• 专利附录
  • 专利说明
  • 权利要求
  • 类似技术
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    • 专利摘要:
    Exoskeleton for assistance to the human movement. The present invention relates to an exoskeleton for assistance to human movement adjustable to the user in dimensions, tensions and joint ranges, this adjustment can be manual or automatic, where its placement in the user can be in the anterioposterior direction in the sagittal plane, being able placed from lying or sitting without the need for functional transfer, where the exoskeleton presents a modular design, compatible with human biomechanics and that reproduces a natural and physiological movement in the user, with up to 7 degrees of mobility actuated and controlled by limb, guaranteeing the stability of the user's balance during locomotion. (Machine-translation by Google Translate, not legally binding)
    公开号:ES2575255A1
    申请号:ES201431763
    申请日:2014-11-27
    公开日:2016-06-27
    发明作者:Elena García Armada；Manuel Javier CESTARI SOTO；Daniel SANZ MERODIO；Xavier CARRILLO DE HIJES
    申请人:Marsi Bionics Sl；Marsi Bionics S L；Consejo Superior de Investigaciones Cientificas CSIC；Universidad Politecnica de Madrid；
    IPC主号:
    专利说明:

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    EXO SKELETON FOR HUMAN MOVEMENT ASSISTANCE
    D E S C R I P C I O N
    OBJECT OF THE INVENTION
    The present invention relates to an exoskeleton for assistance to the human movement adjustable to the user in dimensions, tensions and articular ranges, being this manual or automatic adjustment, where its placement in the user can be from the front to the back in the anterior-posterior direction in the sagittal plane, being able to be placed from lying down or sitting without the need for functional transfer from the user to the exoskeleton.
    The object of the invention is an exoskeleton for assistance to the human movement that has a modular design, compatible with human biomechanics and that reproduces a natural and physiological movement in the user, with up to 7 degrees of mobility operated and controlled by limb, guaranteeing the stability of the user's balance during locomotion without using auxiliary support elements.
    BACKGROUND OF THE INVENTION
    People with disabling neurological conditions, such as spinal injuries, neuromuscular diseases, cerebral palsy, etc., suffer partial or total mobility impairment and in many cases have sensory involvement. The mobility disorder affects the functional independence to perform the activities of daily life, and negatively affects various basic physiological functions causing, among others, urinary and fecal incontinence, sexual dysfunction and cardiovascular problems. The social impact often involves the loss of employment, the separation of the couple, among others. The set also affects the self-esteem of the person and causes severe psychological problems.
    Neurological rehabilitation pursues muscular reeducation and gait training, using orthoses, canes, crutches, walkers and other orthopedic devices. The rehabilitation methods can be improved using active orthotic devices, based on the robotization of passive orthoses by actuating their joints with controlled motors to generate the natural movement of the gait
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    human These devices may be limited to movement on a mobile belt, as part of the rehabilitation machinery of a hospital center, or they may be portable, allowing in the latter case the daily rehabilitation at home, and even ideally it could replace the chair of wheels in daily life, allowing to recover basic physiological functions, and even facilitating the patient's labor and social reinsertion.
    These last devices, portable active braces, or also called wearable exoskeletons (Wearable Exoskeleton), are mechanical devices, formed by rigid segments joined together by motorized joints that are attached to the limbs of a user by means of generally rigid back clamps, manufactured tailored to the patient, and attached to the user's extremities with velcro straps or buckles. The mechanical structure is usually made to fit a patient and lacks flexibility for use in other patients or even in the same user when the disease has significantly evolved. They are therefore non-transferable and short-term use devices. Using automatic motor control techniques, these exoskeletons are controlled to generate joint movement equivalent to that of a healthy person, and transmit said movement to the limb to which they are attached. The source of energy needed to power the motors and electronics must be included on board and usually placed on the back of the device, which is usually an obstacle to sitting or lying down with the exoskeleton, apart from significantly making it difficult to recharge or replace the battery
    One of the main technological challenges faced by wearable exoskeletons is to find the compromise between a light and low-volume structure that facilitates the handling by a user, who usually has muscular weakness, and on the other hand a robotic system that implement a physiologically complete biomechanical model. The second is achieved by increasing the number of degrees of mobility of the robotic structure, to resemble the human biomechanical model, but the weight and volume that the actuators and transmission systems are printing to the structure is multiplied with the number of active joints and the The result is a mechanical structure that is too heavy to be functional. The question is, as long as actuators are not developed with the high power / weight ratio required to achieve this double objective, which of them should prevail. Obviously, if it involves developing devices that allow neuromuscular rehabilitation of the limbs of a patient, the movement that
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    rehabilitate the device must be compatible with human biomechanics. Generating other types of movements can eventually be detrimental to the neuromuscular system. Biomechanics indicates that a human's leg can be modeled with 7 degrees of mobility, however in the study of locomotion, an additional degree of freedom appears: knee rotation at the end of the support phase. Thus, a model of 8 degrees of freedom fits optimally to human biomechanics.
    1. Hip flexion / extension
    2. Hip abduction / adduction
    3. Hip rotation
    4. Flexion / knee extension
    5. Knee rotation
    6. Flexion / extension of the ankle
    7. Eversion / ankle inversion
    8. Ankle rotation
    It is evident that the closer the mechanical model of the exoskeleton is closer to these degrees of freedom or mobility, the more natural and physiologically sound the march will be printed on the patient. But it should also be noted that some of these degrees of freedom have a fundamental role in the human movement. The synchronized flexion / extension movement of the three joints in the sagittal plane generates gait in this plane. Perhaps the most significant is the role of two of the degrees of freedom of the ankle:
    In the movement of plantar flexion or flexion of the ankle 7 muscles are involved: soleus, gastrocnemius, short and long lateral peroneum, posterior tibial and long flexors of the fingers, which together with the Achilles tendon are capable of printing a power of about 500 W (for a man weighing 70 kg) at the time of takeoff from the foot of the ground. This energy is used by the body not only to detach the foot from the ground and prevent any collision during the transfer phase of the foot forward, but that energy propels the entire center of mass forward. Without it, the march loses its natural energy balance and also the ability to maintain the body's anteroposterior balance.
    The movements in the transverse plane, although they do not have an amplitude as remarkable as the movements in the sagittal plane, also take on a relevant function. The hip abduction / adduction movement allows you to balance the weight of the body from one leg to the
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    another during the double support phase, while allowing the direction to change during the march. The eversion / inversion movement of the ankle allows the balance of the body in the lateral plane.
    Most of the known exoskeletons sacrifice the locomotive function in favor of a design of low complexity and cost. Document US7153242B2 describes a lower limb exoskeleton based on rigid segments and clamps, joined by two rotational joints on each leg, one on the hip and one on the knee, which are controlled by linear or rotational actuators, generating movement only in the plane sagittal and conferring a mobility of two degrees of freedom for each leg, which does not allow lateral movements or stabilization of the user's balance during the march. The exoskeleton incorporates a passive ankle joint, with a spring to perform dorsiflexion during the foot transfer phase and avoid collision with the ground. The option of passively activating the ankle has negative effects on the generation of gait, since it prevents any motor capacity in the ankle in the impulse prior to the foot transfer phase.
    This exoskeleton requires the use of crutches to maintain the stability or balance of the patient in the locomotion, and leaves the user in charge of any movement in the lateral plane, such as changes of direction or even the distribution of weight from one leg to the other in The change of support. This restricts its use to patients with muscular strength in the arms and lateral mobility in the trunk. The movement is commanded by thoracic movements in the sagittal plane of the user, so its use is also limited to patients with this ability to move. It is therefore a device exclusively for use in spinal injuries below the sixth dorsal (T6), with paraplegia. The energy source is located on the back of the device, remaining on the patient's back, while the electronic units are located on the front. The device can generate various movement patterns: walking on flat ground and straight line, going up or down stairs, and transitions from sitting to standing and vice versa, but all walking programs are recorded for a particular patient and reproduced in the actuators, preventing any adaptation capacity of the step different from the pre-established. Further improvements to this invention, described in documents US2012 / 0101415A1 and US8096965B2 add the possible use combined with Electric Functional Stimulation (FES) and a safety module that reviews the status of all electronic components to prevent any failure of operation.
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    US7947004B2 and US8057410B2 describe a very similar exoskeleton, although it incorporates some important improvements. Although it also has only two degrees of freedom operated by the leg in the sagittal plane, this exoskeleton incorporates passive joints in the hip and ankle in the lateral plane, which allow a slight movement of abduction and adduction, and incorporates a torsional spring in the upper segment of the leg, allowing a slight rotation of the hip, which in turn has a greater comfort of the user during walking and better adaptation of the brace to the physical characteristics of the patient. Even so, the lack of degrees of freedom acted on has an insufficient march from the medical point of view, since it restricts the controlled movement to the sagittal plane, prevents the control of the balance, so it requires additional elements of support such as canes, and nullifies the energetic contribution of the ankle joint in the impulse prior to the foot transfer phase. This exoskeleton can be attached to the user's shoe, either on the outside, or on the inside as a template that is inserted into the shoe although this usually requires the modification of the shoe. The gait is jointly controlled based on pre-recorded patterns, and the phases of the locomotion cycle are distinguished by sensors under the feet that determine the reaction force of the soil.
    The knee joint is modeled in biomechanics as a single rotation in the sagittal plane. However, this is a simplification that eliminates some of the functions of this joint that is one of the most complex of the human body, being really a capsule composed of three joints: femurotibial joint (between the femur and tibia condyles), femurotulian joint (between the trochlea of the femur and the articular face of the patella) and the proximal tibioperoneal joint. Although the main movement of the knee is flexion-extension in the sagittal plane, the last two knee joints allow the label to slide slightly up or down and from inside to outside. To incorporate these movements, some more realistic biomechanical models incorporate a polycentric axis in the sagittal plane that moves through a four-bar mechanism.
    The ankle joint in the sagittal plane has a fundamental role in human gait. It is the one that provides the greatest instantaneous power to the human body during the impulse phase when the foot is off the ground and proceeds to the transfer phase of the leg forward. The known devices incorporate an elastic system that only flexes the ankle to clear the foot of the floor and prevent it from colliding with it during the transfer. But this eliminates the energetic contribution that the body
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    You need to keep the locomotion energy efficient.
    The international application WO2012 / 027336A1 includes operational lifting and sitting functions, in addition to a state machine for controlling the transition between these functions and the way of walking, and completes the device with an auxiliary support element (walker or crutches) to provide lateral stability that the exoskeleton does not provide. It incorporates in these auxiliary devices some controls or joysticks that allow to command the speed of the exoskeleton. The communication between the exoskeleton and the auxiliary device is wireless. Finally, it includes the incorporation of cerebral interface for the exoskeleton command, and a voice recognition system.
    Document US2011 / 0066088A1 describes an exoskeleton of the lower limb with five degrees of freedom per leg, including sagittal and lateral actuation in the ankle and in the abduction / adduction of the hip, which allows the movement of the patient both in the sagittal plane and on the side, and also allows you to control and maintain patient stability without using auxiliary devices such as crutches or walkers. The mechanical structure is extensible to fit the user's size. The batteries are placed in the back of the exoskeleton, being at the height of the kidneys, which, even being replaceable, hinders this operation by the user himself. This device incorporates a pelvic harness that supports the patient's weight, opening its use to patients with bone weakness. The use of this harness has the disadvantage of inducing external rotation of the hips, which is then corrected by force with the exoskeleton grips in femur and tibia, which causes pathological joint efforts. Pelvic harnesses are not recommended for walking. As a biomechanically successful element it has a polycentric type knee, more similar to the human knee (widely used in knee prostheses). In spite of this characteristic, this design lacks the rotation of the hip, essential to print the trajectory of the center of pressure on the sole of the foot corresponding to a healthy march.
    The structure of this device incorporates protection against water and dust. Its sensory system includes inertial units, incremental optical meters for joint position and pressure sensors on the soles of the feet. A laser or distance sensor allows to determine the profile of the ground to generate adequate walking modes. Even being the only exoskeleton with the ability to control the stability or balance of the patient, the drawback of this exoskeleton is its low speed, unable to reach
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    walking speeds greater than 0.05 m / s, which makes it unusable. This is due to the need to generate very high articular pairs to guarantee the stability of the system, which proportionally reduces the articular speed based on a transmission ratio, necessary given the power limit of the actuators.
    WO2013 / 019749A1 describes a very generic exoskeleton, of very similar benefits to those mentioned above, although it does not contemplate the control of the stability of the exoskeleton-user set understood as control of the postural equilibrium during locomotion. The reference made in the document to stability control refers to the ability of the device to hold the person standing statically or standing, as far as the required forces are concerned. This document also describes the user interface system and the exoskeleton, which can be done using any system capable of acquiring commands from the user.
    US2007 / 0123997A1 describes a lower limb exoskeleton design seeking energy savings during locomotion. The exoskeleton is designed with three degrees of freedom per leg, therefore it generates movement only in the sagittal plane, but only uses an actuator in the hip joint. Based on biomechanics studies, an energy dissipating element of the controllable shock absorber type in the knee, and an elastic element to act on the ankle are proposed in this document. The combination of these three elements: motor, shock absorber and spring generates a pattern of march very similar to the biological one, with a minimal energetic consumption. Another novelty is the incorporation of a rigid pelvic harness, similar to a bicycle saddle, to support the user's weight. This solution improves the problem of conventional pelvic harness.
    There are also examples of portable locomotion assistance exoskeletons that are composed of one or several kinematic chains of segments and joints of any number of degrees of freedom, the size of whose segments can be adjustable in length, and that is coupled to the human body and to its extremities (legs, arms, or segments) by means of a fastening system based on posterior rigid or semi-rigid clamps, straps, straps, velcro closures, buckles, etc. and may include a pelvic or thoracic belt or harness.
    All these devices require excessive prior adjustment by specialized personnel, both of the mechanical structure that must be perfectly coupled to the user,
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    as of the movement control methods, which are based on the follow-up of specific reference patterns for a patient. This lack of flexibility in design and movement control methods greatly hinders the widespread use of exoskeletons. On the one hand, the manufacture tailored to the user precludes a mass production and the consequent lowering of the final product to reach the user. On the other hand, it is important to consider the variability of the symptoms in the same user throughout his life, and throughout each day. For example, a patient suffering from spasticity (joint stiffness) will progressively reduce their degree of spasticity with daily rehabilitation, so they would have to change the device or adjust it conveniently as their pathology evolves. According to neurological rehabilitation professionals, a patient's spasticity can suffer significant variations during a rehabilitation exercise in a short period of time.
    As seen in the review of the state of the art, none of the known embodiments is capable of controlling the balance of the exoskeleton-user assembly during walking at a normal walking speed. For this reason it is necessary to use additional elements such as canes or walkers that help the user maintain balance. This restricts the number of potential users to those who have strength and mobility in the upper limbs, while keeping their hands occupied preventing them from using them for any other function. It is desirable that the exoskeleton maintain balance in a controlled manner without the help of additional elements.
    It is necessary to have exoskeletons that automatically adjust to each user, not only in dimensions, but especially in performance, in the degree of mobility contribution depending on the user's own mobility, and in the control of the movement of each articulation and the March. This adjustment should not require specialized personnel and should be as automatic as possible, so that it requires minimal intervention by the user or the rehabilitation physician.
    The mechanisms of attachment and adjustment of the exoskeleton to the human body are of special relevance in the correct transmission of the movement to the user, at the same time that they must guarantee its health, without pressing or causing any damage. Most of the developments mentioned in the state of the art incorporate rigid rear clamps on the extremities, adjustable to the user by means of velcro fasteners. Some developments also include a pelvic harness that ensures the transfer of part of the weight
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    from the user to the exoskeleton. According to physiotherapy experts, the use of these harnesses prevents natural gait, since by causing the user's opening of English it generates external rotation of the hip, which is artificially corrected by the device when aligning the knees. Both aphysiological effects can cause damage during walking and therefore the use of the pelvic harness is discouraged by medical specialists for walking.
    All lower limb exoskeletons described in the state of the art require functional transfer of the user from his wheelchair or from the bed to the exoskeleton. This prevents the autonomy and independence of the user in their daily use. This is mainly due to the mechanisms of attachment of the exoskeleton to the body of the user, which have rigid clamps on the back of the thigh and shin to ensure the support of the member. In addition, lumbar reinforcement, which is indispensable in any trunk brace on foot by medical determination, is located at the back of the exoskeleton. For this reason it is not possible to place the exoskeleton from the previous position to the posterior one since both the lumbar reinforcement and the clamps are interposed.
    The mechanical structure of the exoskeleton should allow and never prevent the normal physiological position of the longitudinal axes of the parts that fit the user's lower extremities. The feet, in physiological position in standing form an angle to each other, so that during walking, the distance between the heels in the lateral plane is very small and approximately one third of the distance between the toes. For this to be fulfilled in a normal way, the diaphaseal cervical angle of the femur neck and the condylar angle formed between femur and tibia have normal values.
    But in addition, since these are exoskeletons to help rehabilitate patients with aphysiological gait, the mechanical structure should allow adjustment in people with anatomical abnormalities, such as hips with abnormal cervical-diaphase angles or knees vara and valga.
    None of the devices known in the state of the art fulfills this anatomical function, presenting cervical angles of 90 ° and condylar angles of 0 °, which in no case correspond to a physiological gait and therefore generate an abnormal gait in patients without anomaly and cannot be used in patients with anomaly.
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    The exoskeleton for assistance to the human movement of the present invention solves all the aforementioned drawbacks.
    DESCRIPTION OF THE INVENTION
    The present invention relates to an exoskeleton for assistance to human movement, adjustable to the user in dimensions, tensions and joint ranges, this adjustment can be manual or automatic, where its placement in the user can be from the front to the back in the previous direction. posterior in the sagittal plane, being able to be placed from lying down or sitting without the need for functional transfer from the user to the exoskeleton. The exoskeleton presents a modular design, compatible with human biomechanics and that reproduces a natural and physiological movement in the user, with up to 7 degrees of mobility operated and controlled by limb, guaranteeing the stability of the user's balance during locomotion without making use of auxiliary support elements.
    The exoskeleton for assistance to the human movement of the present invention comprises a mechanical structure comprising segments joined by joints that allow relative movement between two or more successive segments to move the user's limbs. Said mechanical structure is modular, that is, it can be constituted by one or two independent and attachable limbs, and to which any other device such as a robotic arm, tool, or even another upper limb exoskeleton can be attached. Each module is formed by one or several kinematic chains of the mentioned segments and joints. The segments are adjustable not only in length, but also in width, being able to adapt to a wide range of users according to their physical constitution.
    The mechanical structure can be rigid, semi-rigid or flexible, and can be manufactured in different materials such as metal, fiber, glass, wood, textile, plastic, or any variant or combination of them. You can also incorporate one or several housings of rigid, semi-rigid or soft material, of any material, as a beautifier or as a system of isolation of the environment or protector of the exoskeleton, or of the user. The structure may incorporate, in addition to, or replacing the housings, a surface treatment, such as paint, anticorrosive, antioxidant, etc.
    The mechanical structure, formed by segments and joints, as mentioned
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    previously, it comprises an abduction / adduction joint in the hip, adjustable by means of an actuator controlled by an articular control system that allows a range of cervical-diaphase angles to be obtained within the desirable ranges for patients with aphysiological gait, due to anatomical abnormalities, as are the hips with abnormal cervical-diaphase angles.
    The mechanical structure also includes a condylar adjustment mechanism that allows passive adjustment of the condylar angle formed between femur and tibia to adapt it to users with anatomical anomalies such as rod or valgus knees.
    As described above, the joints that join the segments of the mechanical structure allow relative movement between two or more successive segments through active, resistive, passive elements, or a combination of these. These joints can be coaxial to the user's joints or not, and their number can match the number of degrees of mobility of human joints or not. In any case, its purpose is to move the user's joints by conferring a natural march. For this, and according to recommendations of medical specialists, the following degrees of mobility are fundamental:
    - Flexion and extension of the hip by rotation in the sagittal plane.
    - Abduction adduction of the hip by rotation in the lateral plane.
    - Hip rotation by rotation in the transverse plane.
    - Flexion and extension of the knee by rotation in the sagittal plane.
    - Flexion and extension of the ankle by rotation in the sagittal plane.
    - Eversion and inversion of the ankle through rotation in the lateral plane.
    These 6 degrees of mobility in each leg or lower limb are an essential requirement to be able to generate a natural and physiologically healthy gait in the user. In the exoskeleton of the present invention, these 6 degrees of mobility per leg are operated. This action can be monoarticular or multiarticular, that is, n motors can be used to move m joints, where n can be greater than, equal to or less than m. For its implementation any multiarticular transmission system is used: mechanisms of bars, belts, cables, pulleys, etc.
    The actuation of the main 6 degrees of mobility is essential to guarantee the control of the stable balance of the exoskeleton-user set. Also, two of these
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    Joints require special treatment because of their biomechanical function: the knee and ankle both in the sagittal plane:
    The knee joint of the present invention comprises an eccentric axis with respect to the crossing of the upper and lower segments, which allows a flexion greater than 100 °, necessary for sitting, and provides greater stability in the support.
    The ankle joint in the sagittal plane comprises an actuator separate from the ankle of the user to reduce the moment of inertia of the leg since the maximum power required in the ankle is approximately 500 W for a subject weighing 70 kg and this would require an actuator of equivalent power that located in the ankle would cause an unwanted increase in weight, volume and moment of inertia for an exoskeleton. The solution proposed instead by said actuator transmits the movement to the ankle through a bar mechanism and an elastic element that exerts traction on the bars of the bar mechanism, to achieve the power requirement without increasing the weight and volume of the actuator, contributing in this way to the plantar flexion of the ankle constantly.
    The joints that join the segments of the mechanical structure of the exoskeleton of the present invention comprise an adjustable joint range and adaptable to the user's joint range. This regulation can be mechanical, electronic, programmed or automatic, or any combination of these types.
    The mechanical structure comprises an actuation system formed by actuators that give movement to the joints that can be linear, rotational, or any combination of both. Its principle of operation can be hydraulic, pneumatic, electric, magnetic, thermal or a combination of these. They can also be intelligent materials, such as ionic polymers, elastomers, piezoelectric, etc., or a hybrid system between conventional systems and intelligent materials. These elements may be placed in the mechanical structure of the exoskeleton, close to human joints or in any other position as appropriate by functionality criteria. The movement, force, or torque is transmitted from the actuators to the joints through one or more transmission systems such as gears, belts, cables, pulleys, spindles, or direct transmission.
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    The exoskeleton comprises a fastening system that allows its coupling to the human body from the anterior part of the body, allowing its placement from a sitting or lying posture without the need for functional transfer, where the fastening system is adjustable and adaptable to the Anatomy of the user and adjustable in tension.
    The fastening system comprises a rigid lumbar reinforcement which in turn comprises two or more attachable segments, two of which are joined to the exoskeleton segments by means of one or more rotation axes, the lumbar reinforcement being able to be retracted by successive rotations until being placed in the sagittal plane to allow placement of the exoskeleton from the front of the user. Once the exoskeleton is attached to the user, the segments that form the lumbar reinforcement are rotated again until they occupy their lumbar functional position, fixing all the segments to each other by means of any coupling system.
    This mode of placement exploits the modularity of the exoskeleton design, each limb being able to be placed independently and finally joining through the lumbar reinforcement.
    The fastening system also comprises an ischiatic support whose function is to transfer the weight of the user to the exoskeleton, where said ischiatic support is preferably a cinch located under the user's buttocks, which supports part or all of the user's weight and transmits it to the structure mechanics. Said ischiatic support is adjustable, being able to graduate its tension through a tension mechanism that can be manual or automatic, besides being removable, which results in the easy placement of the exoskeleton.
    The fastening system also includes fastening devices for fixing the exoskeleton to the user's legs, not being rigid at its rear part so as not to hinder the placement of the exoskeleton to the human body from the front part of the body.
    The fastening system also includes an anchoring device to the user's shoe.
    The exoskeleton comprises an onboard power system that provides energy to the
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    actuation system and a computer system. The on-board power system may consist of batteries, fuel cells, alternating generators, hydraulic system, electro-hydraulic system, piezo-hydraulic system, pneumatic system, piezo-pneumatic system, or any combination of these systems. The on-board power system can be modular, so that each module of which the exoskeleton is composed is fed independently. Thus, an exoskeleton formed by two lower extremities can include at least two power modules, placed on the lateral part of the extremities, so that it does not hinder the user to support his back or lie down and at the same time be easily accessible for his replacement or recharge.
    The exoskeleton comprises a sensory system that monitors the movement of the exoskeleton, which depends on the state of the exoskeleton itself, the user, the user's interaction with the exoskeleton and the environment at every moment. This system includes:
    to. A proprioceptive subsystem, which instantly determines the state of the robot,
    b. A physiological subsystem, which determines the state of the user through biomarkers,
    C. A stereceptive subsystem, which determines instantaneously or over a period of time the state of the environment,
    d. A perceptual subsystem of the exoskeleton-user-environment interaction and that determines the state of mutual interaction between the three previous subsystems,
    being able to include all, some or any combination of these subsystems. For this, the sensory system is composed of combinations of sensory elements of a physical, mechanical, chemical or biological nature or of any other nature, such as force, torque, pressure, position, speed, laser, camera, goniometer, sensors. electromyographs, eye activity sensors, brain activity sensors, heart rate and respiratory meters, spirometer among other options.
    The exoskeleton comprises a motion control system that receives information from the sensory system, and is composed of one or more of the following subsystems:
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    to. Joint control system
    b. Limb control system.
    C. Mass center control system of the exoskeleton-user set.
    The exoskeleton also includes a user interface system that interprets the user's intention to move and transmits this information to the motion control system. This user interface system can consist of a joystick, tablet, mobile phone, touch screen, keyboard, mouse, microphone, camera, eye movement reader, electromyographic sensors (EMG), brain interfaces (BCI) acronym), eye interfaces (EOG) force or torque sensors, pressure sensors, inertial motion sensors (IMU), position, speed, angle, tilt sensors , etc., or any combination of these devices, and includes the electronics and processing of the information required by the interface to capture the user's intention to move.
    The exoskeleton comprises one or several on-board processing units that carry out all the computational processing of one or more of the sensory, user movement control and user interface systems. The processing units may be based on any type of processor, microprocessor, logic-based semiconductor device (FPGA) or any combination thereof.
    BRIEF DESCRIPTION OF THE DRAWINGS
    To complement the description that is being carried out and in order to help a better understanding of the characteristics of the invention, a set of drawings is attached as an integral part of said description, where with an illustrative and non-limiting nature, the next:
    Figures 1a to 1c.- Shows a realization of a lower limb exoskeleton with a user, in three views: profile, front and perspective respectively. In them the elements of the system of subjection of the user to the exoskeleton are indicated.
    Figure 2.- Shows the ischiatic support in the view on the left, and a manual adjustment system for it in the detail on the right.
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    Figures 3a to 3d and 4a to 4c.- It shows in detail the refolding process of the rigid lumbar reinforcement.
    Figure 5.- Shows the degrees of joint mobility and the corresponding actuators for an embodiment of a lower limb exoskeleton of 6 degrees of freedom per leg.
    Figures 6a and 6b.- They show a variant of the invention, with an extra degree of freedom that allows the rotation of the knee in different positions.
    Figure 7a - Shows in detail the anchoring of the exoskeleton to the shoes.
    Figure 7b - Shows a detail of the mechanism of bars and elastic element that complements the actuator of the ankle joint.
    Figure 8.- Shows a side view of an exoskeleton of the lower limb and indicates a variable and controllable actuator of impedance in the knee.
    Figure 9. Shows a diagram of the control system.
    Figures 10a and 10b. They show the mechanical structure adapted to the normal anatomy and to the anomaly, with detail of the condiliar adjustment mechanism in different positions.
    Figures 11a and 11b. They show a variant of the invention for the adjustment of the condylar angle, making use of a four-bar mechanism in different positions.
    PREFERRED EMBODIMENT OF THE INVENTION
    The exoskeleton for assistance to the human movement of the present invention is described in detail below.
    The exoskeleton comprises a modular mechanical structure comprising segments joined by joints. Said mechanical structure comprises an abduction / adduction joint at the hip (32), adjustable by means of an actuator (42) that allows a range of cervical-diaphase angles to be obtained within the desirable ranges for
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    patients with aphysiological gait, due to anatomical abnormalities, such as hips with abnormal cervical-diaphase angles.
    The mechanical structure also includes a condylar adjustment mechanism (18) that allows passive adjustment of the condylar angle formed between femur and tibia to adapt it to users with anatomical anomalies such as rod or valgus knees. In Figures 10a and 10b a first example of realization of said condylar adjustment mechanism (18) is shown, comprising a proximal segment (150) adjacent to a knee joint (105) and a distal segment (151) further away from the knee joint, where the proximal segment (150) is shorter and is inserted into the distal segment (151), and where both segments (150, 151) are joined by a pin (152) arranged perpendicular to the tibia of the user and in the direction of advancement, where the regulation of the condiliar angle is carried out by means of a threaded mechanism arranged at the lower end of the distal segment. Figure 10a shows the mechanical structure of the exoskeleton for a user without anomaly and Figure 10b shows the mechanical structure adjusted for a user with coxa vara and genu valgo.
    The exoskeleton comprises 6 degrees of mobility in each leg that are operated. These degrees of mobility are as follows:
    - Flexion and extension of the hip (31) by rotation in the sagittal plane;
    - Abduction-adduction of the hip (32) by rotation in the lateral plane;
    - Hip rotation (33) by rotation in the transverse plane;
    - Flexion and extension of the knee (34) by rotation in the sagittal plane;
    - Flexion and extension of the ankle (35) by rotation in the sagittal plane;
    - Eversion and inversion of the ankle (36) by rotation in the lateral plane;
    each operated by an actuator (41, 42, 43, 44, 45, 46) respectively.
    The degree of mobility to carry out the flexion and extension of the knee (34) by rotation in the sagittal plane is defined because the mechanical structure comprises an eccentric axis (120) with respect to the crossing of an upper segment (121) and a lower segment (122), eccentric shaft (120) actuated by the corresponding actuator (44), which allows more than 100 ° flexion, necessary for sitting, and provides greater stability in the support, as shown in Figure 1.
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    A second example of realization is shown in Figures 11a and 11b where the condylar adjustment mechanism (18) comprises a 4-bar mechanism (110), arranged below the knee joint (105). In this way the upper segment (121) is offset, although it remains parallel to the inner segment (122), varying the condylar angle and adjusting it to the user.
    The degree of mobility to carry out the flexion and extension of the ankle (35) by rotation in the sagittal plane comprises an actuator (45) separated from the ankle of the user that transmits the movement to the ankle through a bar mechanism (47) and an elastic element (48) that exerts traction on the bars of the bar mechanism (47), where the effect of the elastic element is to contribute to the plantar flexion of the ankle constantly. The combined operation of the actuator (45) and elastic element (48) is as follows: during support, the weight of the user and the action of the actuator (45) exceed the antagonistic torque generated by the elastic element (48) and the phase is Run normally. When the take-off phase is reached, the effect of the user's weight disappears, while the actions of the elastic element (48) and actuator (45) are added in favor of the plantar flexion, which generates the instantaneous power required for the impulse. During the foot transfer phase the actuator (45) has sufficient power to counteract the effect of the elastic element (48) and generate the dorsal flexion of the ankle to avoid collision with the ground. Figure 7b details an implementation of the ankle joint and its position during the support phase and during the impulse.
    The exoskeleton comprises a fastening system (2) that allows its coupling to the human body from the anterior part of the body, allowing its placement from a sitting or lying posture without the need for functional transfer.
    The fastening system (2) comprises a rigid lumbar reinforcement (20) which in turn comprises two or more attachable segments (21), as shown in Figures 3a to 3d, two of which join the segments of the exoskeleton by means of one or more rotation axes (22), where the rigid lumbar reinforcement (20) is retracted by successive rotations until it is placed in the sagittal plane to allow the exoskeleton to be placed from the front of the user. Once the exoskeleton is coupled to the user, the segments that form the rigid lumbar reinforcement (20) are turned back to their lumbar functional position, all segments being fixed together by means of a coupling system (23). Figures 4a to 4c show a view of the rigid lumbar reinforcement (20) in two
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    different positions: Figure 4a shows the natural operating position of the lumbar reinforcement (20), in which both attachable segments (21) are connected and occupy the rear part of the exoskeleton. Figures 4b and 4c show the refolding sequence until both attachable segments (21) are fully collected parallel to the sagittal plane, leaving the interior space of the exoskeleton completely free to proceed with placement from the front of the user.
    This mode of placement exploits the modularity of the exoskeleton design, each limb being able to be placed independently and finally joining through the rigid lumbar reinforcement (20) and the rest of the fastening system components (2).
    The fastening system (2) further comprises an ischiatic support (25) whose function is to transfer the weight of the user to the exoskeleton, where said ischiatic support is preferably a cinch located under the user's buttocks, which supports part or all of the user's weight and transmit it to the mechanical structure, as shown in Figure 2. Said ischiatic support (25) is adjustable, and its tension can be adjusted through a tension mechanism (26) that can be manual or automatic, in addition to be removable, which results in the easy placement of the exoskeleton. In order not to hinder the placement of the exoskeleton, the ischiatic support (25) can be buckled and unbuttoned, depending on the way of placing the exoskeleton.
    The ischiatic support (25) can also be performed using thermoplastic legguards, especially in those patients with bone density deficits such as osteoporosis.
    The fastening system (2) also includes fastening devices, preferably clamps, for fixing the exoskeleton to the user's legs, being not rigid in its rear part so as not to hinder the placement of the exoskeleton to the human body from the previous part. of the body.
    The fastening system further comprises an anchoring device to the user's shoe (28), which is carried out permanently, by means of rivets or other fixing system, or detachably by means of screws or other means of adjustment, either by inside of the shoe or on the outside. Since the majority of patients require the use of specialized orthopedic footwear, it is not advisable to use exoskeletons with a sole, to which the user's shoe fits, but it is preferable that
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    The mechanical structure is anchored directly on the natural sole of the footwear, so as not to interfere with the pathology of the foot. Figures 7a and 7b show an example of realization of the anchoring of the exoskeleton to the user's shoe, in which a clamp-type fastener is used in the heel part of the sole and is grasped by screws or rivets (28).
    The exoskeleton comprises an on-board power system (13) that provides power to an actuation system formed by the actuators (41, 42, 43, 44, 45, 46) comprising the mechanical structure and a computation system (14 ).
    The exoskeleton also includes an on-board sensory system (3) that monitors the movement of the exoskeleton and includes:
    and. A proprioceptive subsystem (4), which instantly determines the state of the robot,
    F. A physiological subsystem (5), which determines the state of the user through biomarkers,
    g. A stereceptive subsystem (6), which determines instantaneously or over a period of time the state of the environment,
    h. A perceptual subsystem (7) of the exoskeleton-user-environment interaction and which determines the state of mutual interaction between the three previous subsystems (4, 5, 6),
    being able to include all, some or any combination of these subsystems (4, 5, 6, 7).
    The exoskeleton comprises a motion control system (12) that receives information from the on-board sensory system (3), and is composed of one or more of the following systems:
    to. Joint control system (8).
    b. Limb control system (10).
    C. Mass center control system of the exoskeleton-user assembly (11).
    The joint control system (8) guarantees the desired joint movement in the user based on the monitoring of a reference signal that can be any physical, mechanical or biomechanical magnitude such as joint position, speed, force, torque or any derivative or combination of they, by means of an automatic control technique (Proportional, Integral,
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    Derivative, neuronal control, diffuse control, heurstic control, non-linear control, robust control, optimal control, etc., or any combination thereof).
    Since the majority of exoskeleton users have spasticity, spasmicity and other anomalies, it is necessary to adapt the joint movement to these effects to avoid damaging the user's tendinomuscular tissue. For this, the joint control system (8) incorporates an impedance control module that receives information from the sensory system (3) and in particular from the physiological subsystem (5) and automatically adapts the movement of the exoskeleton's articulation to the range, stiffness and spasmicity of the user's equivalent articulation. In some embodiments of the invention, this impedance control module can be implemented by means of a variable and controllable impedance joint, as described in the Spanish patent application P201330882 which is incorporated herein by reference, which presents important advantages over programmed modules. Figures 6a and 6b show an embodiment of the invention incorporating a variable and controllable impedance joint (50) in the knee.
    The movement control system of each lower limb (10) synchronizes the joint control systems (8) that integrate the kinematic chain corresponding to that limb as a function of time, position and / or its temporal derivatives, and / or force and / or torque and / or its temporary derivatives, and / or depending on the information from the sensory system to automatically adapt the movement of the lower limb (10) to the stiff conditions of the contact environment.
    The movement control system of the center of mass (11) of the exoskeleton-user assembly synchronizes the control systems of each lower limb (10) as a function of time and / or position and / or its derivatives and / or force and / or torque and / or its derivatives, or any other physical, mechanical or biomechanical variable and / or through the feedback of information from the on-board sensory system (3) and / or through the information commanded by the user through an interface system of user (16) and / or following a movement reference pattern based on joint positions and / or their derivatives and / or joint and / or joint forces and / or lower limb positions (10) and / or their derivatives and / or forces and / or pairs in the lower extremities (10) and / or any biomechanical parameter.
    Figure 9 shows an exemplary embodiment of the motion control system (12) for an exoskeleton with 4 limbs, two arms and two legs, and 6 joints per
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    each limb
    The mass center movement control system (11) has the ability to adapt the reference patterns to the user's biomechanical conditions, by means of an automatic reference pattern adapter. This automatic reference pattern adapter adjusts these movement patterns to the joint range, muscle strength and instantaneous conditions of each limb of the user.
    This system of control of the movement of the center of mass (11) keeps the exoskeleton-user set in dynamic or statically stable equilibrium even in the face of slight external disturbances. Balance control is performed based on the monitoring of a desired Stability Index, which may be based on the nominal trajectory of the Pressure Center, or the Null Moment Point (ZMP), on the Stability Margin Energy (NDESM), or any other Stability Index. Based on an instantaneous measurement of said Index and comparing it with the nominal or desired value, the difference between both values is minimized by any control technique (proportional, derivative, integral, blurred, neuronal, optimal, etc. or any combination thereof) ) by generating a movement or torque in the center of mass of the robot-user assembly or in any of its extremities. The control system of the center of mass (11) will determine if it is necessary to modify the pattern of gait to maintain balance.
    The joint control system (8), the movement control system of each limb (10), and the movement control system of the mass center (11) can be combined with a human actuation system by which the muscles of the user participate in a certain degree in the generation of movement. This system of human action can be carried out directly through the voluntary movement of the user, or indirectly through functional muscle stimulation (FES), or a combination of both. These control systems can also be combined or synchronized with a central motion pattern generator (CPG).
    The user interface system (16) that interprets the user's intention to move and transmits this information to the motion control system. This user interface system (16) can be formed by a joystick, tablet, mobile phone, touch screen,
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    keyboard, mouse, microphone, camera, eye movement reader, electromyographic sensors (EMG), brain interfaces (BCI), eye interfaces (EEG) force or torque sensors , pressure sensors, inertial motion sensors (IMU), position, speed, angle, inclination, etc., or any combination of these devices, and includes electronics and information processing required by the user interface system (16) to capture the user's movement intention.
    The exoskeleton comprises a communication system (15) that links between the control systems (8, 10, 11), the sensory system (3) and the user interface system (16) or between any combination thereof. This communication can be wired, wireless or any combination of both, using any communication protocol (CAN, Ethernet, LAN, etc).
    The exoskeleton also includes one or several on-board processing units that perform all the computational processing of one or more of the systems: sensory (3), control (8, 10, 11) and user interface (16). The processing units may be based on any type of processor, microprocessor, logic-based semiconductor device (FPGA) or any combination thereof.
    All processing electronics, as well as the power source on board the exoskeleton are placed along the mechanical structure. If the power source is based on rechargeable or replaceable batteries, these are located on the side and front of the exoskeleton to facilitate loading or replacement by the user.
    The joints that join the segments of the exoskeleton mechanical structure of the present invention comprise an adjustable joint range and adaptable to the user's joint range. This regulation can be mechanical, electronic, programmed or automatic, or any combination of these types.
    to. Mechanical: by means of a stop or sliding brake, by threading or any other linear displacement system.
    b. Electronics: through the use of end-of-stroke sensors or any similar device that detects the articular position will limit and command the stop of the articular motor.
    C. Scheduled: the user or other responsible person (a medical professional)
    sets the joint limits to the joint control system (8) through the
    user interface system (16).
    d. Automatic: the exoskeleton, through the on-board sensory system (3),
    5 determines the user's joint range and communicates the joint limits to the
    joint control system (8), preferably as part of a self-check program.
    or any combination of these types.
    10
    权利要求:
    Claims (25)
    [1]
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    R E I V I N D I C A C I O N E S
    1. - Exoskeleton for assistance to human movement comprising a mechanical structure comprising segments joined by joints that allow relative movement between two or more successive segments to move the limbs (10) of the user conferring a natural gait and a fastening system ( 2) which allows its coupling to the human body to be carried out characterized in that the fastening system (2) comprises a rigid lumbar reinforcement (20) which in turn comprises two or more attachable segments (21), two of which are joined to the segments of the exoskeleton by at least one axis of rotation (22), where the lumbar reinforcement is retractable by successive rotations until it is located in the sagittal plane.
    [2]
    2. - Exoskeleton for assistance to the human movement according to claim 1 characterized in that it comprises at least 6 degrees of mobility in each lower extremity that are operated, these degrees of mobility being the following:
    - Flexion and extension of the hip (31) by rotation in the sagittal plane;
    - Abduction-adduction of the hip (32) by rotation in the lateral plane,
    - Hip rotation (33) by rotation in the transverse plane;
    - Flexion and extension of the knee (34) by rotation in the sagittal plane;
    - Flexion and extension of the ankle (35) by rotation in the sagittal plane;
    - Eversion and inversion of the ankle (36) by rotation in the lateral plane;
    each operated by an actuator (41, 42, 43, 44, 45, 46) respectively.
    [3]
    3. - Exoskeleton for assistance to the human movement according to claim 2
    characterized in that the mechanical structure comprises an eccentric shaft (120) with respect to the crossing of an upper segment (121) and a lower segment (122) of the knee joint, eccentric shaft (120) actuated by the corresponding actuator (44), which define the degree of mobility of flexion and extension of the knee (34) by rotation in the sagittal plane.
    [4]
    4. - Exoskeleton for assistance to the human movement according to claim 2
    characterized in that the mechanical structure comprises a bar mechanism (47) that receives the movement of the corresponding actuator (45) that is separated from the
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    the user's ankle where the bar mechanism (47) transmits the movement to the ankle, and an elastic element (48) that exerts traction on the bars of the bar mechanism (47).
    [5]
    5. - Exoskeleton for assistance to the human movement according to claim 1
    characterized in that the mechanical structure comprises a condylar adjustment mechanism (18) to passively adjust the condylar angle formed between femur and tibia.
    [6]
    6. - Exoskeleton for assistance to the human movement according to claim 5
    characterized in that the condylar adjustment mechanism (18) comprises a proximal segment (150) adjacent to a knee joint (105) and a distal segment (151) furthest from the knee joint (105), where the proximal segment ( 150) is shorter and is introduced into the distal segment (151), and where both segments (150, 151) are joined by a pin (152) arranged perpendicular to the user's tibia and in the forward direction.
    [7]
    7. - Exoskeleton for assistance to the human movement according to claim 6
    characterized in that the condylar adjustment mechanism (18) comprises a threaded mechanism disposed at the lower end of the distal segment (151) to carry out the regulation of the condylar angle.
    [8]
    8. - Exoskeleton for assistance to the human movement according to claim 5
    characterized in that the condylar adjustment mechanism (18) comprises a 4-bar mechanism (110) disposed below the knee joint (105).
    [9]
    9. - Exoskeleton for assistance to the human movement according to claim 1
    characterized in that the fastening system (2) further comprises an ischiatic support (25), preferably an adjustable and removable strap, where its tension is adjusted through a manual or automatic tension mechanism (26).
    [10]
    10. - Exoskeleton for assistance to the human movement according to claim 1
    characterized in that the fastening system (2) also includes fastening devices that are not rigid at the rear of the exoskeleton, preferably clamps, for fixing the exoskeleton to the lower extremities of the user, fastening devices that are arranged in the back of the exoskeleton.
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    [11]
    11. - Exoskeleton for assistance to human movement according to claim 1 characterized in that the fastening system (2) also comprises an anchoring device to the user's shoe (28) permanently or detachably.
    [12]
    12. - Exoskeleton for assistance to human movement according to any of the preceding claims characterized in that it comprises an on-board power system (13) that provides power to an actuation system formed by the actuators (41, 42, 43, 44, 45, 46) comprising the mechanical structure and a computer system (14).
    [13]
    13. - Exoskeleton for assistance to human movement according to claim 12 characterized in that it also comprises an on-board sensory system (3) that monitors the movement of the exoskeleton and comprises at least one of the following subsystems:
    to. a proprioceptive subsystem (4), which instantly determines the state of the robot,
    b. a physiological subsystem (5), which determines the state of the user through biomarkers,
    C. a stereceptive subsystem (6), which determines instantaneously or over a period of time the state of the environment,
    d. a perceptual subsystem (7) of the exoskeleton-user-environment interaction and that determines the state of mutual interaction between the three previous subsystems (4, 5, 6),
    [14]
    14. - Exoskeleton for assistance to human movement according to claim 13 characterized in that it also includes a motion control system (12) that receives information from the on-board sensory system (3), and which comprises one or more of the following systems :
    to. a joint control system (8),
    b. a limb control system (10),
    C. a control system of the mass center of the exoskeleton-user set (11).
    [15]
    15. - Exoskeleton for assistance to human movement according to claim 14 characterized in that the joint control system (8) comprises an impedance control module that receives information from the sensory system (3) and in particular from the subsystem
    physiological (5) and automatically adapts the movement of the exoskeleton joint to the range, stiffness and spasmicity of the user's equivalent joint.
    [16]
    16. - Exoskeleton for assistance to the human movement according to claim 14
    5 characterized in that the movement control system (12) of each limb (10)
    synchronizes the articular control systems (8) that integrate the kinematic chain corresponding to that limb as a function of time, position and / or its temporal derivatives, and / or force and / or torque and / or its temporal derivatives, and / or in function of the information from the on-board sensory system (3) to automatically adapt the movement 10 of the limb to the stiff conditions of the contact environment.
    [17]
    17. - Exoskeleton for assistance to the human movement according to claim 14
    characterized in that the movement control system of the mass center (11) of the exoskeleton-user assembly synchronizes the control systems of each limb (10)
    15 as a function of time and / or position and / or its derivatives and / or force and / or torque and / or its derivatives, or any other physical, mechanical or biomechanical variable and / or through feedback of information from the system sensory (3) and / or through the information commanded by the user through a user interface system (16) and / or following a movement reference pattern based on articular positions and / or their derivatives and / or pairs and / or 20 joint forces and / or positions of the limbs and / or their derivatives and / or forces and / or pairs on the limbs and / or any biomechanical parameter.
    [18]
    18. - Exoskeleton for assistance to the human movement according to any of claims 14 to 17 characterized in that it comprises a human actuation system
    25 combinable with the articular control system (8), the movement control system (12) of each limb (10), and the movement control system of the mass center (11), by which the user's muscles they participate in a certain degree in the generation of movement.
    30 19.- Exoskeleton for assistance to the human movement according to any of the
    claims 14 or 17 characterized in that it comprises a user interface system (16) that interprets the user's intention of movement and transmits this information to the movement control system of the center of mass (11).
    [20]
    20. - Exoskeleton for assistance to the human movement according to claim 19
    characterized in that it comprises a communication system (15) that links between the control systems (8, 10, 11), the sensory system (3) and the user interface system (16) or between any combination of these .
    5
    [21]
    21. - Exoskeleton for assistance to the human movement according to claim 20
    characterized in that it comprises one or several on-board processing units that perform all the computational processing of one or more of the sensory (3), control (8, 10, 11) and user interface (16) systems.
    10
    [22]
    22. - Exoskeleton for assistance to the human movement according to claim 21
    characterized in that the joints that join the segments of the mechanical structure comprise an adjustable joint range and adaptable to the user's joint range, where this regulation is mechanical or electronic or programmed or automatic, or any
    15 combination of these types.
    [23]
    23. - Exoskeleton for assistance to the human movement according to claim 22
    characterized in that the mechanical regulation is carried out by means of a stop or sliding brake, by threading or by a linear displacement system.
    twenty
    [24]
    24. - Exoskeleton for assistance to the human movement according to claim 22
    characterized in that the regulation e is carried out by means of limit switches.
    [25]
    25. - Exoskeleton for assistance to the human movement according to claim 22
    25 characterized in that the programmed regulation is carried out by establishing the limits
    articular to the articular control system (8) through the user interface system (16).
    [26]
    26. - Exoskeleton for assistance to the human movement according to claim 22
    characterized in that the automatic regulation is carried out through the sensory system
    30 on board (3), which determines the user's joint range and communicates joint limits to the joint control system (8).
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    同族专利:
    公开号 | 公开日
    EP3225363A1|2017-10-04|
    US20170340504A1|2017-11-30|
    EP3225363B1|2019-07-03|
    WO2016083650A1|2016-06-02|
    DK3225363T3|2019-09-02|
    EP3225363A4|2018-08-01|
    ES2575255B1|2017-04-06|
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    ES201431763A|ES2575255B1|2014-11-27|2014-11-27|EXO SKELETON FOR HUMAN MOVEMENT ASSISTANCE|ES201431763A| ES2575255B1|2014-11-27|2014-11-27|EXO SKELETON FOR HUMAN MOVEMENT ASSISTANCE|
    DK15862885.9T| DK3225363T3|2014-11-27|2015-11-25|HUMAN MOVEMENT SUPPORT EXCLUSION|
    PCT/ES2015/070855| WO2016083650A1|2014-11-27|2015-11-25|Exoskeleton for assisting human movement|
    US15/531,266| US20170340504A1|2014-11-27|2015-11-25|Exoskeleton for assisting human movement|
    EP15862885.9A| EP3225363B1|2014-11-27|2015-11-25|Exoskeleton for assisting human movement|
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