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Simulink

Manufactured by MathWorks
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Simulink is a graphical programming environment for modeling, simulating, and analyzing dynamic systems. It provides a user-friendly interface for building and customizing block diagrams, which can represent a wide range of physical and logical systems, including electrical, mechanical, and control systems. Simulink is primarily used for rapid prototyping, design, and testing of complex systems, enabling engineers and researchers to explore system behavior and validate their designs.

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57 protocols using simulink

1

Tactile Sensing for Advanced Prosthetic Hands

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The original, sensorless fingertips of the i-limb were removed and the new fingertips with LMSs (Figure 3h) were mounted onto the i-limb using the same connection points (Figure 4). The prosthetic hand with the LMSs were next mounted onto a six DOF robotic arm (UR-10 (Universal Robots, Odense, Denmark)) to slide the hand along different surfaces and textures at different speeds (Figure 1). The hand was attached to the arm via a 3D printed mechanical adaptor with a coaxial electrical connector and a prosthetic hand lamination collar (Ossur, Reykjavik, Iceland) for stability and electrical connectivity. The robotic arm was programmed using the teach pendant to repeatedly perform the sliding contact against different surfaces and textures.
LM has high conductivity so the resistance of each LMS was approximately 1 Ω. A five-channel printed circuit board was designed to amplify the LMS signals using Wheatstone bridges (Figure S2). The amplification board was powered by the Teensy 3.6 microcontroller (PJRC, Portland, OR, USA) with 3.3 V. The LMSs were connected to the amplifier board and then sampled through the Teensy as a ROS node. The ROS master was initiated in Simulink (The Mathworks, Natick, MA, USA) and the Teensy 3.6 was a slave node that sampled and published the LMS signals to the master in Simulink. Data were recorded in Simulink with a 1 kHz sample rate (Figure 4).
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2

Comparative Statistical Analysis of Biomolecules

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The statistical model applied used one-way analysis of variance (ANOVA), using StatView for Windows (SAS, version 6.0, BrainPower Inc., 24009 Ventura Blvd. Suite 250, Calabasas, CA 91302, USA). Significance between individual means was identified using the Fisher test. When the one-way ANOVA results indicated p  <  0.05, the means were considered significantly different. The 3 means were compared two by two, using the Fisher test, and the significant differences (p  <  0.05) were marked in the tables by superscripts (a, b, c). For estimating how close the individual sample mean is to the system mean, the standard error of the mean (SEM) was calculated. The Pearson correlation for amino acids and fatty acids, and Principal Component Analysis (PCA) were obtained from the corresponding function of the Matlab & Simulink (version 2020, MathWorks Inc Bartok B. ut 15/d 1114 Budapest, Hungary) software package, used to reveal the correlation structure between the investigated parameters.
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3

Nonparenchymal Cell Control in Hepatocyte Dynamics

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Control by nonparenchymal
cells was implemented within the Matlab ODE solver using proportional-plus-integral
(PI) controllers that generate control action 1 (CA1), which influences the environmental contribution to
proliferation (kenvprol), and control
action 2 (CA2), which influences the transition
rate (kenvT), according to the
following differential equations. These control actions (CA1 and CA2) affect
the hepatocyte equations as follows: Here, SRhighss and SRlowss are the steady-state population sizes of SRhigh and SRlow,
respectively, set
to values of 0.95 and 0.05 for the simulations described in this manuscript.
The PI controller parameters were selected using the automatic tuning
function in the Simulink platform (Mathworks, Natick, MA) and are
available in Table 2.
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4

Microelectrode Array Neural Signal Processing

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Neural activity detected by the 96 recording channels of each microelectrode array was transmitted via a cable attached to a percutaneous connector during each recording session. Signals were analog filtered (4th order Butterworth with corners at 0.3 Hz and 7.5 kHz) and digitized at 30 ksps by two 128-channel NeuroPort Neural Signal Processors (Blackrock Microsystems, Salt Lake City, Utah, US). The signals from both systems were fed to custom software written in Simulink (The MathWorks, Inc.) for saving and for further processing and decoding.
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5

Cosurface-based Cell Stimulator Design

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The cosurface-based CC stimulator is composed by 12 stripe-shaped electrodes that are 2 mm wide, 1 mm thick and of different lengths (2 × 12 mm, 2 × 20 mm, 2 × 25 mm, 2 × 28 mm, 2 × 30 mm, 2 × 31 mm). A 0.5 mm gap between electrodes was set. This geometry was designed to stimulate cell cultures on petri dishes of 35 mm in diameter by positioning these cell culture-containing dishes over the stimulators, which in turn are glued to a polymeric substrate. In this configuration, the petri dish thickness prohibits cell-electrode contacts. Electrodes were fabricated in copper due to their very high electrical conductivity. Stripes were machined by conventional technology. Polystyrene dishes and polycarbonate substrates were chosen due to their very high electrical resistivity. Thicknesses of 0.5 mm for polycarbonate substrates and polystyrene dishes were used.
Excitations to power stimulators were configured using a real-time application that was developed using Simulink (v. 7.3, Mathworks) and the Real Time Workshop (v. 7.3, Mathworks) and run using the Real Time Windows Target (v. 3.3, Mathworks) kernel. Excitations were generated by an IO card (MF 624, Humusoft).
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6

Ankle Exosuit Force Control System

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A real-time target machine (Speedgoat, Liebefeld, Switzerland) ran a custom Simulink (MathWorks, Natick, MA, USA) model to drive the motors in the offboard actuator. The high-level controller in the Simulink model was designed to generate the desired force profiles over a gait cycle while not rotating the ankle joints excessively. First, the controller detected heel strikes for each leg using the foot IMU and segmented walking cycles (21 ). Then, the controller ran a PI force control loop cascaded with a current loop to track the desired force profile (66 ). While running the force control loop, the controller also monitored the Bowden cable retraction length and released the cable as soon as the motor reached a participant/task-specific maximum retraction threshold. For this, at the beginning of each active exosuit condition, a handheld controller was used to allow the participant to set the cable retraction threshold as high as possible while ensuring the assistance did not over-rotate their ankles. This approach enabled safe and robust force tracking until the end of push-off.
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7

Computer-Controlled Treadmill Experiment

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All tests were carried out on a PC-controlled treadmill (model Venus, h/p/cosmos Sports & Medical GmbH, Germany; Figure 4). The control algorithm was implemented using real-time Simulink (The MathWorks, Inc., USA) running on the PC. Heart rate was measured by a chest strap (H10, Polar Electro Oy, Finland) and transferred to the PC through a wireless receiver module (Heart Rate Monitor Interface, Sparkfun Electronics, USA) at a rate of 1 Hz. The control algorithm ran at a sample rate of 0.2 Hz (sample interval 5 s) hence the HR measurement was downsampled by averaging every five consecutive values.

The computer-controlled treadmill used in this study.

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8

Computational Model of Sensorimotor Integration

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A simple computational model of sensorimotor integration was implemented under Simulink (The MathWorks, Inc., Natick, MA, USA). The goal was to replicate empirical (behavioral) differences between the patient and the control group and to explain these differences in terms of the underlying neural control signals used in the model. This model (Fig. 4) considered three types of time-varying input signals to be integrated and to form a motor command: (i) visual information on the ramp-hold-and-release target force trajectory, (ii) inhibition modulated as a function of target force, and (iii) tactile/proprioceptive feedback. Each input signal had its own gain: V_Gain, I_Gain and TP_Gain, respectively. This motor command then entered a negative feedback-loop where the grip force (the model output) was dynamically regulated as a function of the error between the motor command and the actual grip force. Signal-dependent noise was added to the grip force. The following assumptions have been implemented:
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9

Extracellular Electrode Array Recordings and Stimulation

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Arrays of 60 Ti/Au/TiN extracellular electrodes with electrode spacing/diameter 500/30 μm, were used [Multi Channel Systems (MCS), Reutlingen, Germany]. A commercial amplifier (MEA-1060-inv-BC, MCS) with frequency limits of 150–3000 Hz and a gain of ×1024 was used to reduce noise. Data was digitized with an acquisition board (PD2-MF-64-3M/12H, UEI, Walpole, MA, USA) and sampled at a frequency of 16 Ksample/s per channel. Monophasic, 200 μs square pulse 100–1000mV voltage stimulation through extracellular electrodes was performed (Wagenaar et al., 2004 (link)), using a dedicated stimulus generator (STG 1004, MCS). Data pre-processing and online event detection were performed using a Simulink-based (The Mathworks, Natick, MA, USA) xPC target application (see Zrenner et al., 2010 (link) for details). Extracellular spikes were detected online by threshold crossing (8 × STD) of the raw voltages. Spike times and shapes, as well as −10 to +50 ms voltage traces triggered by each stimulus, were recorded from all electrodes. When we state the number of used networks, this is congruent with the number of experiments. The data were analyzed by custom MATLAB scripts (The Mathworks, Natick, MA, USA).
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10

Simulating Human Balance Behavior

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The IC model as described in section Independent Channel Model and Figure 1 was implemented in Simulink, Matlab (The Mathworks, Natick, MA, United States) with added pink noise to mimic sensory and motor noise (van der Kooij and Peterka, 2011 (link)). The human body was modeled as a single inverted pendulum and all parameters (Equation 3, Figure 1) were set to the values found in the human experiments. The same perturbation signal (section Perturbation Signal) and analyses (section System Identification and Parameter Estimation) as used in the human experiments were applied resulting in time series, FRFs, and estimated parameters describing the balance behavior simulated by the computer.
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