Mapping Three Electromyography Signals Generated by Human Elbow and Shoulder Movements to Two Degree of Freedom Upper-Limb Robot Control

This article sought to address issues related to human-robot cooperation tasks focusing especially on robotic operation using bio-signals. In particular, we propose to develop a control scheme for a robot arm based on electromyography (EMG) signal that allows a cooperative task between humans and robots that would enable teleoperations. A basic framework for achieving the task and conducting EMG signals analysis of the motion of upper limb muscles for mapping the hand motion is presented. The objective of this work is to investigate the application of a wearable EMG device to control a robot arm in real-time. Three EMG sensors are attached to the brachioradialis, biceps brachii, and anterior deltoid muscles as targeted muscles. Three motions were conducted by moving the arm about the elbow joint, shoulder joint, and a combination of the two joints giving a two degree of freedom. Five subjects were used for the experiments. The results indicated that the performance of the system had an overall accuracy varying from 50% to 100% for the three motions for all subjects. This study has further shown that upper-limb motion discrimination can be used to control the robotic manipulator arm with its simplicity and low computational cost.


Introduction
In the recent past, robots have turned to be an integral part of the society with applications in industrial processes and manufacturing, military, welfare and healthcare systems, transportation, and autonomous vehicles, to name a few [1,2]. Robots in automation are fueled by the inherent virtue of machines in doing monotonous tasks with repeatable precision over a lengthy duration. In contrast to human labor, robots require fewer safety precautions, which makes them ideal for handling dangerous elements and disasters [1,2]. As an application area, the COVID-19 pandemic that has hit the world is a good case for the usage of robots in monitoring and delivery of essential services safely without compromising the safety of the medical staff [3].
Robots have been in use in various aspects of human life, as earlier mentioned. Regarding the control mechanism, modes of application of robot can be broadly categorized as autonomous, cooperative, and or hybrid mode [4]. Autonomous mode, in this case, is defined to capture all control schemes that do not require human intervention. This is the case in most often used as control schemes. The objective, in this case, is to characterize motion, gripping force, rotation of angles, and others [5,11,18,27,[29][30][31][32].
The main objective of this experiment is to investigate the application of wearable EMG device to control a robot arm in real-time. The focus is on EMG signal control corresponding to upper-limb motions of the arm and to analyze its relations. The control scheme is non-pattern recognition in nature, specifically ON/OFF control with threshold level control. This motivation for the usage of this scheme was informed by its simplicity and low computation cost. However, the method has been reported to have reduced accuracy compared with other pattern-based methods [24].
The authors in [33] proposed the use of pattern recognition control mechanism for a malfunctioning upper-limb prosthesis. In this control scheme, only a single degree of freedom (DOF) movement (hand open/close or wrist flexion/extension) was supported at any one time. This paper target multiple DOF with fewer electrodes on the upper limb. Besides, the limitation of the DOF, conventional amplitude-based control method has a slow response and takes time for the users to learn to contract/co-contract the targeted upper-limb muscles [1,25,26,33,34].
In this research, the EMG signal corresponding to upper-limb motions consisting of elbow and shoulder joints is discriminated to control a robot arm applicable in the teleoperated robot cooperation system. A low-cost wearable embedded system was customized to conduct three motions corresponding to the motion of the elbow joint and shoulder joint in real-time to the robot manipulator. The robot manipulator is a compact serial communication robot and suitable for use in home or experiment environments. Three pairs of surface EMG sensors were mounted on the Anterior deltoid, Biceps brachii, and Brachioradialis as the target muscles.
Three different motions were proposed for analysis; the elbow flexion as motion 1, shoulder flexion as motion 2, and a combination of elbow and shoulder flexion movement called the uppercut motion as motion 3. In the recording of the EMG signal, the upper limb of motion 1 and motion 2 are limited to a range of up to 90 degrees for modeling of the relation of EMG and joint angle. The contribution of this study is the development of a control scheme for a robot arm based on the Electromyography and the influence of the position of the EMG muscle targeted and its relationship to upper-limb movements. The targeted muscles are those that play an active role in the movement of the upper arm involving the elbow and shoulder joints. The initial hypothesis from this research is that the brachioradialis muscle (EMG channel 1/CH1) and biceps brachii (CH2) will play a role in movement 1, while the anterior deltoid muscle (CH3) will play a major role in motion 2 and motion 3.
The rest of this document is divided as follows: Section 2 covers the methodology, setup, and materials used. Section 3 summarizes the results from the experiment highlighting the significance of the results in the discussion, and finally, Section 4 offers the conclusion. Figure 1 shows an overview of the proposed control scheme. The system comprises of EMG signal acquisition system, processing unit, motion discrimination model/algorithm, and robot control mechanism. First, three target muscles were selected that are representative of arm muscle activity during motion. Data acquisition was performed on muscle surface using silver chloride electrodes (Ag/AgCl, size: 57 × 48 mm, Biorode, Japan). A combination of three different motion comprising of single and double DOF were recorded.

Proposed System Overview
The flowchart in Figure 2 describes the flow from the beginning until the end of the robot control. EMG measurement system featured a sensor circuit comprising of an instrumentation amplifier and an operational amplifier. The detailed schematic circuit can be found in reference [14]. The system employed an analog band-pass filter with a lower cut-off frequency of approximately 7 Hz and an upper cut-off frequency of 589 Hz and differential amplifiers' adjustable gain set to around 59-65 dB for each channel. Data acquisition unit comprised of National Instruments (NI) Corporation USB-6008 Robotics 2020, 9, 83 4 of 14 for analog to digital conversion and a personal computer (PC) i5 2.7 GHz Let' note Panasonic. In the offline mode, signals were acquired at a sampling rate of 2 kHz. We used MATLAB ® software for subsequent signal processing. The flowchart in Figure 2 describes the flow from the beginning until the end of the robot control. EMG measurement system featured a sensor circuit comprising of an instrumentation amplifier and an operational amplifier. The detailed schematic circuit can be found in reference [14]. The system employed an analog band-pass filter with a lower cut-off frequency of approximately 7 Hz and an upper cut-off frequency of 589 Hz and differential amplifiers' adjustable gain set to around 59-65 dB for each channel. Data acquisition unit comprised of National Instruments (NI) Corporation USB-6008 for analog to digital conversion and a personal computer (PC) i5 2.7 GHz Let' note Panasonic. In the offline mode, signals were acquired at a sampling rate of 2 kHz. We used MATLAB ® software for subsequent signal processing.

EMG Analysis
The experimental setup involved multichannel EMG signal detection. Control is achieved by the introduction of a threshold to discriminate the state of muscle activation. The signals were processed   EMG measurement system featured a sensor circuit comprising of an instrumentation amplifier and an operational amplifier. The detailed schematic circuit can be found in reference [14]. The system employed an analog band-pass filter with a lower cut-off frequency of approximately 7 Hz and an upper cut-off frequency of 589 Hz and differential amplifiers' adjustable gain set to around 59-65 dB for each channel. Data acquisition unit comprised of National Instruments (NI) Corporation USB-6008 for analog to digital conversion and a personal computer (PC) i5 2.7 GHz Let' note Panasonic. In the offline mode, signals were acquired at a sampling rate of 2 kHz. We used MATLAB ® software for subsequent signal processing.

EMG Analysis
The experimental setup involved multichannel EMG signal detection. Control is achieved by the introduction of a threshold to discriminate the state of muscle activation. The signals were processed

EMG Analysis
The experimental setup involved multichannel EMG signal detection. Control is achieved by the introduction of a threshold to discriminate the state of muscle activation. The signals were processed with a conventional signal processing start from classical EMG signal acquisition, EMG feature extraction, and EMG motion mapping/model. The acquired raw EMG signal was first processed to remove zero-offset, rectified, and filtered to smoothen the signal. Although the necessary analog filter already performed in the EMG measurement device, digital filter processing, as recommended by the previous researcher [31,35,36] was conducted. The band-pass filter having a bandwidth of 10-400 Hz was applied using the MATLAB signal processing toolbox to remove high random frequency interferences, noise introduced in the digitalization process, and remaining low-frequency noises from the motion artifacts, etc.
Feature extraction employed in this research was in time-domain. The method is often used because of its quick and simple implementation. Time-domain features are processed without any signal transformation for the raw EMG signals and evaluated based on the value of signal amplitude that varies over time [1,22,28,30,32,33,37]. Processing of the raw data is critical to remove baseline noises, motion artifact noises, etc. An essential part of this paper is the analysis of the EMG signal. The acquired signal is passed through equation 1 for rectification and smoothing (by moving average) as shown below.
where M is the smoothing window size, and n is the current sampling point, x is the raw EMG signal from DAQ. The output Y[n] represents the processed EMG signal of the anterior deltoid, biceps brachii, and brachioradialis muscles, respectively [14]. After getting the processed EMG signal, the signal was normalized to obtain a uniform distribution discernable by a specified threshold. Equation (2) shows the operation.
where Y[n] (min) is the minimum value of the processed signal, and Y[n] (max) is the maximum. Discrimination of active motion was done by identifying different features of three EMG channels (Ch1, Ch2, and Ch3). In this case, we used the features as the control parameters. Three control parameters were applied; the mean of the envelope signal, the maximum value of the amplitude, and the area under the curve. These steps consisted of how to overcome the desired output from the signal features. As earlier mentioned, to discriminate the activation state of the muscles from each channel, we proposed the threshold method. The control parameters determine whether the threshold will be activated or not. The threshold method determined muscle activation state (MS), which was expressed as muscle activation (ON) or muscle deactivation (OFF). The ON state was returned if the signal was above the baseline threshold of the envelope signal whereas, an OFF state resulted whenever the rectified signal was below the baseline threshold. The choice of the threshold was advantageous in aiding the removal of any residual noise of the envelope signal [38]. The muscle state is defined as in (3): where EMGnorm is represented as normalized and filtered EMG signal and n represent either channels 1, 2, or 3 of EMG. To evaluate the performance of the controlling parameter, the successful mapping rate at the times that the robot arm mimics the motion of the subject's upper-limb motion correctly out of the total number of trials was determined.

Robot Control
Custom assembled R-R-R (three revolute joints) configuration robot arm shown in Figure 3c, assembled from the Dynamixel unit was used in this research work for experiments. Dynamixel AX-12A is a smart actuator with a fully integrated DC servo motor module. The input voltage rating is around 9.0-12 V, which can produce a speed of 59 rpm with a rotation angle (max) of 300 degree, and resolution of 0.2930 deg/pulse. Four actuators were assembled as a robotic arm with two links and three joints, as shown in Figure 3b. In this research, two motors are needed to move the robot joint according to the movement of the shoulder joint and elbow joint.
Robot-PC communication was achieved by using a serial connection between MATLAB and the motor controller connected to the computer via USB. Servo motor controller is a small size universal serial bus (USB) communication converter that enables the interfacing and operation of the actuators from the computer. It also supports 3 pin TTL connectors that used to link up with the Dynamixel motor.

Target Upper Limb Motion
Human upper-limb movement is one of the most complex motions and involves many components such as musculoskeletal, nerves, and others to support multiple degrees of freedom. The upper limb conducts many motions that require coordination of the joint, which consists of many ranges of motions for daily life tasks. To make the scope of the research more specific, we focus on the shoulder and elbow joints moving separately to represent single DOF movements and a combination of two joints to achieve multiple DOF. The combination of three motion gesture is as illustrated in Figure 4a. Shoulder motion allows three DOFs (i.e., abduction/adduction, flexion/extension, and internal/external rotation). Elbow motion has two DOFs (i.e., flexion/extension and supination/pronation) [36,39].
Targeted muscles were selected, incorporating the motion which is applied. EMG signals were captured from Brachioradialis, Biceps Brachii, and Anterior Deltoid muscles using bipolar electrode placement and one common electrode as reference (ground) placed on the bony part of the elbow as shown in Figure 4b. Robot-PC communication was achieved by using a serial connection between MATLAB and the motor controller connected to the computer via USB. Servo motor controller is a small size universal serial bus (USB) communication converter that enables the interfacing and operation of the actuators from the computer. It also supports 3 pin TTL connectors that used to link up with the Dynamixel motor.

Target Upper Limb Motion
Human upper-limb movement is one of the most complex motions and involves many components such as musculoskeletal, nerves, and others to support multiple degrees of freedom. The upper limb conducts many motions that require coordination of the joint, which consists of many ranges of motions for daily life tasks. To make the scope of the research more specific, we focus on the shoulder and elbow joints moving separately to represent single DOF movements and a combination of two joints to achieve multiple DOF. The combination of three motion gesture is as illustrated in Figure 4a. Shoulder motion allows three DOFs (i.e., abduction/adduction, flexion/extension, and internal/external rotation). Elbow motion has two DOFs (i.e., flexion/extension and supination/pronation) [36,39].

Experimental Design
Five healthy, right-handed subjects (all males) with ages ranging from 20 to 40 years participated as volunteers for the experiment. All of them provided written informed consent following approval procedures (number 27-226) issued by Gifu University ethics committee. The issue is the application to motion intention estimation and device control based on biological signal measurement considering user-specific physical characteristics and environmental characteristics. The experiment was conducted with subjects seated comfortably in a chair with right arm rested (0-degrees). For familiarization, the participants performed several arm motions prior to recording as well as get a proper threshold for individual calibration.  Targeted muscles were selected, incorporating the motion which is applied. EMG signals were captured from Brachioradialis, Biceps Brachii, and Anterior Deltoid muscles using bipolar electrode placement and one common electrode as reference (ground) placed on the bony part of the elbow as shown in Figure 4b.

Experimental Design
Five healthy, right-handed subjects (all males) with ages ranging from 20 to 40 years participated as volunteers for the experiment. All of them provided written informed consent following approval procedures (number 27-226) issued by Gifu University ethics committee. The issue is the application to motion intention estimation and device control based on biological signal measurement considering user-specific physical characteristics and environmental characteristics. The experiment was conducted with subjects seated comfortably in a chair with right arm rested (0-degrees). For familiarization, the participants performed several arm motions prior to recording as well as get a proper threshold for individual calibration.
During recording, the participants were instructed to raise and lower the arm, as shown in Figure 4a within 2 s. Every motion was repeated 10 times in offline mode. In online mode, the robot was moved with successive arm motion for visual feedback. The robot arm control was initially conducted in offline mode. The EMG data loaded as an input for controlling the robotic arm.
From Formula (3), if we represented MS(CH1) as A, MS(CH2) as B, and MS(CH3) as C, discrimination of the active motion is handled by the control algorithm with conditions shown in (4). Motion 1, motion 2, and motion 3 are deduced conditional manipulations of signals from the three channels. In particular, when the EMG signal from both CH1 and CH2 is above the baseline TH (threshold), and CH3 is below the threshold; the command to activate motion 1 is classified as ON, as shown in Equation 3. Similarly, if either CH 1 or CH2 is lower than the threshold and CH3 is higher than the threshold, then motion 2 is ON. Finally, motion 3 is solely dependent on all channels that are greater than the threshold.

I f A > Th and B > Th and C < A then It is Condition 1 I f A < Th or B< Th and C >Th then It is Condition 2 I f A > Th and B > Th and C > Th It is Condition 3
(4) Table 1 shows the discriminations status for each EMG signal related to the movements of the robot arm. Angle θ 1 (shoulder joint) and θ 2 (elbow joint) are joint angles.

Results and Discussion
The following section describes the experiment, signal processing, and robot control model results. The output of the processed EMG is used for controlling the robotic manipulator. Figure 5 shows three channels and raw EMG signals matrix captured for 2 s. From the figure, motion 1 produces a higher EMG signal on Ch1 (column 1) and Ch2 (column 2) compared to Ch 3 (column 3). The second row describes the results of motion 2, the muscles that are most active to produce the EMG signal voltage are the anterior deltoid (Ch3) and bicep brachii (Ch2) muscles, while the brachioradialis muscles tend to produce minimal tension. Meanwhile, motion 3 is seen in the third line, where all channels appear to generate EMG signal activity. motion 1 produces a higher EMG signal on Ch1 (column 1) and Ch2 (column 2) compared to Ch 3 (column 3). The second row describes the results of motion 2, the muscles that are most active to produce the EMG signal voltage are the anterior deltoid (Ch3) and bicep brachii (Ch2) muscles, while the brachioradialis muscles tend to produce minimal tension. Meanwhile, motion 3 is seen in the third line, where all channels appear to generate EMG signal activity.  Figure 6 shows the result of EMG after rectification. Rectification basically yields the magnitude of the signal without its polarity. The full-wave rectified results show oscillatory input of the muscles from the neural activation that EMG signals. This is inherent in all EMG signals, and hence, further processing is necessary to ensure usability. Further processing is performed to arrive at a processed signal.  Figure 6 shows the result of EMG after rectification. Rectification basically yields the magnitude of the signal without its polarity. The full-wave rectified results show oscillatory input of the muscles from the neural activation that EMG signals. This is inherent in all EMG signals, and hence, further processing is necessary to ensure usability. Further processing is performed to arrive at a processed signal. The results of the normalized and processed signal are shown in Figure 7. From the figure, the onset of raising hand motion is clearly discernable as well as lowering motion. From the design of the experiment, 2 s was found sufficient to capture all the motion. Motion 3 had the strictest time budget, while motion 1 had excess time that resulted in the capturing of motion not related to the research. This excess motion included wrist flex, as will be discussed later. The results of the normalized and processed signal are shown in Figure 7. From the figure, the onset of raising hand motion is clearly discernable as well as lowering motion. From the design of the experiment, 2 s was found sufficient to capture all the motion. Motion 3 had the strictest time budget, while motion 1 had excess time that resulted in the capturing of motion not related to the research. This excess motion included wrist flex, as will be discussed later. The results of the normalized and processed signal are shown in Figure 7. From the figure, the onset of raising hand motion is clearly discernable as well as lowering motion. From the design of the experiment, 2 s was found sufficient to capture all the motion. Motion 3 had the strictest time budget, while motion 1 had excess time that resulted in the capturing of motion not related to the research. This excess motion included wrist flex, as will be discussed later.   Figure 8 shows the comparison of three control parameters; mean of the envelope (shown as Mean in the figure), maximum amplitude (Max), and area under the curve (AUC) of the envelope signal (Area). From the results, the AUC of the signal shows more consistency in the accuracy of successful control for each motion better than the Mean and Max methods. Besides the comparison of accuracy, the consistency of the results for different motions was an important factor to consider in choosing the model for the robot arm control. It can be seen in Figure 8 that the Area shows the highest level of accuracy compared to other parameters for each movement. Also, the consistency, calculated as average error for each control parameter, was least in the AUC method. The average error of AUC was 10.1% compared to the Mean and Max methods that reported an error of 13.1% and 14.3%, respectively. From this, AUC parameter is maintained in the rest of the document for inter-subject evaluation of performance. Figure 9 shows the robotic arm motion corresponding to the discriminated motion. From Figure 9a, which corresponds to Motion 1, brachioradialis muscle (CH1) and biceps brachii (CH2) surpass the baseline threshold. In Figure 9b for motion 2, CH2 and CH3 surpass the threshold, with CH2 being more dominant. In motion 3, all the channels surpass the threshold. From this, it can be seen that anterior deltoid muscle (CH3) plays a major role in motion 2 and motion 3. Biceps brachii (CH2) is equally significant in motion 2 and 3 but more pronounced in motion 3. This can be understood intuitively by the extended nature of motion 2, compared to the clenched elbow joint in motion 3. A visualization of motion and corresponding robot manipulation can be found in this link: https://rb.gy/lfq1iv. The video illustrates controlling a robotic arm using EMG signals in an offline system. successful control for each motion better than the Mean and Max methods. Besides the comparison of accuracy, the consistency of the results for different motions was an important factor to consider in choosing the model for the robot arm control. It can be seen in Figure 8 that the Area shows the highest level of accuracy compared to other parameters for each movement. Also, the consistency, calculated as average error for each control parameter, was least in the AUC method. The average error of AUC was 10.1% compared to the Mean and Max methods that reported an error of 13.1% and 14.3%, respectively. From this, AUC parameter is maintained in the rest of the document for inter-subject evaluation of performance.  Figure 9 shows the robotic arm motion corresponding to the discriminated motion. From Figure  9a, which corresponds to Motion 1, brachioradialis muscle (CH1) and biceps brachii (CH2) surpass the baseline threshold. In Figure 9b for motion 2, CH2 and CH3 surpass the threshold, with CH2 being more dominant. In motion 3, all the channels surpass the threshold. From this, it can be seen that anterior deltoid muscle (CH3) plays a major role in motion 2 and motion 3. Biceps brachii (CH2) is equally significant in motion 2 and 3 but more pronounced in motion 3. This can be understood intuitively by the extended nature of motion 2, compared to the clenched elbow joint in motion 3. A visualization of motion and corresponding robot manipulation can be found in this link: https://rb.gy/lfq1iv. The video illustrates controlling a robotic arm using EMG signals in an offline system. error of AUC was 10.1% compared to the Mean and Max methods that reported an error of 13.1% and 14.3%, respectively. From this, AUC parameter is maintained in the rest of the document for inter-subject evaluation of performance.  Figure 9 shows the robotic arm motion corresponding to the discriminated motion. From Figure  9a, which corresponds to Motion 1, brachioradialis muscle (CH1) and biceps brachii (CH2) surpass the baseline threshold. In Figure 9b for motion 2, CH2 and CH3 surpass the threshold, with CH2 being more dominant. In motion 3, all the channels surpass the threshold. From this, it can be seen that anterior deltoid muscle (CH3) plays a major role in motion 2 and motion 3. Biceps brachii (CH2) is equally significant in motion 2 and 3 but more pronounced in motion 3. This can be understood intuitively by the extended nature of motion 2, compared to the clenched elbow joint in motion 3. A visualization of motion and corresponding robot manipulation can be found in this link: https://rb.gy/lfq1iv. The video illustrates controlling a robotic arm using EMG signals in an offline system.  The results of the comparison of intersubject performance carried out in the experiments are shown in Figure 10. It shows the accuracy of the output of successful robot control out of the repetition for the five subjects. The accuracy for each subject varied from 50% to 100% for the three motions. Motion 1 had the highest consistency than others.
The results of the comparison of intersubject performance carried out in the experiments are shown in Figure 10. It shows the accuracy of the output of successful robot control out of the repetition for the five subjects. The accuracy for each subject varied from 50% to 100% for the three motions. Motion 1 had the highest consistency than others. Subjects 1, 2, and 4 controlled the robot with more than 70% accuracy while 3 and 5 reported trouble, particularly in motion 2 and 3, which ranged between 50-60%. This was attributed to inconsistent muscle activity during recording. Muscle inconsistency resulted from excessive force employed during motion that is not part of the target muscle activity. This included wrist motions (fist crunching, flexing, or rotations), among others. The discrepancy in the muscle activation introduced difficulty in proper threshold determination. Additionally, we noted timing errors in motion 3 to be a challenge for the two subjects. Besides the motion artifacts, noise and other crosstalk artifacts affected the quality of the signal and thereby affected the prediction of intention from the signal, which is expected from EMG processing [1,22,25]. This presented as overshoots and oversaturation in the amplification gain whenever the users overexerted the motions. This was remedied by familiarization repetitions and feedback from the experimenter during preparatory steps.
From the above, the implementation of upper arm control using the two main joints of the elbow and shoulder is possible. The EMG signal obtained from the movement of the upper arm can be observed and the movement mapped. Based on Farina et al. [40], there are several criteria for implementing ideal prosthetic arm such accuracy, intuitively, robustness, adaptive for the user, the minimum number of electrodes, short and easy training/calibration, feedback on relevant functions/close loop control, limited computational complexity, low consumptions, response time. There is no ideal system to date that meets all of the criteria, but several researchers have tried at least some of these criteria. In this research, we have attempted to optimize target muscle and characterize the upper-limb motion for 2D robot control. The challenge with the approach is a priori knowledge of the sensor data required to inform the choice of threshold. An adaptive threshold determination algorithm and pattern recognition will be explored to further the research. Overall, the development of a measurement control system that improves accuracy, robustness, response time can be attained from this control scheme. Subjects 1, 2, and 4 controlled the robot with more than 70% accuracy while 3 and 5 reported trouble, particularly in motion 2 and 3, which ranged between 50-60%. This was attributed to inconsistent muscle activity during recording. Muscle inconsistency resulted from excessive force employed during motion that is not part of the target muscle activity. This included wrist motions (fist crunching, flexing, or rotations), among others. The discrepancy in the muscle activation introduced difficulty in proper threshold determination. Additionally, we noted timing errors in motion 3 to be a challenge for the two subjects. Besides the motion artifacts, noise and other crosstalk artifacts affected the quality of the signal and thereby affected the prediction of intention from the signal, which is expected from EMG processing [1,22,25]. This presented as overshoots and oversaturation in the amplification gain whenever the users overexerted the motions. This was remedied by familiarization repetitions and feedback from the experimenter during preparatory steps.
From the above, the implementation of upper arm control using the two main joints of the elbow and shoulder is possible. The EMG signal obtained from the movement of the upper arm can be observed and the movement mapped. Based on Farina et al. [40], there are several criteria for implementing ideal prosthetic arm such accuracy, intuitively, robustness, adaptive for the user, the minimum number of electrodes, short and easy training/calibration, feedback on relevant functions/close loop control, limited computational complexity, low consumptions, response time. There is no ideal system to date that meets all of the criteria, but several researchers have tried at least some of these criteria. In this research, we have attempted to optimize target muscle and characterize the upper-limb motion for 2D robot control. The challenge with the approach is a priori knowledge of the sensor data required to inform the choice of threshold. An adaptive threshold determination algorithm and pattern recognition will be explored to further the research. Overall, the development of a measurement control system that improves accuracy, robustness, response time can be attained from this control scheme.

Conclusions
This paper presented an EMG investigation of the upper-limb motion-based interface for human-robot interaction in terms of teleoperation tasks. This research demonstrates that three EMG signals that correspond with upper-limb motions have been discriminated and applied successfully for controlling the robotic arm. The area under the curve parameter control yielded more consistency in performance better than the mean and maximum amplitude signals of parameter control. Based on the model's discrimination that generated from the EMG signals envelope using moving average processing signal, the result shows that models can be used for all subjects to control the robotic arm for conducting single and two DOF movements with its simplicity and low computation cost. Also, the performance of the systems statistically describes the accuracy of all motion for all subjects that varies from 50% to 100%. Further developments will include an improved control scheme using pattern recognition, and better methods can be used to tackle the limitation of the system.