof.
14. A communication system for interfacing with a powered human augmentation device, the system comprising:
a wireless transmitter for adjusting a parameter of the powered device within a gait cycle by transmitting a control signal thereto, whereby the adjusted parameter falls within a target range corresponding to that parameter, providing at least a biomimetic response to a wearer of the powered device.
15. The system of claim 14 , wherein the parameter is selected from the group consisting of net work, toe-off angle, peak power applied by the powered device, and timing of the peak power relative to the gait cycle.
16. The system of claim 14 , wherein the target range corresponding to the parameter is a function of at least one of ambulation speed and ambulation pattern.
17. The system of claim 14 , wherein adjusting the parameter is based at least in part on at least one of ambulation speed and ambulation pattern.
18. The system of claim 14 , wherein adjusting the parameter is based at least in part on at least one of terrain and activity.
19. The system of claim 18 , wherein the activity is selected from the group consisting of walking on level ground, walking on uneven ground, walking upslope, walking downslope, ascending stairs, and descending stairs.
20. The system of claim 14 , wherein adjusting the parameter is related to at least one of weight of the wearer, early-stance stiffness, power applied by the powered device, timing of application of power, hard-stop sensitivity, and a speed threshold for low-power mode of the powered device.
21. The system of claim 20 , wherein the adjusted parameter comprises a gain in a positive force-feedback, whereby the power applied by the powered device is adjusted.
22. The system of claim 20 , wherein the adjusted parameter comprises an exponent in a positive force-feedback, whereby the timing of the application of power is adjusted.
23. The system of claim 14 , further comprising a receiver for receiving a data signal from the powered device, wherein adjusting the parameter is based at least in part on the received data signal.
24. The system of claim 23 , wherein the received data signal is related to at least one of rate of plantarflexion, heel rise, ambulation-step length.
25. The system of claim 14 , wherein the control signal is transmitted during at least one of a training mode and a use mode.
26. The system of claim 14 , wherein the wireless transmitter is adapted to store the transmitted control signal for subsequent retransmission thereof.
27. The system of claim 14 , wherein the powered augmentation device is selected from the group consisting of a prosthetic device and an orthotic device.
28. The system of claim 14 , wherein the wireless transmitter is adapted to transmit the control signal to a second powered human augmentation device.
29. The system of claim 14 , wherein the wireless transmitter comprises a transmitter of a mobile device.
30. The system of claim 29 , wherein the mobile device is selected from the group consisting of a cell phone, a personal digital assistant, and a tablet PC.
31. An article of manufacture, comprising a non-transitory machine-readable medium storing instructions that, when executed by a processor, configure the processor to:
adjust a parameter of the powered device within a gait cycle by wirelessly transmitting a control signal thereto, whereby the adjusted parameter falls within a target range corresponding to that parameter, providing at least a biomimetic response to a wearer of the powered device.
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Cited By (20)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8551184B1 (en) | 2002-07-15 | 2013-10-08 | Iwalk, Inc. | Variable mechanical-impedance artificial legs |
US8900325B2 (en) | 2008-09-04 | 2014-12-02 | Iwalk, Inc. | Hybrid terrain-adaptive lower-extremity systems |
US20150089455A1 (en) * | 2013-09-26 | 2015-03-26 | Fujitsu Limited | Gesture input method |
WO2016168463A1 (en) * | 2015-04-14 | 2016-10-20 | Ekso Bionics, Inc. | Methods of exoskeleton communication and control |
US9693883B2 (en) | 2010-04-05 | 2017-07-04 | Bionx Medical Technologies, Inc. | Controlling power in a prosthesis or orthosis based on predicted walking speed or surrogate for same |
US9737419B2 (en) | 2011-11-02 | 2017-08-22 | Bionx Medical Technologies, Inc. | Biomimetic transfemoral prosthesis |
US20170273853A1 (en) * | 2016-03-25 | 2017-09-28 | Kabushiki Kaisha Yaskawa Denki | Controller for motion assisting apparatus, motion assisting apparatus, method for controlling motion assisting apparatus, and recording medium |
US10195057B2 (en) | 2004-02-12 | 2019-02-05 | össur hf. | Transfemoral prosthetic systems and methods for operating the same |
US10251762B2 (en) | 2011-05-03 | 2019-04-09 | Victhom Laboratory Inc. | Impedance simulating motion controller for orthotic and prosthetic applications |
US10285828B2 (en) | 2008-09-04 | 2019-05-14 | Bionx Medical Technologies, Inc. | Implementing a stand-up sequence using a lower-extremity prosthesis or orthosis |
US10390974B2 (en) | 2014-04-11 | 2019-08-27 | össur hf. | Prosthetic foot with removable flexible members |
US10405996B2 (en) | 2007-01-19 | 2019-09-10 | Victhom Laboratory Inc. | Reactive layer control system for prosthetic and orthotic devices |
US10531965B2 (en) | 2012-06-12 | 2020-01-14 | Bionx Medical Technologies, Inc. | Prosthetic, orthotic or exoskeleton device |
US10543109B2 (en) | 2011-11-11 | 2020-01-28 | Össur Iceland Ehf | Prosthetic device and method with compliant linking member and actuating linking member |
US10575970B2 (en) | 2011-11-11 | 2020-03-03 | Össur Iceland Ehf | Robotic device and method of using a parallel mechanism |
US10639170B2 (en) | 2015-11-11 | 2020-05-05 | Samsung Electronics Co., Ltd. | Torque output timing adjustment method and apparatus |
US10695197B2 (en) | 2013-03-14 | 2020-06-30 | Össur Iceland Ehf | Prosthetic ankle and method of controlling same based on weight-shifting |
US10940027B2 (en) | 2012-03-29 | 2021-03-09 | Össur Iceland Ehf | Powered prosthetic hip joint |
US11007072B2 (en) | 2007-01-05 | 2021-05-18 | Victhom Laboratory Inc. | Leg orthotic device |
US11285024B2 (en) | 2013-02-26 | 2022-03-29 | Össur Iceland Ehf | Prosthetic foot with enhanced stability and elastic energy return |
Families Citing this family (9)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20140172120A1 (en) * | 2012-09-06 | 2014-06-19 | Freedom Innovations, Llc | Method and system for a prosthetic device with multiple levels of functionality enabled through multiple control systems |
US9517561B2 (en) * | 2014-08-25 | 2016-12-13 | Google Inc. | Natural pitch and roll |
KR102161310B1 (en) | 2014-11-26 | 2020-09-29 | 삼성전자주식회사 | Method and apparatus for setting assistant torque |
CN110928203B (en) * | 2019-11-21 | 2021-08-06 | 苏宁智能终端有限公司 | Wearable terminal and shutdown method thereof |
US11298287B2 (en) | 2020-06-02 | 2022-04-12 | Dephy, Inc. | Systems and methods for a compressed controller for an active exoskeleton |
US11148279B1 (en) | 2020-06-04 | 2021-10-19 | Dephy, Inc. | Customized configuration for an exoskeleton controller |
US11147733B1 (en) | 2020-06-04 | 2021-10-19 | Dephy, Inc. | Systems and methods for bilateral wireless communication |
US11389367B2 (en) | 2020-06-05 | 2022-07-19 | Dephy, Inc. | Real-time feedback-based optimization of an exoskeleton |
US11173093B1 (en) | 2020-09-16 | 2021-11-16 | Dephy, Inc. | Systems and methods for an active exoskeleton with local battery |
Citations (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20050251079A1 (en) * | 2004-05-06 | 2005-11-10 | Carvey Matthew R | Metabolically efficient leg brace |
US20060184280A1 (en) * | 2005-02-16 | 2006-08-17 | Magnus Oddsson | System and method of synchronizing mechatronic devices |
US20080039756A1 (en) * | 2006-06-30 | 2008-02-14 | Freygardur Thorsteinsson | Intelligent orthosis |
US20100179668A1 (en) * | 2008-09-04 | 2010-07-15 | Iwalk, Inc. | Hybrid Terrain-Adaptive Lower-Extremity Systems |
Family Cites Families (247)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US2529968A (en) | 1948-06-15 | 1950-11-14 | Sartin Hansel | Mechanism for artificial legs |
US2489291A (en) | 1948-07-09 | 1949-11-29 | Ulrich K Henschke | Leg prosthesis |
US3098645A (en) | 1961-01-11 | 1963-07-23 | Walter J Owens | Laminated torsion bar suspension |
US3207497A (en) | 1963-07-02 | 1965-09-21 | Dura Corp | Torsion spring assembly |
US3844279A (en) | 1973-05-14 | 1974-10-29 | R Konvalin | Adjustable leg brace |
US4463291A (en) | 1979-12-31 | 1984-07-31 | Andale Company | Automatic control system and valve actuator |
US4921293A (en) | 1982-04-02 | 1990-05-01 | The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration | Multi-fingered robotic hand |
US4442390A (en) | 1982-07-06 | 1984-04-10 | Davis Kenneth W | Feedback system for a linear actuator |
US4518307A (en) | 1982-09-29 | 1985-05-21 | The Boeing Company | Compliant robot arm adapter assembly |
IN161427B (en) | 1983-05-12 | 1987-11-28 | Westinghouse Brake & Signal | |
IN160902B (en) | 1983-05-12 | 1987-08-15 | Westinghouse Brake & Signal | |
IN161426B (en) | 1983-05-12 | 1987-11-28 | Westinghouse Brake & Signal | |
US4546296A (en) | 1983-05-12 | 1985-10-08 | Westinghouse Brake & Signal | Electric actuators |
US4546298A (en) | 1983-05-12 | 1985-10-08 | Westinghouse Brake & Signal Co. | Electric actuators |
US4569352A (en) | 1983-05-13 | 1986-02-11 | Wright State University | Feedback control system for walking |
CA1276710C (en) | 1983-11-30 | 1990-11-20 | Kazuo Asakawa | Robot force controlling system |
US4600357A (en) | 1984-02-21 | 1986-07-15 | Heath Company | Gripper force sensor/controller for robotic arm |
US4657470A (en) | 1984-11-15 | 1987-04-14 | Westinghouse Electric Corp. | Robotic end effector |
SE454943B (en) | 1986-06-26 | 1988-06-13 | Ossur Hf | ACCESSORIES, SPECIAL FOR AMPUTATION STUMP |
JP2645004B2 (en) | 1987-02-27 | 1997-08-25 | 株式会社東芝 | Control device for multi-degree-of-freedom manipulator |
JPS6471686A (en) | 1987-09-09 | 1989-03-16 | Komatsu Mfg Co Ltd | Flexible arm robot |
US4865376A (en) | 1987-09-25 | 1989-09-12 | Leaver Scott O | Mechanical fingers for dexterity and grasping |
JPH02502990A (en) | 1988-01-20 | 1990-09-20 | ムーグ インコーポレーテツド | Vehicle suspension system and how it works |
US4921393A (en) | 1988-03-09 | 1990-05-01 | Sri International | Articulatable structure with adjustable end-point compliance |
US4843921A (en) | 1988-04-18 | 1989-07-04 | Kremer Stephen R | Twisted cord actuator |
US5088478A (en) | 1988-05-10 | 1992-02-18 | Royce Medical Company | Gel and air cushion ankle brace |
USRE34661E (en) | 1988-05-10 | 1994-07-12 | Royce Medical Company | Gel and air cushion ankle brace |
US4964402A (en) | 1988-08-17 | 1990-10-23 | Royce Medical Company | Orthopedic device having gel pad with phase change material |
US5062673A (en) | 1988-12-28 | 1991-11-05 | Kabushiki Kaisha Toyota Chuo Kenkyusho | Articulated hand |
US5252102A (en) | 1989-01-24 | 1993-10-12 | Electrobionics Corporation | Electronic range of motion apparatus, for orthosis, prosthesis, and CPM machine |
US4923475A (en) | 1989-02-21 | 1990-05-08 | Gosthnian Barry M | Inflatable limb prosthesis with preformed inner surface |
US5112295A (en) | 1990-04-20 | 1992-05-12 | Zinner Norman R | Penile prosthesis and method |
US5049797A (en) | 1990-07-02 | 1991-09-17 | Utah State University Foundation | Device and method for control of flexible link robot manipulators |
US5092902A (en) | 1990-08-16 | 1992-03-03 | Mauch Laboratories, Inc. | Hydraulic control unit for prosthetic leg |
US6071313A (en) | 1991-02-28 | 2000-06-06 | Phillips; Van L. | Split foot prosthesis |
US5181933A (en) | 1991-02-28 | 1993-01-26 | Phillips L Van | Split foot prosthesis |
US5701686A (en) | 1991-07-08 | 1997-12-30 | Herr; Hugh M. | Shoe and foot prosthesis with bending beam spring structures |
US5367790A (en) | 1991-07-08 | 1994-11-29 | Gamow; Rustem I. | Shoe and foot prosthesis with a coupled spring system |
US5383939A (en) | 1991-12-05 | 1995-01-24 | James; Kelvin B. | System for controlling artificial knee joint action in an above knee prosthesis |
JPH05216504A (en) | 1992-02-06 | 1993-08-27 | Fanuc Ltd | Adaptive sliding mode control system for control object including spring system |
US5327790A (en) | 1992-06-19 | 1994-07-12 | Massachusetts Institute Of Technology | Reaction sensing torque actuator |
US5294873A (en) | 1992-10-27 | 1994-03-15 | The United States Of America As Represented By The Administrator Of The National Aeronautics And Space Administration | Kinematic functions for redundancy resolution using configuration control |
US5358513A (en) | 1992-12-09 | 1994-10-25 | Medtronic, Inc. | Parameter selection and electrode placement of neuromuscular electrical stimulation apparatus |
US5405409A (en) | 1992-12-21 | 1995-04-11 | Knoth; Donald E. | Hydraulic control unit for prosthetic leg |
US5443521A (en) | 1992-12-21 | 1995-08-22 | Mauch Laboratories, Inc. | Hydraulic control unit for prosthetic leg |
US5329705A (en) | 1993-02-16 | 1994-07-19 | Royce Medical Company | Footgear with pressure relief zones |
US5456341A (en) | 1993-04-23 | 1995-10-10 | Moog Inc. | Method and apparatus for actively adjusting and controlling a resonant mass-spring system |
DE69434390T2 (en) | 1993-07-09 | 2006-04-27 | Kinetecs, Inc. | EXERCISE DEVICE AND TECHNOLOGY |
US5476441A (en) | 1993-09-30 | 1995-12-19 | Massachusetts Institute Of Technology | Controlled-brake orthosis |
US5502363A (en) | 1994-01-04 | 1996-03-26 | University Of Maryland-Baltimore County | Apparatus for controlling angular positioning and stiffness modulations of joint of robotic manipulator |
US5458143A (en) | 1994-06-09 | 1995-10-17 | Herr; Hugh M. | Crutch with elbow and shank springs |
US6206934B1 (en) | 1998-04-10 | 2001-03-27 | Flex-Foot, Inc. | Ankle block with spring inserts |
US6144385A (en) | 1994-08-25 | 2000-11-07 | Michael J. Girard | Step-driven character animation derived from animation data without footstep information |
US5662693A (en) | 1995-06-05 | 1997-09-02 | The United States Of America As Represented By The Secretary Of The Air Force | Mobility assist for the paralyzed, amputeed and spastic person |
US5650704A (en) | 1995-06-29 | 1997-07-22 | Massachusetts Institute Of Technology | Elastic actuator for precise force control |
US5748845A (en) | 1995-07-31 | 1998-05-05 | Motorola, Inc. | FES method and system for controlling the movement of a limb |
US5643332A (en) | 1995-09-20 | 1997-07-01 | Neuromotion Inc. | Assembly for functional electrical stimulation during movement |
US6056712A (en) | 1995-10-31 | 2000-05-02 | Grim; Tracy E. | Multi-functional orthosis for the foot, heel, ankle and lower leg |
US5718925A (en) | 1995-11-15 | 1998-02-17 | Ossur Hf. | Apparatus for making a prosthesis socket |
US7311686B1 (en) | 1995-12-28 | 2007-12-25 | Ossur Hf | Molded orthopaedic devices |
DK0799894T3 (en) | 1996-02-09 | 2004-08-09 | Degussa | Process for the preparation of (S) -cyanhydrins |
US5888212A (en) | 1997-06-26 | 1999-03-30 | Mauch, Inc. | Computer controlled hydraulic resistance device for a prosthesis and other apparatus |
US6113642A (en) | 1996-06-27 | 2000-09-05 | Mauch, Inc. | Computer controlled hydraulic resistance device for a prosthesis and other apparatus |
US7288076B2 (en) | 1996-08-29 | 2007-10-30 | Ossur Hf | Self-equalizing resilient orthopaedic support |
US5898948A (en) | 1996-10-31 | 1999-05-04 | Graham M. Kelly | Support/sport sock |
US6064912A (en) | 1997-03-28 | 2000-05-16 | Kenney; John P. | Orthotic/electrotherapy for treating contractures due to immobility |
US6136039A (en) | 1997-05-06 | 2000-10-24 | Ossur Hf | Dual durometer silicone liner for prosthesis |
US5932230A (en) | 1997-05-20 | 1999-08-03 | Degrate; Frenchell | Topical analgesic formulation containing fruits, oils and aspirin |
US6202806B1 (en) | 1997-10-29 | 2001-03-20 | Lord Corporation | Controllable device having a matrix medium retaining structure |
BR9909656A (en) | 1998-03-17 | 2001-10-16 | Gary S Kochamba | Method and apparatus for stabilizing tissue |
US6067892A (en) | 1998-03-18 | 2000-05-30 | Erickson; Joel R. | Artificial muscle actuator assembly |
AU3487999A (en) | 1998-04-10 | 1999-11-01 | Van L. Phillips | Coil spring shock module prosthesis |
US6511512B2 (en) | 1998-04-10 | 2003-01-28 | Ossur Hf | Active shock module prosthesis |
US6517503B1 (en) | 1998-09-18 | 2003-02-11 | Becker Orthopedic Appliance Company | Orthosis knee joint |
US6267742B1 (en) | 1998-09-29 | 2001-07-31 | Brown Medical Industries | Biplanar foot dorsiflexion collapsible posterior splint |
JP2000145914A (en) | 1998-11-17 | 2000-05-26 | Tsubakimoto Chain Co | Bearing linear actuator with backstop mechanism |
AU758948B2 (en) | 1999-03-01 | 2003-04-03 | Ossur Hf | Multiple section orthotic or prosthetic sleeve of varying elasticity |
US6666796B1 (en) | 1999-09-16 | 2003-12-23 | Aerovironment, Inc. | Walking assisting apparatus |
FI110159B (en) | 1999-12-17 | 2002-12-13 | Respecta Oy | Lower extremity prosthesis |
ES2247057T3 (en) | 2000-01-20 | 2006-03-01 | Massachusetts Institute Of Technology | ELECTRONICALLY CONTROLLED KNEE PROTESIS. |
US6706364B2 (en) | 2000-03-14 | 2004-03-16 | Ossur Hf | Composite elastic material |
KR20030011074A (en) | 2000-03-15 | 2003-02-06 | 오서 에이치에프 | Apparatus and process for making prosthetic suction sleeve |
DE60131377T2 (en) | 2000-03-29 | 2008-09-04 | Massachusetts Institute Of Technology, Cambridge | SPEED ADAPTED AND PATIENT ATTACHED KNEE PROSTHESIS |
US6811571B1 (en) | 2000-05-02 | 2004-11-02 | Van L. Phillips | Universal prosthesis with cushioned ankle |
US20030195439A1 (en) | 2000-05-30 | 2003-10-16 | Caselnova Ronald J. | Thermal pad and boot designed for applying hot or cold treatment |
GB2368017B (en) | 2000-06-20 | 2004-05-12 | Bournemouth University Higher | Apparatus for electrical stimulation of the leg |
US6923834B2 (en) | 2000-10-04 | 2005-08-02 | Ossur Hf | Artificial limb socket containing volume control pad |
CA2424407A1 (en) | 2000-10-04 | 2002-04-11 | Ossur Hf | Prosthetic socket and socket component assembly |
DE60142451D1 (en) | 2000-10-26 | 2010-08-05 | Ossur North America Inc | FUSES WITH FEDUCED ANKLE |
US6702076B2 (en) | 2001-01-16 | 2004-03-09 | Michael T. Koleda | Shaft vibration damping system |
US6443993B1 (en) | 2001-03-23 | 2002-09-03 | Wayne Koniuk | Self-adjusting prosthetic ankle apparatus |
US7153242B2 (en) | 2001-05-24 | 2006-12-26 | Amit Goffer | Gait-locomotor apparatus |
JP3760186B2 (en) | 2001-06-07 | 2006-03-29 | 独立行政法人科学技術振興機構 | Biped walking type moving device, walking control device thereof, and walking control method |
US6752774B2 (en) | 2001-06-08 | 2004-06-22 | Townsend Design | Tension assisted ankle joint and orthotic limb braces incorporating same |
US7650204B2 (en) | 2001-06-29 | 2010-01-19 | Honda Motor Co., Ltd. | Active control of an ankle-foot orthosis |
DE10142491B4 (en) | 2001-08-30 | 2004-10-07 | össur h.f. | Sealing arrangement with lips for a prosthetic socket |
DE10142492A1 (en) | 2001-08-30 | 2003-04-03 | Carstens Orthopaedie Und Mediz | Prosthetic socket with seal |
WO2003033070A1 (en) | 2001-10-16 | 2003-04-24 | Case Western Reserve University | Neural prosthesis |
US6921376B2 (en) | 2001-10-23 | 2005-07-26 | The Jerome Group, Inc. | Cervical brace |
DE10164892B4 (en) | 2001-11-05 | 2009-08-27 | össur h.f. | Stocking liner for use with a cup-shaped prosthesis stem |
JP3790816B2 (en) | 2002-02-12 | 2006-06-28 | 国立大学法人 東京大学 | Motion generation method for humanoid link system |
US6992455B2 (en) | 2002-02-15 | 2006-01-31 | Sony Corporation | Leg device for leg type movable robot, and method of controlling leg type movable robot |
JP2003236783A (en) | 2002-02-18 | 2003-08-26 | Japan Science & Technology Corp | Bipedal walking transfer device |
JP4182726B2 (en) | 2002-02-20 | 2008-11-19 | 日本精工株式会社 | Linear actuator |
JP3976129B2 (en) | 2002-02-28 | 2007-09-12 | 本田技研工業株式会社 | Parallel link mechanism and artificial joint device using the same |
US7029500B2 (en) | 2002-04-12 | 2006-04-18 | James Jay Martin | Electronically controlled prosthetic system |
US20090030530A1 (en) | 2002-04-12 | 2009-01-29 | Martin James J | Electronically controlled prosthetic system |
EP2106886B1 (en) | 2002-04-26 | 2011-03-23 | Honda Giken Kogyo Kabushiki Kaisha | Self-position estimating device for leg type movable robots |
AU2002306091A1 (en) | 2002-05-06 | 2003-11-17 | Somas Groep B.V. | Drop foot device |
EP1539028A2 (en) | 2002-07-08 | 2005-06-15 | Ossur Engineering Inc. | Socket liner incorporating sensors to monitor amputee progress |
US20040064195A1 (en) | 2002-07-15 | 2004-04-01 | Hugh Herr | Variable-mechanical-impedance artificial legs |
US7597674B2 (en) | 2002-07-23 | 2009-10-06 | össur hf | Versatile orthopaedic leg mounted walker |
US7303538B2 (en) | 2002-07-23 | 2007-12-04 | Ossur Hf | Versatile orthopaedic leg mounted walkers |
US7094058B2 (en) | 2002-08-16 | 2006-08-22 | Ossur Hf | Educational prosthesis device and method for using the same |
US7736394B2 (en) | 2002-08-22 | 2010-06-15 | Victhom Human Bionics Inc. | Actuated prosthesis for amputees |
KR100690909B1 (en) | 2002-08-22 | 2007-03-09 | 빅톰 휴먼 바이오닉스 인크. | Actuated Leg Prosthesis for Above-knee Amputees |
JP4129862B2 (en) | 2002-08-30 | 2008-08-06 | 本田技研工業株式会社 | Prosthetic joint device |
AU2002951193A0 (en) | 2002-09-04 | 2002-09-19 | Northern Sydney Area Health Service | Movement faciliatation device |
US7105122B2 (en) | 2002-10-08 | 2006-09-12 | Ossur Hf | Prosthesis socket direct casting device having multiple compression chambers |
US7094212B2 (en) | 2002-10-11 | 2006-08-22 | Ossur Hf | Rigid dressing |
US7037283B2 (en) | 2002-10-18 | 2006-05-02 | Ossur Hf | Casting product and method for forming the same |
EP1558333B1 (en) | 2002-10-24 | 2007-05-23 | Lockheed Martin Corporation | System for treating movement disorders |
AU2003290526A1 (en) | 2002-11-07 | 2004-06-03 | Ossur Hf | Ankle-foot orthosis |
US6966882B2 (en) | 2002-11-25 | 2005-11-22 | Tibion Corporation | Active muscle assistance device and method |
US7025793B2 (en) | 2002-12-20 | 2006-04-11 | Ossur Hf | Suspension liner with seal |
US8034120B2 (en) | 2002-12-20 | 2011-10-11 | Ossur Hf | Suspension liner system with seal |
US7909884B2 (en) | 2002-12-20 | 2011-03-22 | Ossur Hf | Suspension liner system with seal |
US7304202B2 (en) | 2002-12-31 | 2007-12-04 | Ossur Hf | Wound dressing |
US7295892B2 (en) | 2002-12-31 | 2007-11-13 | Massachusetts Institute Of Technology | Speed-adaptive control scheme for legged running robots |
US7465281B2 (en) | 2003-04-18 | 2008-12-16 | Ossur, Hf | Versatile hardenable cast or support |
US7101487B2 (en) | 2003-05-02 | 2006-09-05 | Ossur Engineering, Inc. | Magnetorheological fluid compositions and prosthetic knees utilizing same |
US7198071B2 (en) | 2003-05-02 | 2007-04-03 | Össur Engineering, Inc. | Systems and methods of loading fluid in a prosthetic knee |
JP4315766B2 (en) | 2003-05-21 | 2009-08-19 | 本田技研工業株式会社 | Walking assist device |
US7427297B2 (en) | 2003-06-20 | 2008-09-23 | Ossur Hf | Prosthetic socket with self-contained vacuum reservoir |
US8007544B2 (en) | 2003-08-15 | 2011-08-30 | Ossur Hf | Low profile prosthetic foot |
US20050049652A1 (en) | 2003-08-25 | 2005-03-03 | Kai-Yu Tong | Functional electrical stimulation system |
US7266910B2 (en) | 2003-09-05 | 2007-09-11 | Ossur Hf | Orthotic footplate |
WO2005025464A2 (en) | 2003-09-11 | 2005-03-24 | The Cleveland Clinic Foundation | Apparatus for assisting body movement |
US7531711B2 (en) | 2003-09-17 | 2009-05-12 | Ossur Hf | Wound dressing and method for manufacturing the same |
DK1675536T3 (en) | 2003-09-17 | 2016-04-18 | Bsn Medical Gmbh | WOUND COMPOUND AND PROCEDURE FOR PREPARING IT |
US8075633B2 (en) * | 2003-09-25 | 2011-12-13 | Massachusetts Institute Of Technology | Active ankle foot orthosis |
US7534220B2 (en) | 2003-09-29 | 2009-05-19 | Ossur Hf | Adjustable ergonomic brace |
US6969408B2 (en) | 2003-09-30 | 2005-11-29 | Ossur Engineering, Inc. | Low profile active shock module prosthesis |
SE526430C2 (en) | 2003-10-17 | 2005-09-13 | Oessur Hf | Artificial multi-axis knee joint |
US20070282480A1 (en) | 2003-11-10 | 2007-12-06 | Pannese Patrick D | Methods and systems for controlling a semiconductor fabrication process |
US7107180B2 (en) | 2003-11-14 | 2006-09-12 | Ossur Hf | Method and system for determining an activity level in an individual |
US20050107889A1 (en) | 2003-11-18 | 2005-05-19 | Stephane Bedard | Instrumented prosthetic foot |
US7637959B2 (en) | 2004-02-12 | 2009-12-29 | össur hf | Systems and methods for adjusting the angle of a prosthetic ankle based on a measured surface angle |
AU2005215769B2 (en) | 2004-02-12 | 2012-01-19 | Ossur Hf. | System and method for motion-controlled foot unit |
WO2005087144A2 (en) * | 2004-03-10 | 2005-09-22 | össur hf | Control system and method for a prosthetic knee |
USD503480S1 (en) | 2004-04-22 | 2005-03-29 | Ossur Hf | Ankle-foot orthosis |
US7217060B2 (en) | 2004-04-30 | 2007-05-15 | Ossur Hf | Prosthesis locking assembly |
US7455696B2 (en) | 2004-05-07 | 2008-11-25 | össur hf | Dynamic seals for a prosthetic knee |
US7581454B2 (en) | 2004-05-28 | 2009-09-01 | össur hf | Method of measuring the performance of a prosthetic foot |
US7347877B2 (en) | 2004-05-28 | 2008-03-25 | össur hf | Foot prosthesis with resilient multi-axial ankle |
USD503802S1 (en) | 2004-05-28 | 2005-04-05 | Ossur Hf | Prosthesis liner |
CN100450460C (en) | 2004-05-28 | 2009-01-14 | 奥苏尔公司 | Prosthetic or orthotic sleeve having external surface peripheral profiles |
US7429253B2 (en) | 2004-09-21 | 2008-09-30 | Honda Motor Co., Ltd. | Walking assistance system |
US7762973B2 (en) | 2004-12-22 | 2010-07-27 | Ossur Hf | Spacer element for prosthetic and orthotic devices |
US7198610B2 (en) | 2004-12-22 | 2007-04-03 | Ossur Hf | Knee brace and method for securing the same |
US7896827B2 (en) | 2004-12-22 | 2011-03-01 | Ossur Hf | Knee brace and method for securing the same |
US7713225B2 (en) | 2004-12-22 | 2010-05-11 | Ossur Hf | Knee brace and method for securing the same |
US7794418B2 (en) | 2004-12-22 | 2010-09-14 | Ossur Hf | Knee brace and method for securing the same |
US7597675B2 (en) | 2004-12-22 | 2009-10-06 | össur hf | Knee brace and method for securing the same |
EP1848380B1 (en) | 2004-12-22 | 2015-04-15 | Össur hf | Systems and methods for processing limb motion |
US7465283B2 (en) | 2005-01-12 | 2008-12-16 | Ossur, Hf | Cast assembly with breathable double knit type padding |
US7513881B1 (en) | 2005-01-12 | 2009-04-07 | Ossur Hf | Knee immobilizer |
US7161056B2 (en) | 2005-01-28 | 2007-01-09 | Ossur Hf | Wound dressing and method for manufacturing the same |
CN101155557B (en) | 2005-02-02 | 2012-11-28 | 奥瑟Hf公司 | Sensing systems and methods for monitoring gait dynamics |
EP1843823B1 (en) * | 2005-02-02 | 2016-10-26 | Össur hf | Prosthetic and orthotic systems usable for rehabilitation |
US20070162152A1 (en) | 2005-03-31 | 2007-07-12 | Massachusetts Institute Of Technology | Artificial joints using agonist-antagonist actuators |
US20060249315A1 (en) | 2005-03-31 | 2006-11-09 | Massachusetts Institute Of Technology | Artificial human limbs and joints employing actuators, springs, and variable-damper elements |
US7313463B2 (en) | 2005-03-31 | 2007-12-25 | Massachusetts Institute Of Technology | Biomimetic motion and balance controllers for use in prosthetics, orthotics and robotics |
US20070123997A1 (en) | 2005-03-31 | 2007-05-31 | Massachusetts Institute Of Technology | Exoskeletons for running and walking |
US8500823B2 (en) | 2005-03-31 | 2013-08-06 | Massachusetts Institute Of Technology | Powered artificial knee with agonist-antagonist actuation |
US20070043449A1 (en) | 2005-03-31 | 2007-02-22 | Massachusetts Institute Of Technology | Artificial ankle-foot system with spring, variable-damping, and series-elastic actuator components |
US10080672B2 (en) | 2005-03-31 | 2018-09-25 | Bionx Medical Technologies, Inc. | Hybrid terrain-adaptive lower-extremity systems |
DE602006005915D1 (en) | 2005-04-12 | 2009-05-07 | Honda Motor Co Ltd | ACTIVE CONTROL OF A FUSSGELENKORTHESE |
US7240876B2 (en) | 2005-04-21 | 2007-07-10 | Ossur, Hf | Dispenser box |
NL1029086C2 (en) | 2005-05-20 | 2006-11-27 | Somas Groep B V | Hip portese, method for preventing hip dislocation and use of a hip portese. |
USD523149S1 (en) | 2005-05-24 | 2006-06-13 | Ossur Hf | Prosthetic or orthotic sleeve |
JP4332136B2 (en) | 2005-06-03 | 2009-09-16 | 本田技研工業株式会社 | Limb body assist device and limb body assist program |
WO2007008803A2 (en) | 2005-07-11 | 2007-01-18 | Ossur Hf | Energy returing prosthetic joint |
US7531006B2 (en) | 2005-09-01 | 2009-05-12 | össur hf | Sensing system and method for motion-controlled foot unit |
US8048172B2 (en) | 2005-09-01 | 2011-11-01 | össur hf | Actuator assembly for prosthetic or orthotic joint |
US7431708B2 (en) | 2005-09-19 | 2008-10-07 | Ossur Hf | Knee brace having lateral/medial width adjustment |
US7959589B2 (en) | 2005-09-19 | 2011-06-14 | Ossur Hf | Adjustable orthotic device |
CA2624989C (en) | 2005-10-12 | 2014-12-23 | Ossur Hf | Knee brace with posterior hinge |
US7449005B2 (en) | 2005-11-07 | 2008-11-11 | Ossur Hf. | Traction collar and method of use |
USD527825S1 (en) | 2005-12-21 | 2006-09-05 | Ossur Hf | Knee brace |
USD529180S1 (en) | 2006-03-01 | 2006-09-26 | Ossur Hf | Knee brace |
EP1991180B1 (en) * | 2006-03-09 | 2012-09-05 | The Regents of the University of California | Power generating leg |
USD533280S1 (en) | 2006-03-22 | 2006-12-05 | Ossur Hf | Wrist brace |
US7914475B2 (en) | 2006-03-22 | 2011-03-29 | Ossur Hf | Orthopedic brace |
US7488349B2 (en) | 2006-03-24 | 2009-02-10 | Ossur Hf | Ventilated prosthesis system |
US7438843B2 (en) | 2006-06-30 | 2008-10-21 | Ossur Hf | Method and kit for making prosthetic socket |
US7662191B2 (en) | 2006-06-30 | 2010-02-16 | össur hf | Liner donning and doffing device |
US7503937B2 (en) | 2006-07-03 | 2009-03-17 | Ossur Hf | Prosthetic foot |
US7632315B2 (en) | 2006-10-10 | 2009-12-15 | össur hf | Vacuum chamber socket system |
US7842848B2 (en) | 2006-11-13 | 2010-11-30 | Ossur Hf | Absorbent structure in an absorbent article |
US7552021B2 (en) * | 2006-12-07 | 2009-06-23 | Step Of Mind Ltd. | Device and method for improving human motor function |
DE102006059206B4 (en) | 2006-12-13 | 2010-12-30 | Otto Bock Healthcare Gmbh | Orthopedic device |
US7985265B2 (en) | 2006-12-14 | 2011-07-26 | Chas. A. Blatchford & Sons Limited | Prosthetic ankle and foot combination |
USD567072S1 (en) | 2007-02-12 | 2008-04-22 | Ossur Hf | Strap retainer |
WO2008100486A2 (en) | 2007-02-12 | 2008-08-21 | Ossur Hf | Orthopedic brace and component for use therewith |
USD558884S1 (en) | 2007-02-12 | 2008-01-01 | Ossur Hf | Knee brace |
US8021317B2 (en) | 2007-04-26 | 2011-09-20 | Ossur Hf | Orthopedic device providing access to wound site |
US7868511B2 (en) | 2007-05-09 | 2011-01-11 | Motor Excellence, Llc | Electrical devices using disk and non-disk shaped rotors |
EP2151039A1 (en) | 2007-05-09 | 2010-02-10 | Motor Excellence, LLC | Generators using electromagnetic rotors |
US20080294083A1 (en) | 2007-05-21 | 2008-11-27 | Julia Chang | Orthopedic device |
USD576781S1 (en) | 2007-07-03 | 2008-09-16 | Ossur Hf | Orthotic device |
US8657772B2 (en) | 2007-07-20 | 2014-02-25 | össur hf. | Wearable device having feedback characteristics |
US7935068B2 (en) | 2007-08-23 | 2011-05-03 | Ossur Hf | Orthopedic or prosthetic support device |
US8043244B2 (en) | 2007-09-13 | 2011-10-25 | Ossur Hf | Wearable device |
CN101827568A (en) | 2007-10-15 | 2010-09-08 | 奥索集团公司 | Orthopedic device having a patient compliance system |
USD583956S1 (en) | 2007-12-11 | 2008-12-30 | Ossur, Hf | Orthotic device |
KR101718345B1 (en) | 2007-12-26 | 2017-03-21 | 렉스 바이오닉스 리미티드 | Mobility aid |
USD588753S1 (en) | 2008-02-12 | 2009-03-17 | Ossur Hf | Patella protector assembly |
WO2009120637A1 (en) | 2008-03-24 | 2009-10-01 | Ossur Hf | Transfemoral prosthetic systems and methods for operating the same |
US8652218B2 (en) * | 2008-04-21 | 2014-02-18 | Vanderbilt University | Powered leg prosthesis and control methodologies for obtaining near normal gait |
USD596301S1 (en) | 2008-04-25 | 2009-07-14 | Ossur Hf | Orthopedic device |
WO2009139893A1 (en) | 2008-05-15 | 2009-11-19 | Ossur Hf | Circumferential walker |
CN102112334B (en) | 2008-07-31 | 2013-06-26 | F3&I2有限责任公司 | Modular panels for enclosures |
CN102196785B (en) | 2008-08-28 | 2014-02-26 | 雷神公司 | A biomimetic mechanical joint |
USD611322S1 (en) | 2008-09-09 | 2010-03-09 | össur hf | Handle |
USD627079S1 (en) | 2008-09-09 | 2010-11-09 | Ossur Hf | Container |
CN102227196B (en) | 2008-12-03 | 2013-09-11 | 欧苏尔公司 | Cervical collar having height and circumferential adjustment |
USD628696S1 (en) | 2009-08-28 | 2010-12-07 | Ossur Hf | Handle |
USD629115S1 (en) | 2009-08-28 | 2010-12-14 | Ossur Hf | Back brace |
USD616555S1 (en) | 2009-09-14 | 2010-05-25 | Ossur Hf | Orthopedic device |
USD620124S1 (en) | 2009-09-14 | 2010-07-20 | Ossur Hf | Orthopedic device |
USD616997S1 (en) | 2009-09-14 | 2010-06-01 | Ossur Hf | Orthopedic device |
USD616996S1 (en) | 2009-09-14 | 2010-06-01 | Ossur Hf | Orthopedic device |
USD618359S1 (en) | 2009-09-14 | 2010-06-22 | Ossur Hf | Expansion part for orthopedic device |
USD643537S1 (en) | 2009-09-22 | 2011-08-16 | Ossur Hf | Pump for an orthopedic device |
USD616556S1 (en) | 2009-09-22 | 2010-05-25 | Ossur Hf | Orthopedic device |
USD634852S1 (en) | 2009-09-22 | 2011-03-22 | Ossur Hf | Sole for orthopedic device |
USD640380S1 (en) | 2009-11-13 | 2011-06-21 | Ossur Hf | Rehabilitative vest component |
USD646394S1 (en) | 2009-11-13 | 2011-10-04 | Ossur Hf | Rehabilitative vest component |
USD640381S1 (en) | 2009-11-13 | 2011-06-21 | Ossur Hf | Rehabilitative vest component |
USD641482S1 (en) | 2010-05-25 | 2011-07-12 | Ossur Hf | Orthosis component |
USD641483S1 (en) | 2010-05-25 | 2011-07-12 | Ossur Hf | Orthosis component |
USD634438S1 (en) | 2010-06-14 | 2011-03-15 | Ossur Hf | Orthopedic walker |
USD647624S1 (en) | 2010-08-06 | 2011-10-25 | Ossur Hf | Cervical collar |
USD647623S1 (en) | 2010-08-06 | 2011-10-25 | Ossur Hf | Height adjustment mechanism for cervical collar |
USD647622S1 (en) | 2010-08-20 | 2011-10-25 | Ossur Hf | Orthopedic device |
USD637942S1 (en) | 2010-08-20 | 2011-05-17 | Ossur Hf | Strap retainer |
-
2012
- 2012-01-12 US US13/349,216 patent/US20120259430A1/en not_active Abandoned
- 2012-01-12 WO PCT/US2012/021084 patent/WO2012097156A2/en active Application Filing
- 2012-01-12 EP EP12701403.3A patent/EP2663904A2/en not_active Ceased
-
2013
- 2013-11-26 US US14/090,359 patent/US10537449B2/en active Active
-
2020
- 2020-01-09 US US16/738,273 patent/US20200146849A1/en not_active Abandoned
Patent Citations (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20050251079A1 (en) * | 2004-05-06 | 2005-11-10 | Carvey Matthew R | Metabolically efficient leg brace |
US20060184280A1 (en) * | 2005-02-16 | 2006-08-17 | Magnus Oddsson | System and method of synchronizing mechatronic devices |
US20080039756A1 (en) * | 2006-06-30 | 2008-02-14 | Freygardur Thorsteinsson | Intelligent orthosis |
US20100179668A1 (en) * | 2008-09-04 | 2010-07-15 | Iwalk, Inc. | Hybrid Terrain-Adaptive Lower-Extremity Systems |
Cited By (36)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US8551184B1 (en) | 2002-07-15 | 2013-10-08 | Iwalk, Inc. | Variable mechanical-impedance artificial legs |
US10195057B2 (en) | 2004-02-12 | 2019-02-05 | össur hf. | Transfemoral prosthetic systems and methods for operating the same |
US11007072B2 (en) | 2007-01-05 | 2021-05-18 | Victhom Laboratory Inc. | Leg orthotic device |
US11607326B2 (en) | 2007-01-19 | 2023-03-21 | Victhom Laboratory Inc. | Reactive layer control system for prosthetic devices |
US10405996B2 (en) | 2007-01-19 | 2019-09-10 | Victhom Laboratory Inc. | Reactive layer control system for prosthetic and orthotic devices |
US10299943B2 (en) | 2008-03-24 | 2019-05-28 | össur hf | Transfemoral prosthetic systems and methods for operating the same |
US9351856B2 (en) | 2008-09-04 | 2016-05-31 | Iwalk, Inc. | Hybrid terrain-adaptive lower-extremity systems |
US9554922B2 (en) | 2008-09-04 | 2017-01-31 | Bionx Medical Technologies, Inc. | Hybrid terrain-adaptive lower-extremity systems |
US9211201B2 (en) | 2008-09-04 | 2015-12-15 | Iwalk, Inc. | Hybrid terrain-adaptive lower-extremity systems |
US10285828B2 (en) | 2008-09-04 | 2019-05-14 | Bionx Medical Technologies, Inc. | Implementing a stand-up sequence using a lower-extremity prosthesis or orthosis |
US10105244B2 (en) | 2008-09-04 | 2018-10-23 | Bionx Medical Technologies, Inc. | Hybrid terrain-adaptive lower-extremity systems |
US8900325B2 (en) | 2008-09-04 | 2014-12-02 | Iwalk, Inc. | Hybrid terrain-adaptive lower-extremity systems |
US9693883B2 (en) | 2010-04-05 | 2017-07-04 | Bionx Medical Technologies, Inc. | Controlling power in a prosthesis or orthosis based on predicted walking speed or surrogate for same |
US10406002B2 (en) | 2010-04-05 | 2019-09-10 | Bionx Medical Technologies, Inc. | Controlling torque in a prosthesis or orthosis based on a deflection of series elastic element |
US11185429B2 (en) | 2011-05-03 | 2021-11-30 | Victhom Laboratory Inc. | Impedance simulating motion controller for orthotic and prosthetic applications |
US10251762B2 (en) | 2011-05-03 | 2019-04-09 | Victhom Laboratory Inc. | Impedance simulating motion controller for orthotic and prosthetic applications |
US9737419B2 (en) | 2011-11-02 | 2017-08-22 | Bionx Medical Technologies, Inc. | Biomimetic transfemoral prosthesis |
US10575970B2 (en) | 2011-11-11 | 2020-03-03 | Össur Iceland Ehf | Robotic device and method of using a parallel mechanism |
US10543109B2 (en) | 2011-11-11 | 2020-01-28 | Össur Iceland Ehf | Prosthetic device and method with compliant linking member and actuating linking member |
US10940027B2 (en) | 2012-03-29 | 2021-03-09 | Össur Iceland Ehf | Powered prosthetic hip joint |
US10531965B2 (en) | 2012-06-12 | 2020-01-14 | Bionx Medical Technologies, Inc. | Prosthetic, orthotic or exoskeleton device |
US11285024B2 (en) | 2013-02-26 | 2022-03-29 | Össur Iceland Ehf | Prosthetic foot with enhanced stability and elastic energy return |
US11576795B2 (en) | 2013-03-14 | 2023-02-14 | össur hf | Prosthetic ankle and method of controlling same based on decreased loads |
US10695197B2 (en) | 2013-03-14 | 2020-06-30 | Össur Iceland Ehf | Prosthetic ankle and method of controlling same based on weight-shifting |
US20150089455A1 (en) * | 2013-09-26 | 2015-03-26 | Fujitsu Limited | Gesture input method |
US9639164B2 (en) * | 2013-09-26 | 2017-05-02 | Fujitsu Limited | Gesture input method |
US11446166B2 (en) | 2014-04-11 | 2022-09-20 | Össur Iceland Ehf | Prosthetic foot with removable flexible members |
US10390974B2 (en) | 2014-04-11 | 2019-08-27 | össur hf. | Prosthetic foot with removable flexible members |
US20180092536A1 (en) * | 2015-04-14 | 2018-04-05 | Ekso Bionics, Inc. | Methods of Exoskeleton Communication and Control |
US10694948B2 (en) * | 2015-04-14 | 2020-06-30 | Ekso Bionics | Methods of exoskeleton communication and control |
WO2016168463A1 (en) * | 2015-04-14 | 2016-10-20 | Ekso Bionics, Inc. | Methods of exoskeleton communication and control |
CN107847389A (en) * | 2015-04-14 | 2018-03-27 | 埃克苏仿生公司 | Ectoskeleton communicates and the method for control |
US10639170B2 (en) | 2015-11-11 | 2020-05-05 | Samsung Electronics Co., Ltd. | Torque output timing adjustment method and apparatus |
US20170273853A1 (en) * | 2016-03-25 | 2017-09-28 | Kabushiki Kaisha Yaskawa Denki | Controller for motion assisting apparatus, motion assisting apparatus, method for controlling motion assisting apparatus, and recording medium |
US10603241B2 (en) * | 2016-03-25 | 2020-03-31 | Kabushiki Kaisha Yaskawa Denki | Controller for motion assisting apparatus, motion assisting apparatus, method for controlling motion assisting apparatus, and recording medium |
CN107440888A (en) * | 2016-03-25 | 2017-12-08 | 株式会社安川电机 | The control device of action assisting device, action assisting device, the control method of action assisting device |
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WO2012097156A3 (en) | 2012-09-20 |
EP2663904A2 (en) | 2013-11-20 |
WO2012097156A2 (en) | 2012-07-19 |
US10537449B2 (en) | 2020-01-21 |
US20140088727A1 (en) | 2014-03-27 |
US20200146849A1 (en) | 2020-05-14 |
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