Design of Shape Memory Alloy-Based Soft Wearable Robot for Assisting Wrist Motion

Abstract

In this paper, we propose a shape memory alloy (SMA)-based wearable robot that assists the wrist motion for patients who have difficulties in manipulating the lower arm. Since SMA shows high contraction strain when it is designed as a form of coil spring shape, the proposed muscle-like actuator was designed after optimizing the spring parameters. The fabricated actuator shows a maximum force of 10 N and a maximum contraction ratio of 40%. The SMA-based wearable robot, named soft wrist assist (SWA), assists 2 degrees of freedom (DOF) wrist motions. In addition, the robot is totally flexible and weighs 151g for the wearable parts. A maximum torque of 1.32 Nm was measured for wrist flexion, and a torque of larger than 0.5 Nm was measured for the other motions. The robot showed the average range of motion (ROM) with 33.8, 30.4, 15.4, and 21.4 degrees for flexion, extension, ulnar, and radial deviation, respectively. Thanks to the soft feature of the SWA, time cost for wearing the device is shorter than 2 min as was also the case for patients when putting it on by themselves. From the experimental results, the SWA is expected to support wrist motion for diverse activities of daily living (ADL) routinely for patients.

1. Introduction

Loss of mobility and power in the upper extremity (UE) is a common symptom resulting from damage to the peripheral nervous system, muscle weakness, tendon disorders, muscle contracture and change in muscle tone after an accident or a medical disorder such as cerebral palsy, stroke, traumatic brain injury or damage to the spinal cord [1,2,3,4,5,6]. The disabilities of the upper extremity can manifest themselves individually more often, but they also occur in combination. Also, several of these neurological diseases are chronic as well as progressive [3,4]. Consequently, the ability to perform voluntary movement and fine motor and manipulation skills are lost [7]. This results in loss of independence during the performance of tasks required in activities of daily living (ADL) such as feeding, self-hygiene, dressing and transferring [8].

Especially for rehabilitation treatment, there is less improvement of patients in the wrist mobility compared to the shoulder or elbow. The radiocarpal joint is one of the major and complex parts of the upper extremity, comprising of bones, ligaments, nerves, tendons and connective tissues. Its anatomy allows a wide spectrum of intricate movements necessary in performing day-to-day tasks, which in turn, makes it susceptible to injuries [9]. Compression or damage to the radial, ulnar and median nerve of the wrist such as wrist drop, ulnar claw or carpal tunnel syndrome also lead to chronic wrist impairment. Owing to the motor, neurological and perceptual defects of the wrist joint, the quality of life and independence of the patient reduces along with the adverse effect on the ability to perform ADL. Moreover, the reduced mobility at the wrist results in compensatory movement of the shoulder, and the elbow [10]. In many cases, physical therapy leads to recovery by stimulating the affected muscles together with leveraging neuroplasticity [11,12]. Similarly, rehabilitation in the form of repetitive motions and exercises have resulted in restoring some degree of motor loss [13] and cortical reorganization while regaining some portion of the lost sensorimotor skills [14]. Findings of 6 months of longitudinal studies reveal that about 30 to 66% of hemiplegic patients, had little or no function in the paralyzed arm, whereas only 5 to 20% showed complete functional recovery [15]. Nevertheless, recovery is not limited to the months following stroke [16] with rehabilitation of the UE being reported many years after stroke [17]. Also, manual therapeutic rehabilitation where the therapist has to guide the paralyzed limb directly requires a daily treatment, which makes the treatment difficult and expensive [18].

In the past decades, researchers have developed many robotic rehabilitation systems [19,20,21,22,23,24,25,26,27,28,29,30,31,32,33,34,35]. A few investigations show that the improvement of recovery for acute and chronic patients facing stroke, cerebral palsy and injury to the spinal cord was observed from rehabilitation treatment by applying robotic systems [19,20,21,22,23]. Conventionally used rehabilitation robots have rigid structures and the force to the patients is delivered primarily by a motor located at the respective joint. However, these robots are not suitable in wearable applications since the rigid links and joints are heavy and bulky. Also, the limitation of the degrees of freedom (DOF) causes inconvenience for the user.

Applying soft robotic technologies is a great approach for a compact, lightweight, user-friendly and portable exoskeleton for the upper limb, since the soft actuators and sensors are lightweight, compact and have high DOFs [36,37,38,39,40,41,42,43,44,45]. Pneumatic actuators are widely used for wearable applications since they can produce high force compared to that of other soft actuators along with large deformations. Several soft wearable robots for the wrist using multiple pneumatic actuators that produce bending or linear contraction motion were suggested [36,37,38,39,40]. However, the systems that use the pneumatic actuators require compressors and regulators, which in turn makes it hard to be used as a portable robot. Tendon-driven systems are also generally employed for designing wearable robots [42,43,44,45]. The use of Bowden cables along with DC motors [42,43] or twisted coil actuators [44] allows locating the actuators away from the point of interest, reducing the weight on the wearer and mobilizing the external joints that were constrained using the rigid exoskeleton. For example, Choi et al. used a simple cable-driven wearable robot with flexible polymer structures and an active anchor to produce the dart-throwing motion of the wrist [45]. However, further improvement in the anchoring mechanism is needed to accomplish a precise and repetitive motion.

Recently, Shape Memory Alloy (SMA) has been highlighted as a potential material to be used as an artificial muscle thanks to its unique characteristics of shape memory effects [46]. The shape change of the SMA is caused by the change in crystalline arrangement with change in temperature. The actuators that are fabricated using SMA can produce high force and can be rapidly actuated via Joule heating. Also, the SMA actuators that are shaped as a coil spring are capable of producing large strains, over 200% of their initially contracted length. The wearable robots targeting the UE that utilize wire type SMA actuators have been introduced [47,48,49]. However, slow response and the need of a passive force to pre-stretch the actuator makes practical implementation for such systems difficult.

In this paper, we propose a new soft SMA-based wearable wrist robot aimed at portability and compliance, so that the wearer can use the robot independently and effortlessly. Our device focuses on the 2-DOF wrist motion occurring near the two non-aligned axis of the radiocarpal joint; namely extension, flexion and ulnar and radial deviation. In this paper, the design process of the highly stretchable, fast-response muscle-like actuator is described first by optimizing the parameters of the SMA coil spring and the cooling system of the actuator. Next, the design process and the performances of the wearable robot are described. The fabricated wearable robot can produce the 2-DOF motion of the wrist by selectively activating the muscle-like actuators. Finally, user tests were performed to observe the wearability and the range of motion (ROM). Time spent for self and assistive wearing were measured as well as the ROM of the SWA for five subjects.

2. Design of Muscle-Like Actuator Based on Shape Memory Alloy (SMA) Coil Spring

Typical type of SMA for actuator applications is in the form of wires [47,48,49,50]. The advantage of the wire-shaped SMA actuator is that it can produce high forces compared to the other soft actuator technologies such as Ionic Polymer Metal Composites [51], dielectric elastomers [52], shape-morphing polymers [53] and hydrogels [54]. However, the strain that the actuator can produce is relatively low (<8% of its initial length) [46], which is insufficient for the use in making a wearable robot. In order to enhance actuating performance, SMA can be shaped in the shape of coiled springs that result in substantially larger displacement when it is utilized as an actuator [46,55,56,57,58,59]. The coil spring shaped SMA actuators have large extension strain over 200% [46,55], which is enough for the desired application as the strain of a SMA coil spring is larger than that exhibited by human muscles [60].

Another shortcoming faced when working with SMA actuators is the slow response due to the difficulty of both heating up and cooling down the SMA rapidly in the same system. Generally, many SMA-based actuators are operated in ambient air, which offers a fast heating rate, but the limitation is a slow cooling rate as well [46,47,48,49,59]. To enhance the response speed of SMA based actuators, a few works have applied water as an alternative coolant during the actuation of the SMA [50,55,56,57,58]. Park et al. developed SMA coil spring-based actuator that was composed of the SMA coil spring bundles and a stretchable polymer tube that can stretch over 300% of its initial length [55,56,57]. The heat transfer from water activated the SMA coil spring, and the temperature of the water that flows through the tube was controlled by the faucet-like valve system, which adjusts the amount of hot and cool water from the reservoir. The above-mentioned actuator showed up to 50% contraction strain when 5kg load was applied with 1Hz actuation speed. However, this actuation method is not suitable for wearable applications since large reservoirs for hot and cool water are needed.

The highly stretchable muscle-like actuator proposed in this work is designed based on SMA coil springs and coolant circuit for a thin, high force, displacement, and fast response. Figure 1 shows the schematic design of the proposed actuator. In order to make the actuator thin, one SMA coil spring is integrated with a coolant circulation system. An electrical wire is connected to both the ends of the SMA coil spring while attaching it tightly at the end of a Polycarbonate connector containing the coolant flow inlet and outlet. The temperature of the SMA increases when the electrical current is applied to the SMA as the SMA itself is resistance. A stretchable polymer tube that is designed to surround the SMA coil spring is used for the flow of coolant. The polymer tube is made with Ecoflex 00-30 (Smooth on Co). It stretches and contracts in conjunction with the SMA coil spring thanks to its high stretchability of over 300% of its initial length. The tubes attach to the pump and the radiator was connected to the other end of the connectors. The coolant flows in closed circulation. The initial diameter of the stretchable polymer tube before stretching is selected as 7 mm. The width and height of the connectors are less than 15 mm. Mineral oil is chosen as a coolant that flows inside the tube.

In order to design the SMA coil spring for a wearable robot, the actuator parameters which determine the maximum force as well as displacement should be analyzed. Adjustable parameters for designing conventional spring are described in Figure 2. The relationship between force and displacement of the spring is Equation (1):

$$\mathrm{F}=\frac{{\mathrm{Gd}}^4}{8{\mathrm{D}}^3\mathrm{n}}\mathsf{\delta }$$

(1)

F is the force, G is the shear modulus of the SMA, d is the wire diameter of the SMA, D is the coil diameter of the SMA, n is the number of coil turns, and $\mathsf{\delta }$ is the displacement of the SMA coil spring. Shear modulus is the property of the SMA material itself, whereas D, d, and n can be changed in the fabrication process. In the case of SMA, the shear modulus G changes depending on the temperature change. In addition, the transition temperature of the SMA, which is the temperature that the phase transformation from martensite to austenite starts, can be considered as a parameter to be selected depending on the environment in which the actuator is used. In order to determine the spring parameters that optimize the performances, five samples of coil springs that have different transition temperatures, wire diameter, and spring diameter were fabricated, and the force and displacement relationships of those samples were observed. The selected values of spring parameters and the transition temperature of these five samples are displayed in

Table 1. Parameters of five shape memory alloy (SMA) coil spring samples.

Sample Number	SMA Materials	Spring Diameter (D)	Number of Turns (n)	Initial Length (mm)
1	d = 0.5 mm Transition Temperature 40 °C	3 mm	55	50
2		2.8 mm	55	50
3		2.5 mm	55	50
4	d = 0.42 mm Transition Temperature 70 °C	3 mm	55	45
5		2.5 mm	55	45

.

Several target performances of the proposed muscle-like actuator are determined for the wearable robot application. The actuator should be designed to produce high force in the desired deformation range. As preloading the SMA is required to be stretched, the target range of deformation is determined under load conditions. The target force required is 10 N per a single coil spring. The target maximum contraction ratio is selected to be greater than 40% of its initial stretched length, which exhibits a similar contraction ratio as that of a human muscle [60]. The target displacement range is selected as 50 mm from its initial stretched length when a 10 N load is applied to the spring samples. Target maximum length of the spring is selected up to 150 mm, which is a suitable size for a compact wearable robot for the wrist. In addition, a main consideration in actuator design is that the actuator should be as thin as possible to make the wearable robot portable and easy to wear. Finally, the maximum surface temperature has to be as low as possible to prevent burning of human skin since the SMA is activated by the increase of temperature.

The experimental setup for the force-displacement relationship measurement of the spring samples is shown in Figure 3. The temperature of the SMA was measured by the thermocouple and was kept constant by feedback control. For the samples that have transition temperatures of 40 °C, the temperature was controlled at 30, 40, 50, 60 and 70 °C. For the samples that have transition temperature of 70 °C, the temperature was controlled at 30, 50, 70 and 90 °C.

The graphs of the relationship between force and displacement of the sample springs at various temperatures are shown in Figure 4. Several characteristics of SMA can be observed in all the experimental results. As the temperature increases, the spring force in the same displacement increased as well. In addition, residual strains occur at low temperature as the crystalline arrangement of the SMA was converted from twinned martensite to detwinned martensite phase.

The real displacement range of the spring by temperature change is the difference of the displacements when the temperatures of the spring are 40 °C and 70 °C under 10 N load conditions. Sample 4 and 5 have relatively low stiffness compare to sample 1, 2 and 3 since the wire diameter is smaller. Additionally, the actuator has to be heated to a higher temperature to exert high force compared to other samples. Sample 1, 2 shows enough force over 10 N, but it needs larger displacement range than the target value. The optimal SMA coil spring is selected as sample 3 since it satisfies the target force in the displacement range, is the thinnest, and has the lowest transition temperature.

The fabricated SMA-based actuator is shown in Figure 5. The SMA-based actuator shows high stretchability. It can contract and release 40% of its initial stretched length with an actuation frequency of 0.5 Hz when 1 kg pre-load is applied. Since the average frequency responses of general ADLs is around 1 Hz [61], the proposed actuator can support the ADLs of low frequencies. The SMA coil spring heats up to around 70 °C in 1 s, and the temperature at the polymer tube surface reaches around 70 °C in 6 s. In addition, time spent on cooling the SMA at ambient temperature is less than 1 s.

3. Design of Soft Wrist Assist (SWA)

Wrist motion is required for the activities of daily living (ADL) like opening a door, lifting a spoon or fork for food intake, and manipulating objects. Therefore, the ultimate goal of our robot is to provide a sufficient amount of torque and ROM for 2-DOF motions of flexion/extension and ulnar/radial deviation. Another important consideration in designing the robot is that it is lightweight and easy to wear for helping patients in carrying out the ADL associated with the wrist motion routinely.

The proposed wearable robot, named soft wrist assist (SWA), consists of two parts, a wearable fingerless glove that is worn on the hand and a wearable strap that is placed on the forearm. Each end of the muscle-like actuators is strongly attached to the glove and the strap part using an adhesive (LOCTITE^® 401). The mass of the wearable part of the fabricated SWA is only 151 g, and the total mass of the robot including the pump and radiator is around 1 kg.

In this chapter, the mechanism of the human wrist motion is introduced first. Next, the mechanism and design of the robot for a 2-DOF motion of the wrist are described. Finally, the anchor design of the wearable parts is explained.

3.1. Mechanism of Wrist Motion

The wrist contains multiple joints including the radiocarpal joint, a few intercarpal joints, and five carpometacarpal joints connecting the hand to the forearm. The joints can be approximated as a single wrist joint that possesses two non-aligned rotational axes [62]. Figure 6 shows the targeted four motions of the wrist. Bending the wrist such that the palm goes closer to the anterior surface of the forearm results in flexion. Extension is the movement of the wrist toward the opposite direction of flexion. Ulnar deviation, also known as ulnar flexion, is the movement of the wrist towards the ulnar bone. The movement of the wrist towards the radius bone, which is the opposite direction of ulnar deviation results in Radial deviation. Moreover, flexion and extension occur within the transverse axis whereas ulnar and radial deviation occurs within the anteroposterior axis. Flexion and extension are antagonistic movements in the same plane, and ulnar and radial deviation are also antagonistic in the other plane.

3.2. The Alignment of the Actuator

The fabricated SWA is shown in Figure 7. To achieve 2-DOF motion of the wrist, 5 muscle-like actuators are attached to the SWA at various positions which are chosen based on the pilot studies and the anatomical placement of tendons and joints to perform the targeted motions. In addition, these positions are selected considering that the robot should not interfere with the hand motion. Three actuators are attached to the back of the hand, as shown in Figure 7b. The other two actuators are attached to the sides of the palm, as shown in Figure 7c.

Figure 8 shows the four fundamental motions of the wrist that are produced by the proposed robot. The diverse wrist motions of the SWA could be easily performed by controlling the muscle-like actuators selectively (each actuator is numbered as shown in Figure 7 to explain the mechanism easily). For example, the contraction of the actuators that are placed on the palm side (4 and 5) causes flexion, and the contraction of the actuators that are placed on the back of the wrist (1, 2 and 3) causes the extension motion of the wrist. Similarly, the contraction of the actuators that are placed on the side of the hand near the fifth finger (1 and 4) causes the ulnar deviation, and the contraction of the actuators that is placed on the side of the hand near the thumb (3 and 5) causes the radial deviation. Additionally, diverse wrist movements resulting from the combination of the motion on the different axes can be realized by activating the actuators selectively. For example, the wrist motion which combines the extension and radial deviation can be performed easily by contracting actuators 1, 2, and 4 simultaneously.

The initial stretched length of the actuators when the wrist is in the neutral position is set to 120 mm to ensure enough displacement of the actuators as well as the compact design of the robot. The distance between the actuators that are positioned at the back of the hand is selected to be 15 mm, and the distance between the actuators positioned at the palm is chosen as 60 mm.

3.3. Anchor Design

In order to prevent the dislocation of the wearable robot that occurred due to the force exerted by the muscle-like actuator, the anchoring mechanism is considered. The glove design is selected since it would possibly prevent the dislocation of the robot from the hand. Fingerless glove is adopted since the user can wear it easily compared to the full-glove design. For the wearable part located at the forearm, a strap design with Velcro that can be tightened to the forearm is adopted to make the robot easy to wear. In addition, the strap structure allows the robot to be firmly fixed for every user regardless of the forearm size. The width of the Velcro strap is 75 mm, which is selected to be wide to increase the friction. To prevent the stretch of the fabric by the force of the actuator, the wearable parts are fabricated by non-stretchable fabric.

3.4. Torque Evaluation

The torques of the four wrist motions were measured to observe the performance of the SWA. The experimental setup is shown in Figure 9. The robot was worn on a 3D-printed hand-forearm model, in which the hand and the forearm were connected via a universal joint. The universal joint was used since it had two non-aligned axes, similar functions to that shown in a real wrist joint. The maximum torque was measured when the wrist was in its neutral position. One end of a steel wire was connected to the wearable robot, and the other end of the wire was connected to a load cell that measured the tension in the wire. The torque was estimated by multiplying the distance between the universal joint and the wire by the tension [45]. The simple equation for the estimation of the torque is described in Equation (2).

$${\mathrm{M}}_{\mathrm{SMA}}={\mathrm{T}}_{\mathrm{wire}}\times \mathrm{l}$$

(2)

Table 2. Maximum torque of the robot in the direction of various wrist motions.

Wrist Motion	Flexion	Extension	Radial Deviation	Ulnar Deviation
Maximum Torque (Nm)	0.61	1.32	0.90	0.62

shows the measured maximum torques exerted by the SWA in the direction of four wrist motions. Since the largest number of actuators produce the motion in the direction of the extension, the highest torque of 1.32 Nm was measured in the direction of extension motion. In addition, torques of 0.61, 0.90, 0.62 Nm were measured in the direction of flexion, radial deviation, and ulnar deviation.

From the experimental results of torque evaluation, it is noted that the SWA can produce a maximum torque near 1.5 Nm in the direction of the extension. Additionally, the torques measured in all other directions were higher than 0.5 Nm. Since most ADL that use the wrist motion requires the torque less than 1.5 Nm [63], it is expected that the proposed SWA can support wrist motion executed during some ADL that do not require relatively high torque.

3.5. User Test

Wearability and ROM are also the important factors that have to be considered, as the SWA is focused on patients who have difficulties in manipulating the wrist. To observe the performances in these factors, several experiments were conducted. In all experiments, five healthy subjects (all male), with no impairment in the upper arm, were tested. Tests were conducted after obtaining informed consent from the participants. The average ages of the subjects are 24.2 years.

The ROM in the four directions were measured by the use of image capture, similar to the motion capture measurement [64]. The markers were attached to the wrist joint, hand, and forearm respectively, and the ROM was measured by calculating the angles formed by these three markers after the device was maximally rotated. In the experiment, the subjects were instructed to relax their wrist. Therefore, the wrist motion was made passively only by the robot. Figure 10a shows the average ROMs for the four wrist motions. The average ROMs of five subjects were 33.8, 30.4, 21.4, and 15.4 degrees for flexion, extension, radial deviation, and ulnar deviation respectively. The greatest ROM was measured in flexion motion, while the smallest ROM was measured in ulnar deviation motion. The standard deviations of the ROM of flexion and extension motion are around 13, which is the directions that have large ROM. The lowest standard deviation is observed in ulnar deviation, around 3.

The ROM produced by the robot showed variation depending on the person wearing it since the size of the wrist, arm and hand of each person is different from the rest. Additionally, the difference due to the passive stiffness of the wrist of each individual can be another factor that accounts for the dissimilarity. Therefore, when designed according to the size of the hand and wrist of each user, the SWA can generate a large amount of ROMs that are adequate for the wrist ADLs. Furthermore, since the SWA is designed by simply attaching multiple SMA-based actuators at desired locations, the torque and ROM can be easily increased by attaching additional actuators to the robot.

The wearability is assessed by measuring the time spent wearing the robot. The experiments were conducted in consideration of the fact that the robot is designed to be used by patients who have difficulties in manipulating lower arm. Two scenarios were provided for the experiments; self and assistive wearing. The self-wearing experiment was conducted to observe how easily the patients could wear the robot on their own. Therefore, the subjects wore the robot on the passive hand, by using only one hand in this experiment. In the assistive wearing experiment, the time that it takes to attach the robot to the patients by an assistant was measured.

Figure 10b shows the measured average wearing times of two experiments. The average time spent on self-wearing was measured as 87 s. The average assistive wearing time was measured at 75 s. The step that consumed the most time was inserting fingers into the glove in both experiments. The fact that it takes less than 2 min to wear the robot indicates that the proposed robot system can be worn easily. In particular, the experimental result of the self-wearing implies that the proposed robot can be worn solely by the patient with only one hand in about 80 to 90 s. Therefore, the patients facing motor impairments in their wrist can also wear the robot without the need for external assistance.

4. Conclusions and Future Work

A need for wearable robots that are flexible, easy to wear, lightweight and provide enough force has increased for patients who have difficulties in manipulating their bodies. This paper shows the first step in the development of a new type of soft wearable robot. We demonstrated an SMA-based soft wearable robot made for the assistance of wrist motion. To design a wearable robot that possesses such advantages for supporting the wrist, several design processes are carried out. To design a wearable robot that possesses such advantages for assisting the wrist, several design processes are carried out in this paper. Firstly, a highly stretchable muscle-like actuator is designed to achieve the target performances of force and contraction ratio required for wearable applications. The optimal design of the SMA coil spring is selected by comparing the force-displacement relationships of five coil springs samples. In order to enhance the response speed, an active cooling system using mineral oil was integrated with the SMA coil spring. The fabricated muscle-like actuator shows a maximum force of 10 N and a maximum contraction ratio of 40% respectively. Furthermore, by attaching the proposed muscle-like actuators to multiple positions on a wearable anchor, we propose a new soft wearable robot for the wrist named SWA, which is able to assist the 2-DOF motion of the wrist. The fabricated SWA is totally flexible and lightweight. The mass of the wearable parts of the robot was only 151 g. Additionally, the highest torque measured was 1.32 N for wrist extension, while the robot provided a torque of higher than 0.5 Nm for the other wrist motions.

In order to observe the wearability and the ROM of the robot, we conducted user tests on five healthy male subjects with no impairment in the upper extremity. The average ROM is measured as 33.8, 30.4, 21.4, and 15.4 degrees for flexion, extension, radial deviation, and ulnar deviation. In addition, the wearability of the SWA was observed by measuring the time cost for wearing the device. The self-wearing time is measured as 87 s, and the assistive wearing time is measured as 75 s. The experimental results imply that the SWA can be used routinely to assist patients facing motor impairments at the wrist since it can be worn easily, even when under single hand use.

However, there are some issues that have to be resolved in the design process. Firstly, although we designed the anchor system that prevents the dislocation of the wearable parts, it could not be perfectly prevented. Additional anchoring at the forearm to increase the fixation force can be applied. Secondly, since the size and the shape of the hands and forearms vary from person to person, the force and motion imbalance resulting from the misalignment of the actuators can occur while using the robot. In order to optimize the robot performances for all users, the attachment positions of the actuators should be easily modified, while having strong fixing force when it is attached. Adopting locking mechanisms that allow fixing the actuators on the wearable anchor regardless of the attachment position can be considered.

As a future work, we will integrate highly stretchable skin patch-like sensors fabricated using a stretchable polymer and a waved optical fiber with the proposed robot to measure its position. Furthermore, the position of the wrist can be possibly controlled by feedback provided from the integrated sensors. Recognizing the intention of the users by adopting intention sensing systems like EMG, force, or ultra-sensitive strain measurement systems will be covered in upcoming studies. We expect that the development of the SWA could be helpful for patients who have difficulties in manipulating their lower arm by suggesting a new portable assistive wearable robot that supports the wrist motion in everyday ADL.