The project is funded by the Engineering and Physical Sciences Research Council EPSRC (EP/K503745/1), National Institute for Health Research (NIHR) Biomedical Research Centre (BRC) (BRC272/HI/JG/101440) and the UCL change makers.

The protocol follows the guidelines of the University College London&#39;s human research ethics committee.
CAUTION: This protocol contains an electrical hazard and a burn hazard (soldering iron); read both before attempting this protocol. This protocol includes connecting a device to skin. Ensure that at no time there is a path between the skin and electricity mains. Never touch the element of the soldering iron. Hold wires to be heated with tweezers or clamps. Keep the cleaning sponge wet during use. Always return the soldering iron to its stand when not in use. Never put it down on the workbench. Turn unit off and unplug it when not in use.
1. Assembling the Base Components
NOTE: Figure 3 gives a high-level overview of the protocol steps.
<ol>
	<li>To build the Bionic Clicker MK I, plug the bio-signals sensor shield into the microcontroller and screw the EMG cables into the E, M and GND screw terminals of the shield (see Figure 4). Continue to step 1.6.</li>
	<li>To build the MK II, place a row of three header pins into the muscle sensor in the +, - and SIG holes (see Figure 5) from above, and solder underneath.
	<ol>
		<li>Bend the header pins 90 &#176; with a pair of plyers halfway up the pins. This places the pins in the correct position for the case.</li>
		<li>If using the abductor indicis muscle as the input, continue to step 1.3, if not move to step 1.4.</li>
	</ol>
	</li>
	<li>Remove the short black reference cable from the muscle sensor.
	<ol>
		<li>Cut the three EMG cables with a wire cutter to run from the wrist to the back of the hand. Strip the end of the three EMG cables with a wire stripper.</li>
		<li>Place the stripped end of the black wire into the R hole, the blue wire into the E hole, and the red wire into the M hole of the muscle sensor (Figure 5). Solder the wires in place on the underside of the muscle sensor. Move to step 1.5.</li>
	</ol>
	</li>
	<li>Clip two electrode pads into the underside of the muscle sensor and one electrode into the connector of the black reference cable.
	<ol>
		<li>Stick the muscle sensor onto the selected muscle with the electrode pads and place the black reference electrode in an appropriate place.</li>
	</ol>
	</li>
	<li>Cut 8 single-core multi-thread wires to length and strip each end: 5 short (7 cm) wires to run from the microcontroller to the control board (red, black, green, white and blue) and 3 longer (approximately 12 cm but dependent on wrist size) wires (red, black and green) to run from one side of the wrist to the other. 
	NOTE: If placing the muscle sensor on a different muscle make sure that the longer wires will run from the muscle sensor site to the wireless microcontroller site.
	<ol>
		<li>Place the wires into the microcontroller ready for soldering: 2 red wires into the 3V hole, 2 black wires into the GND hole, the long green wire into the A0 hole, the short blue wire into the 2 hole, the long white wire into the 3 hole, and the short green wire into the 5 hole. Solder the wires in place on the underside of the microcontroller.</li>
		<li>Solder the other end of the 3 long wires to 3 header sockets in the order: red, black, green. See Figure 5. If not using the abductor indicis muscle proceed on to step 2.</li>
	</ol>
	</li>
	<li>Place the EMG sensor pads on the hand, as shown in Figure 6, with two of the electrodes at either end of the abductor indicis muscle and one EMG sensor pad on the middle of the back of the hand.
	<ol>
		<li>Clip the electrode pads into the connector end of the muscle sensor cables (push fit). The blue and red electrodes clip above the muscle, the black electrode clips on the back of the hand.</li>
	</ol>
	</li>
</ol>
2. Test EMG Output
<ol>
	<li>Download the library for the bio-signals shield following the link14 from the reference section. Unzip it and place it in the Integrated Development (IDE) libraries folder (usually found in documents/Arduino/libraries). Continue to step 2.3. If building the MK II, proceed to step 2.2.</li>
	<li>Add the microcontroller boards to the IDE, following the instructions15.</li>
	<li>Download &#39;ThresholdTest.ino&#39; for the MK I or &#39;BLEThresholdTest.ino&#39; and &#39;BluefruitConfig.h&#39; for the MK II and open in the IDE software (Supplemental files).</li>
	<li>Unplug the laptop from the mains and then, and only then, plug the microcontroller into the laptop via a Universal Serial Bus (USB) cable.</li>
	<li>Upload the relevant version of the threshold test to the microcontroller and then open the serial monitor (Tools&#62;Serial Monitor). The output of the EMG will now be displayed.</li>
	<li>Move the index finger from side to side and move the hand around without moving the index finger. Write down the values displayed in each case. 
	NOTE: When using the MK II make sure that the cables do not move as it is extremely sensitive to noise generated this way.</li>
	<li>Select a value that is above what is seen when the hand is moved around, but below what is seen when the finger is moved from side to side. Write down this value. 
	NOTE: The value is selected so that the device will only be activated by a purposeful movement of the finger. This is the Threshold Trigger Value, the value at which the device will be activated. The muscle sensor has a gain setting that can be manually altered if the threshold value is hard to find. The electrodes might need to be replaced. If using the abductor indicis muscle, set the gain to minimum as the starting point. The gain setting is altered by the potentiometer on the muscle sensor marked by GAIN, and this can be changed by a small flat-head screwdriver.</li>
</ol>
3. Test Threshold
<ol>
	<li>Download &#39;BoomTest.ino&#39; for the MK I or &#39;BLEBoomTest.ino&#39; and BluefruitConfig.h for the MK II and open it in the IDE software.</li>
	<li>Edit the provided code by replacing &#39;PLACE_YOUR_THRESHOLD_TRIGGER_VALUE_HERE&#39; with the Threshold Trigger Value previously determined in step 2.8. This is line 37 of the code for the MK I and line 47 of the code for the MK II.</li>
	<li>Upload the correct version of BoomTest to the microcontroller and then open the serial monitor (Tools&#62;Serial Monitor).</li>
	<li>Move the hand around (not moving the index finger from side to side); nothing is seen on the serial output.</li>
	<li>Move the index finger from side to side; the word &#39;BOOM&#39; appears. 
	NOTE: If &#39;BOOM&#39; appears at the wrong time or not at all, check the connections and move back to step 2.7.</li>
</ol>
4. 3D Print the MK II Case
<ol>
	<li>If building the MK II, download the stl files for all 5 components of the case (see Figure 7 for all 5 parts). Print the parts of the case by any preferred method. Proceed to step 5.2. If building the MK I, move on to section 5. 
	NOTE: The case has been successfully printed by both fused deposition modelling16 (FDM) and photolithography printers17.</li>
</ol>
5. Solder the Control Board
NOTE: If building the MK II, proceed to step 5.2.
<ol>
	<li>Place a row of two header pins, five 10 K&#937; resistors, a sliding switch and two push button switches for the components as shown in Figure 8A; then solder them in place on the underside of the board.
	<ol>
		<li>Break the copper tracks on the strip board by slicing through with a craft knife, following the grey lines on Figure 8A. This allows for individual tracks to have multiple functions across the board.</li>
		<li>Cut 7 wires (black, red, blue, orange, white, brown and yellow) of the correct length with a wire cutter so that they will run from the forearm to the upper arm (around 30 cm). Cut a red wire of 7 cm, a black wire of 3 cm and an orange and a blue wire of 4 cm.</li>
		<li>Strip both ends of the wires with a wire stripper.</li>
		<li>Place the wires in the control board, following the circuit diagram shown in Figure 9; solder the wires in place on the underside.</li>
		<li>Solder the long red and black wires to a pair of header pins, and then solder the other long wires to a strip of header pins in the order: blue, orange, white, brown, yellow.</li>
		<li>Solder the 5V and GND pins of the wireless module to the header pins on the control board.</li>
		<li>Solder the short orange wire to pin 2 of the wireless communication module and the short blue wire to pin 3.</li>
	</ol>
	</li>
	<li>Place three 10 K&#937; resistors, a sliding switch and two push button switches as shown in Figure 10A and solder them into place on the underside of the board.
	<ol>
		<li>Break the copper tracks on the strip board by slicing through with a craft knife, following the grey lines on Figure 10A. This allows for the track to have multiple functions on the board.</li>
		<li>Cut the wires that were previously soldered to the microcontroller with a wire cutter so that they can run through the mid layer of the microcontroller case to the control board without stopping the case from closing (Figure 10B).</li>
		<li>Place the wires in the control board, following the circuit diagram (Figure 11). Solder the wires in place. Proceed to step 6.2.</li>
	</ol>
	</li>
</ol>
6. Assemble Clicker and Update Microcontroller
<ol>
	<li>Re-assemble the Bionic Clicker, connecting the header connectors from the control board wires to the microcontroller and bio-signals shield (5V and GND on the MK I, pin 22-30 on the MKII). Connect the battery to the microcontroller. See Figure 12. Move on to step 6.3.</li>
	<li>Re-assemble the Bionic Clicker, connecting the header connector from the microcontroller to the muscle sensor (green wire to SIG). See Figure 13.</li>
	<li>Connect the microcontroller to the laptop via USB cable.</li>
	<li>Download &#39;BionicClicker.ino&#39; or &#39;BLEBionicClicker.ino and BluefruitConfig.h and open it in the IDE software.</li>
	<li>Edit the code and replace &#39;PLACE_YOUR_THRESHOLD_TRIGGER_VALUE_HERE&#39; with the Threshold Trigger Value determined in step 2.7 (on line 59 of the code for the MK I, line 83 of the code for the MK II). 
	NOTE: The name that the MK II device appears as when connecting over wireless can be changed by editing line 47 of the code. Replace &#39;Bionic Clicker MK II&#39; with an alternative title.</li>
	<li>Disconnect the microcontroller from the laptop by removing the USB cable.</li>
</ol>
7. Connect the Device to a Computer
<ol>
	<li>If using the MK I, follow the instructions to pair the wireless module to the device by following the manufacturer&#39;s guide18. If using the MK II, connect to the device wirelessly following the procedure to connect a wireless keyboard to the computer being used.</li>
</ol>
8. Test the Clicker
<ol>
	<li>Open some typing software and enter some text, such as &#39;Lorem ipsum dolor sit amet&#39;. This allows the presses to be perceived to test whether these commands are sent and received. 
	NOTE: If the battery is low the device may give erratic behavior; always use a fresh battery.
	<ol>
		<li>Press the manual forward button to see the cursor move forward and the manual backwards button to see the cursor move backwards. Raise the index finger to also move forward.</li>
	</ol>
	</li>
	<li>To test the clicker with the presentation software, raise the index finger to progress the slides. 
	NOTE: The override switch turns the EMG function on and off, and the manual forward and backwards buttons progress and retreat the slides in both scenarios.</li>
</ol>
9. Mount the Clicker
NOTE: If building the MK II move to step 9.2.
<ol>
	<li>If building the MK I, cut the double-sided hook and loop material with scissors, so that it fits comfortably around the wrist. Make sure the loops are facing inwards to not scratch the wrist.
	<ol>
		<li>Cut the double-sided hook and loop material so that it fits comfortably around the upper arm, again make sure the loops face inwards.</li>
		<li>Cut the double-sided hook and loop strips to the size of the microcontroller (10 cm x 5 cm) and the control board (2.5 cm x 6.4 cm). Cut a strip that will fit tightly around the battery (4 cm x 12 cm).</li>
		<li>Using the glue gun, glue the loop side of the strips to the bottom of the microcontroller and the bottom of the control board.</li>
		<li>Attach the control board to the wrist strap. Attach the microcontroller and battery to the upper arm strap.</li>
		<li>Plug everything in: The 9 V battery plugs into the microcontroller with the PP3 connector. The microcontroller and e-health shield connect to the control board via the soldered wires. 
		NOTE: The MK I is now finished.</li>
	</ol>
	</li>
	<li>If building the MK II, cut double-sided hook and loop material 35 mm wide and long enough to wrap around the wrist (around 22 cm for smaller wrists).
	<ol>
		<li>Slide the hook and loop material through the clips at the bottom of the case. Make sure that the loops are facing inwards to not scratch the wrist.</li>
		<li>Plug the wires soldered to the microcontroller terminating in the female header into the male header pins on the muscle sensor, and clip the electrodes into the EMG cables by pushing them on. 
		NOTE: The MK II is now finished. See Figure 14.</li>
	</ol>
	</li>
</ol>

<ol><li>Navarro, X., Krueger, T. B., Lago, N., Micera, S., Stieglitz, T., Dario, P. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/pubmed?term=((A+critical+review+of+interfaces+with+the+peripheral+nervous+system+for+the+control+of+neuroprostheses+and+hybrid+bionic+systems%5BTitle%5D)+AND+%22J+Periph+Nerv+Syst%22%5BJournal%5D)">A critical review of interfaces with the peripheral nervous system for the control of neuroprostheses and hybrid bionic systems.</a> J Periph Nerv Syst. 10 (3), 229-258 (2005).</li>
<li>Yang, D. P., et al. <a target="_blank" href="https://www-sciencedirect-com.remotexs.ntu.edu.sg/science/article/pii/S1672652908601195">An anthropomorphic robot hand developed based on underactuated mechanism and controlled by EMG signals.</a> J Bionic Eng. 6 (3), 255-263 (2009).</li>
<li>Chu, J. U., Moon, I., Lee, Y. J., Kim, S. K., Mun, M. S. <a target="_blank" href="http://ieeexplore.ieee.org/document/4244373/">A supervised feature-projection-based real-time EMG pattern recognition for multifunction myoelectric hand control.</a> IEEE/ASME Trans Mechatronics. 12 (12), 282-290 (2007).</li>
<li>Bitzer, S., Van Der Smagt, P. <a target="_blank" href="http://ieeexplore.ieee.org/document/1642128/">Learning EMG control of a robotic hand: towards active prostheses.</a> Proceedings 2006 IEEE International Conference on Robotics and Automation. , Orlando, Florida. (2006).</li>
<li>Cipriani, C., Zaccone, F., Micera, S., Carrozza, M. C. On the shared control of an EMG-controlled prosthetic hand: analysis of user-prosthesis interaction. IEEE Trans Rob. 24 (1), 170-184 (2008).</li>
<li>Tenore, F., Ramos, A., Fahmy, A., Acharya, S., Etienne-Cummings, R., Thakor, N. V. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/pubmed?term=((Towards+the+control+of+individual+fingers+of+a+prosthetic+hand+using+surface+EMG+signals%5BTitle%5D)+AND+%22IEEE+EMBS%22%5BJournal%5D)">Towards the control of individual fingers of a prosthetic hand using surface EMG signals.</a> IEEE EMBS. 2007, 6145-6148 (2007).</li>
<li>Reinvee, M., Pääsuke, M. <a target="_blank" href="https://journals-sagepub-com.remotexs.ntu.edu.sg/doi/abs/10.1177/1541931213601092">Overview of Contemporary Low-cost sEMG Hardware for Applications in Human Factors and Ergonomics.</a> In Proc Hum Fact Ergon Soc Annu Meet. 60 (1), 408-412 (2016).</li>
<li>George, P. K., Minas, V. L., Agisilaos, G. Z., Christoforos, I. M., Kostas, J. K. <a target="_blank" href="http://ieeexplore.ieee.org/document/7354209/">Open-Source, Anthropomorphic, Underactuated Robot Hands with a Selectively Lockable Differential Mechanism: Towards Affordable Prostheses.</a> 2015 IEEE/RSJ International Conference of Intelligent Robots and Systems. , Hamburg. (2015).</li>
<li>Agisilaos, G. Z., Minas, V. L., Christoforos, I. M., Kostas, J. K. Open-Source, Affordable, Modular, Light-Weight, Underactuated Robot Hands. IEEE/RSJ International Conference of Intelligent Robots and Systems. , Chicago, Illinois. (2014).</li>
<li>Minas, V. L., Agisilaos, G. Z., Melina, N. B., Kostas, J. K. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/pubmed?term=((Open-Source%2C+Low-Cost%2C+Compliant%2C+Modular%2C+Underactuated+Fingers%3A+Towards+Affordable+Prostheses+for+Partial+Hand+Amputations%5BTitle%5D)+AND+%222014+36th+Annual+International+Conference+of+the+IEEE+Engineering+in+Medicine+and+Biology+Society%22%5BJournal%5D)">Open-Source, Low-Cost, Compliant, Modular, Underactuated Fingers: Towards Affordable Prostheses for Partial Hand Amputations.</a> 2014 36th Annual International Conference of the IEEE Engineering in Medicine and Biology Society. , Chicago, Illinois. (2014).</li>
<li><a target="_blank" href="http://scholar.google.com/scholar?hl=en&safe=off&q=%22Engaging+the+senses%3A+object-based+learning+in+higher+education%22">Engaging the senses: object-based learning in higher education</a>. Chatterjee, H. J., Hannan, L. , Ashgate Publishing, Ltd. (2015).</li>
<li>Zainee, N. M., Chellappan, K. <a target="_blank" href="http://ieeexplore.ieee.org/document/7047512/">Emergency clinic multi-sensor continuous monitoring prototype using e-Health platform.</a> 2014 IEEE Conference on Biomedical Engineering and Sciences (IECBES). , Kuala Lumpur. (2014).</li>
<li>Paul, P., Motskin, M. <a target="_blank" href="http://www.ncbi.nlm.nih.gov/pubmed?term=((Engaging+the+Public+with+Your+Research%5BTitle%5D)+AND+%22Trends+Immunol%22%5BJournal%5D)">Engaging the Public with Your Research.</a> Trends Immunol. 37 (4), 268-271 (2016).</li>
<li>e-Health Sensor Platform V2.0 for Arduino and Raspberry Pi. , Available from: 
 <a target="_blank" href="https://www.cooking-hacks.com/documentation/tutorials/ehealth-biometric-sensor-platform-arduino-raspberry-pi-medical#step3_1">https://www.cooking-hacks.com/documentation/tutorials/ehealth-biometric-sensor-platform-arduino-raspberry-pi-medical#step3_1</a> (2017).</li>
<li>Arduino IDE Setup. , Available from: 
 <a target="_blank" href="https://learn.adafruit.com/add-boards-arduino-v164/setup">https://learn.adafruit.com/add-boards-arduino-v164/setup</a> (2017).</li>
<li>Ultimaker 2+. , Available from: 
 <a target="_blank" href="https://ultimaker.com/en/products/ultimaker-2-plus">https://ultimaker.com/en/products/ultimaker-2-plus</a> (2017).</li>
<li>Form 2. , Available from: 
 <a target="_blank" href="https://formlabs.com/3d-printers/form-2/">https://formlabs.com/3d-printers/form-2/</a> (2017).</li>
<li>Pairing to Bluefruit. , Available from: 
 <a target="_blank" href="https://learn.adafruit.com/introducing-bluefruit-ez-key-diy-bluetooth-hid-keyboard/pairing-to-bluefruit">https://learn.adafruit.com/introducing-bluefruit-ez-key-diy-bluetooth-hid-keyboard/pairing-to-bluefruit</a> (2017).</li>
</ol>

The authors have nothing to disclose.

The saturation of the MK II when used on the abductor indicis is less of an issue than it may first appear. Careful placement of the electrodes and correct gain setting stops this from being an issue when the device is used as a clicker. Unless interested in accurately recording the activity of the abductor indices, this is unlikely to be a problem at all. No over-saturation has been seen on any other muscle after the gain has been set. The false negatives with the MK II are due to the difficulty of selecting the proper threshold value when using the abductor indicis. With larger muscles the difference between the magnitude of non-purposeful activation of the muscle and purposeful tensing of the muscle is greater, allowing for the selection of a threshold point that is further from both the false-positive and false-negative points. On particularly small hands the abductor indicis muscle may be too small for the electrodes to be correctly placed (though with smaller electrode pads this could potentially be solved).
The considerably longer battery life for the MK II is useful for a variety of reasons. Firstly, the MK I device started to act erratically after 45 minutes of use, so it cannot be used for longer demonstrations. Secondly with a multi-hour battery life, the MK II can be considered as a control input for a useful device, and with only a small increase in physical battery size, it could be used as an all-day monitoring device. The wireless microcontroller has 6 analogue inputs and 13 digital inputs; this means that the device could accept signals from multiple muscle sensors to create a device with more degrees of freedom in the control inputs. It should also be noted that the muscle sensor could be replaced by any biosensor with an analogue output to create a device that uses other biological signals as the input. The code of the device can also be easily modified to change its functionality. Changes to the software and hardware of the device allow for simple and varied modifications to the device.
One limitation of the device as it currently stands is that the EMG output cannot be sent wirelessly at a high data rate as this can overload the wireless microcontroller buffer. Another limitation is that the technique uses the abductor indices as the input, and as the muscle is very small, the spacing of the electrodes on the hand almost overlap; if someone has particularly small hands, it may be impossible to place the electrodes correctly over this muscle. 
The device has several advantages over the more expensive devices when it comes to flexibility in potential research projects. It is low cost: the device costs 80 USD and additional EMG channels only cost 35 USD, making it ideal for smaller or student projects. It is easy to customize, the software can be easily edited, and the inputs changed for other hardware. It has a small size, so a person wearing it does not need to carry heavy or bulky equipment. It also appears as a wireless keyboard to other devices, so it can be easily integrated with any compatible wireless device. The device has already been incorporated into an assistive device that will be published in the near-future.
Due to the size and ease of customization of the MK II, it is already being considered for incorporation into several research projects as a wireless EMG module and as a wireless trigger mechanism. It is also being used as the foundation of one of the lab sessions on a master student's course. The main improvement we would like to make to the device is to increase the wireless transmission rate; the goal is to achieve 10 Hz, and whether this will be done through hardware or software is yet to be determined. 
The most critical steps within the protocol are steps 2.6 and 2.7: the selection of the Threshold Trigger Value. In step 2.6, special attention needs to be paid to the movement of the EMG cables, as these can act as antenna and generate motion artifacts; however, if these are kept stationary this is not an issue. In step 2.7, if the selected value is too high, this results in false negatives. If this value is too low, this results in false positives. In the case of the abductor indicis, it is very difficult to find a value that does not result in the occasional false negative, although with larger muscles this does not appear to be an issue. If finding the correct value is still an issue, the gain can be corrected by setting it to the minimum value and increasing it until a large difference between non-activation and activation is seen through the serial readout, with the values staying below the point of saturation.
Overall the MK II is a considerable improvement over the MK I as a potential research device, although because the MK I has a stronger visual impact, it is likely to still be used in future public engagement events.

The Aspire Centre for Rehabilitation Engineering and Assistive Technology investigates techniques that are applicable and transferable between different domains in related areas of interest, including but not limited to, stroke, muscular dystrophy, amputation, the ageing population and training of specialized skills. One area of research that the center is involved in is neuroprosthesis. Of the many techniques used for control of neuroprosthetic arms, EMG is one of the most common inputs for the control systems1,2,3,4,5,6. This is in a large part due to its ease of use and affordability when compared to other control systems7. Recently developed 3D-printed prostheses such as the Ada hand can cost only 1,000 USD when using this type of control8,9,10. However, when attempting to demonstrate such systems to the public there is no easy way of doing so without the aid of an amputee.
To raise the awareness of the research activities in this field to members of the public, a bionic clicker demo device was developed. It is very important to use object-based demonstration as it attracts attention and accelerates the learning and understanding of the subject being taught11. Our device not only helps to teach the concept of EMG but also to increase the knowledge of the current development of modern technologies. Moreover, it inspires younger generations to choose studies within Science, Technology, Engineering and Math (STEM) areas.
The Bionic Clicker MK I was made using readily available parts that were already in use within the lab. It consisted of a microcontroller, a bio-signals shield12, electrodes, a control board, a wireless communication board and a 9 V battery. The device functioned by picking up the activity of the abductor indicis muscle located between the index finger and thumb. It triggers a slide change by mimicking a keyboard and sending a &#39;right keypress&#39; whenever a preselected threshold was reached. The control board allowed for the manual sending of &#39;right&#39; and &#39;left&#39; keypresses (progress slides and retreat slides) and could also be used to override the EMG input if things went wrong during a live demonstration.
As part of the Medical Physics and Biomedical Engineering department public engagement activities, we demonstrated the Bionic Clicker to members of the public. It received an enthusiastic response from the audience and generated interest in starting several collaborations. After the success of the initial device a second version of the device was designed.
The goal for the design of the second device was to produce a device that was cheaper, less cumbersome and more customizable than the first device. The purpose of this device was to design something that could easily be modified for student projects and be cheaply incorporated into existing projects. The main advantage of this device over others available1,2,3,4,5,6 is its ease of use, small size, and low cost. Although the bionic clicker devices may not have the resolution of other research devices, such as trigger devices, they are more than good enough. The MK II would be an ideal basis for any system that uses an EMG threshold to trigger a device, such as a prosthetic controller or assistive device.
The design was based around a wireless-capable microcontroller and a muscle sensor. It also included a 3.7 V 150 mAh lithium polymer battery, a manual control board and a 3D-printed case. Figure 3 shows an overview of the differences between the designs. The MK II design has the same basic functionality as the original device but has significantly more potential functionality for new applications such as wireless EMG monitoring.

<table><tbody><tr><td>&lt;strong&gt;For the Mark I&lt;/strong&gt;</td><td></td><td></td><td></td></tr><tr><td>&lt;strong&gt;Equipment&lt;/strong&gt;</td><td></td><td></td><td></td></tr><tr><td>Laptop</td><td></td><td></td><td>Any laptop with USB</td></tr><tr><td>USB B cable</td><td></td><td></td><td>From laptop to USB-B connection on Arduino</td></tr><tr><td>Soldering Station</td><td></td><td></td><td></td></tr><tr><td>Solder</td><td></td><td></td><td></td></tr><tr><td>Hot glue gun</td><td></td><td></td><td></td></tr><tr><td>Hot glue gun glue</td><td></td><td></td><td></td></tr><tr><td>&lt;strong&gt;Items&lt;/strong&gt;</td><td></td><td></td><td></td></tr><tr><td>Small Single-Core Multi-thread Wires</td><td></td><td></td><td>Black, Red, Yellow, Brown, Orange White, Blue,</td></tr><tr><td>Arduino MEGA 2560</td><td>Arduino</td><td>Arduino MEGA 2560</td><td>(Geniuno MEGA 2560 outside US)</td></tr><tr><td>E-Health Shield v2.0</td><td>Cooking Hacks</td><td>e-Health Sensor Shield V2.0 for Arduino, Raspberry Pi and Intel Galileo [Biometric / Medical Applications]</td><td></td></tr><tr><td>EMG cables</td><td>Cooking Hacks</td><td>Electromyography Sensor (EMG) for e-Health Platform [Biometric / Medical Applications]</td><td></td></tr><tr><td>EMG Electrodes</td><td>Sparkfun</td><td>SEN-12969</td><td></td></tr><tr><td>9V battery</td><td></td><td></td><td>Any</td></tr><tr><td>Power cable</td><td></td><td></td><td>PP3 9v connector with jack</td></tr><tr><td>Bluefruit EZ-KEY HID</td><td>Adafruit</td><td>1535</td><td></td></tr><tr><td>strip board</td><td>Amazon.co.uk</td><td>Small Stripboard 25 X 64mm Pack of 3</td><td>any similiar stripboard 2.54mm pitch 7x25</td></tr><tr><td>push button switch</td><td></td><td>COM-00097</td><td></td></tr><tr><td>slide switch</td><td>amazon.com</td><td>20 Pcs On/Off/On DPDT 2P2T 6 Pin Vertical DIP Slide Switch 9x4x3.5mm</td><td></td></tr><tr><td>resistors</td><td></td><td>COM-11508</td><td></td></tr><tr><td>Double sided Velcro</td><td></td><td></td><td></td></tr><tr><td>Break Away Headers - Straight</td><td>Sparkfun</td><td>PRT-00116</td><td>2, 2 and 5 needed</td></tr><tr><td>&lt;strong&gt;For the Mark II&lt;/strong&gt;</td><td></td><td></td><td></td></tr><tr><td>&lt;strong&gt;Equipment&lt;/strong&gt;</td><td></td><td></td><td></td></tr><tr><td>Laptop</td><td></td><td></td><td>Any laptop with USB connection</td></tr><tr><td>USB micro cable</td><td></td><td></td><td>From laptop to USB micro (standard phone connector style)</td></tr><tr><td>Soldering Station</td><td></td><td></td><td>Any</td></tr><tr><td>Solder</td><td></td><td></td><td></td></tr><tr><td>&lt;strong&gt;Items&lt;/strong&gt;</td><td></td><td></td><td></td></tr><tr><td>Small Single-Core Multi-thread Wires</td><td></td><td></td><td>Black, Red, Green, White, Blue,</td></tr><tr><td>Feather BLE 32U4</td><td>Adafruit</td><td>2829</td><td></td></tr><tr><td>MyoWare</td><td>Sparkfun</td><td>SEN-13723</td><td></td></tr><tr><td>EMG cables</td><td>Sparkfun</td><td>CAB-12970</td><td></td></tr><tr><td>EMG electrodes</td><td>Sparkfun</td><td>SEN-12969</td><td></td></tr><tr><td>3.7 V LiPo</td><td>Adafruit</td><td>1317</td><td></td></tr><tr><td>Strip Board</td><td>amazon.co.uk</td><td>Small Stripboard 25 X 64mm Pack of 3</td><td>2.54 pitch 7x9 rows</td></tr><tr><td>Push Button switch</td><td></td><td>COM-00097</td><td></td></tr><tr><td>slide switch</td><td>amazon.com</td><td>20 Pcs On/Off/On DPDT 2P2T 6 Pin Vertical DIP Slide Switch 9x4x3.5mm</td><td></td></tr><tr><td>resistors</td><td></td><td>COM-11508</td><td></td></tr><tr><td>3D printed parts</td><td></td><td></td><td>Can be 3D printed yourself or printed from a website</td></tr><tr><td>Double sided Velcro</td><td></td><td></td><td></td></tr><tr><td>Break Away Headers - Straight</td><td>Sparkfun</td><td>PRT-00116</td><td>3 pins needed</td></tr><tr><td>Female Headers</td><td>sparkfun</td><td>PRT-00115</td><td>3 pins needed</td></tr></tbody></table>

the bionic clicker mark i &amp; ii

In this manuscript, we present two 'Bionic Clicker' systems, the first designed to demonstrate electromyography (EMG) based control systems for educational purposes and the second for research purposes. EMG based control systems pick up electrical signals generated by muscle activation and use these as inputs for controllers. EMG controllers are widely used in prosthetics to control limbs.
The Mark I (MK I) clicker allows the wearer to change the slide of a presentation by raising their index finger. It is built around a microcontroller and a bio-signals shield. It generated a lot of interest from both the public and research community.
The Mark II (MK II) device presented here was designed to be a cheaper, sleeker, and more customizable system that can be easily modified and directly transmit EMG data. It is built using a wireless capable microcontroller and a muscle sensor.

The MK II is more affordable, customizable and less cumbersome than the MK I device. The entire MK II costs only slightly more than the bio-signals shield alone (75 USD). The device is significantly smaller sitting on the wrist rather than the arm and the wireless microcontroller could potentially simultaneously support inputs from 6 muscle sensors. The functional battery life of the MK I device is just under an hour using a 9 V 550 mAh battery and the functional battery life of the MK II device (when used as a clicker) is around 8 hours using a 3.7 V 150 mAh battery; see Table 1 for a comparison of the devices.
The Bionic Clicker MK II can have an issue when used on the abductor indicis: the amplifier can saturate and take more than a second to discharge (see Figure 15). Careful placement of the electrodes and correctly setting the gain can overcome this issue. This does not happen with the Bionic Clicker MK I or on any other commonly used muscles for EMG.
Whilst calibrating the devices to find the Threshold Trigger Value, many different values can be observed. They fall into three ranges: the values when the hand is stationary, the values when the hand is moving, and the values when the finger is moved. Table 2 shows recorded values in each range; for the stationary and hand moving ranges, the maximum values are shown and for the finger tensing range the minimum value is shown. The threshold value is selected to lie above the hand moving value and below the finger tensing value. A value nearer to the hand moving range increases the chance of false positive and reduces the chance of false negatives, whilst a value closer to the finger tensing range has the opposite effect.
Both devices where tested for false negatives and false positives when tensing the abductor indices muscle. A false negative was recorded when the device did not trigger a change of slide upon tensing of the muscle and a false positive was recorded if the slide changed when no tensing occurred. Neither device had an issue with false positives, though the MK II device experienced the occasional false negative (less than 5% of the time). The MK I device experiences no false positives or negatives during the first 45 minutes of operation, though the number of false negatives increases rapidly until total device failure between 50 minutes and an hour (see Table 3).
These results show that the device succeeded in its stated aims. Table 1 shows that the MK II is cheaper and has more flexibility than the MK I. Table 2 and Table 3 show that the device functions as intended and can be used as an EMG-based trigger device. Figure 15 shows the issues that can occur if using the abductor indices muscle: this is not a problem that occurs with most muscles and can be fixed by altering the gain. Although the devices have some issues, they are sufficient for the intended use.
<img alt="Figure 1" class="xfigimg" src="/files/ftp_upload/55705/55705fig1.jpg" /> 
Figure 1: The Bionic Clicker MK I. This shows the Bionic Clicker MK I and all of its components mounted on the left arm. <a href="https://cloudflare-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55705/55705fig1large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 2" class="xfigimg" src="/files/ftp_upload/55705/55705fig2.jpg" /> 
Figure 2: Block diagram of the devices. Each box represents a separate section of the device; within each box is the functionality that section has as a part of the device. <a href="https://cloudflare-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55705/55705fig2large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 3" class="xfigimg" src="/files/ftp_upload/55705/55705fig3.jpg" /> 
Figure 3: Steps to build the device. A flow diagram containing a high-level overview of each step of the protocol. <a href="https://cloudflare-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55705/55705fig3large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 4" class="xfigimg" src="/files/ftp_upload/55705/55705fig4.jpg" /> 
Figure 4: Initial MK I assembly. Microcontroller with the bio-signals shield and electrode cables. <a href="https://cloudflare-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55705/55705fig4large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 5" class="xfigimg" src="/files/ftp_upload/55705/55705fig5.jpg" /> 
Figure 5: Initial MK II assembly. Microcontroller with the muscle sensor and soldered connections. <a href="https://cloudflare-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55705/55705fig5large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 6" class="xfigimg" src="/files/ftp_upload/55705/55705fig6.jpg" /> 
Figure 6: Electrode Placement. This figure shows the correct placement of the electrodes on the hand when using the abductor indicis. <a href="https://cloudflare-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55705/55705fig6large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 7" class="xfigimg" src="/files/ftp_upload/55705/55705fig7.jpg" /> 
Figure 7: The MK II case parts. The parts of the MK II case ready for printing in a photolithography printer. <a href="https://cloudflare-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55705/55705fig7large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 8" class="xfigimg" src="/files/ftp_upload/55705/55705fig8.jpg" /> 
Figure 8: The MK I control circuit. (a) Circuit board from above (gray marks where the strip board had contacts broken on the underside). (b) Completed Circuit Board. <a href="https://cloudflare-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55705/55705fig8large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 9" class="xfigimg" src="/files/ftp_upload/55705/55705fig9.jpg" /> 
Figure 9: The MK I control board circuit diagram. The circuit diagram for the MK I control board showing the connections between the resistors, switches and wires. <a href="https://cloudflare-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55705/55705fig9large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 10" class="xfigimg" src="/files/ftp_upload/55705/55705fig10v2.jpg" /> 
Figure 10: The MK I control circuit. (a) Control Board from above (gray mark where the strip board had contact broken on the underside). (b) Completed Circuit Board <a href="https://cloudflare-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55705/55705fig10v2large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 11" class="xfigimg" src="/files/ftp_upload/55705/55705fig11.jpg" /> 
Figure 11: The MK II control board circuit diagram. The circuit diagram for the MK I control board showing the connections between the resistors, switches and wires. <a href="https://cloudflare-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55705/55705fig11large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 12" class="xfigimg" src="/files/ftp_upload/55705/55705fig12.jpg" /> 
Figure 12: The assembled MK I. This shows all the components of the MK I device before they have been mounted on the arm. <a href="https://cloudflare-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55705/55705fig12large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 13" class="xfigimg" src="/files/ftp_upload/55705/55705fig13.jpg" /> 
Figure 13: Assembling the Clicker MK II. (a) Place the microcontroller in the bottom of the case. (b) Place the battery in the mid-section and put on the lid. (c) Place the muscle sensor in its case and put on the lid. (d) Connect the microcontroller to the muscle sensor and connect the battery to the microcontroller. <a href="https://cloudflare-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55705/55705fig13large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 14" class="xfigimg" src="/files/ftp_upload/55705/55705fig14.jpg" /> 
Figure 14: The completed Bionic Clicker MK II. (a) On the hook and loop strap. (b) On the wrist. <a href="https://cloudflare-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55705/55705fig14large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<img alt="Figure 15" class="xfigimg" src="/files/ftp_upload/55705/55705fig15.jpg" /> 
Figure 15: Oversaturation of the muscle sensor. This figure shows what happens when the muscle sensor is oversaturated; the plateaus are when muscle activation was too strong for the current gain setting on the device. <a href="https://cloudflare-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55705/55705fig15large.jpg" target="_blank">Please click here to view a larger version of this figure.</a>
<table fo:keep-together.within-page="1">
	<tbody>
		<tr>
			<td></td>
			<td>MK I</td>
			<td>MK II</td>
		</tr>
		<tr>
			<td>EMG sensor</td>
			<td>General Bio-sensor</td>
			<td>Dedicated Muscle Sensor</td>
		</tr>
		<tr>
			<td>Wireless</td>
			<td>Separate wireless module</td>
			<td>On the microcontroller board</td>
		</tr>
		<tr>
			<td>EMG over wireless?</td>
			<td>No</td>
			<td>Yes</td>
		</tr>
		<tr>
			<td>Battery</td>
			<td>9 V PP3</td>
			<td>150 mAh LiPo</td>
		</tr>
		<tr>
			<td>Operational Time</td>
			<td>1 h</td>
			<td>8 h</td>
		</tr>
		<tr>
			<td>Build Time</td>
			<td>5 h</td>
			<td>4 h</td>
		</tr>
		<tr>
			<td>Total cost</td>
			<td>$150</td>
			<td>$80</td>
		</tr>
		<tr>
			<td>False Positives (%)</td>
			<td>0</td>
			<td>0</td>
		</tr>
		<tr>
			<td>False Negatives (%)</td>
			<td>0</td>
			<td>4.7</td>
		</tr>
	</tbody>
</table>
Table 1: Comparison of the devices. This table compares several aspects of the devices, from design to functionality.
<table fo:keep-together.within-page="1">
	<tbody>
		<tr>
			<td></td>
			<td>Stationary (maximum)</td>
			<td>Hand Moving (maximum)</td>
			<td>Finger Tensing (minimum)</td>
			<td>Threshold Value</td>
		</tr>
		<tr>
			<td>MK I</td>
			<td>25</td>
			<td>35</td>
			<td>215</td>
			<td>200</td>
		</tr>
		<tr>
			<td>MK II</td>
			<td>40</td>
			<td>280</td>
			<td>460</td>
			<td>400</td>
		</tr>
	</tbody>
</table>
Table 2: Calibration Results. This table shows the values obtained whilst keeping the hand stationary, moving the hand and finger tensing, as well as the threshold value selected.
<table fo:keep-together.within-page="1">
	<tbody>
		<tr>
			<td></td>
			<td colspan="3">Number of false negatives (Tested every 30 s)</td>
			<td colspan="2">Number of false positives (Spontaneous activations)</td>
		</tr>
		<tr>
			<td></td>
			<td>First 45 min</td>
			<td>45 min-1 h</td>
			<td>1-8 h</td>
			<td>First h</td>
			<td>1-8 h</td>
		</tr>
		<tr>
			<td>MK I</td>
			<td>0</td>
			<td>35</td>
			<td>N/A</td>
			<td>0</td>
			<td>N/A</td>
		</tr>
		<tr>
			<td>MK II</td>
			<td>4</td>
			<td>1</td>
			<td>40</td>
			<td>0</td>
			<td>0</td>
		</tr>
	</tbody>
</table>
Table 3: Testing of the devices. Comparison of false positives and false negatives between the two devices.
Supplemental code files for MK I and MK II: 
<a href="https://www-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55705/BionicClicker.ino" target="_blank">Please click here to download &#34;BionicClicker.ino&#34;</a> 
<a href="https://www-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55705/BLEBionicClicker.ino" target="_blank">Please click here to download &#34;BLEBionicClicker.ino&#34;.</a> 
<a href="https://www-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55705/BLEBoomTest.ino" target="_blank">Please click here to download &#34;BLEBoomTest.ino&#34;.</a> 
<a href="https://www-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55705/BLEThresholdTest.ino" target="_blank">Please click here to download &#34;BLEThresholdTest.ino&#34;.</a> 
<a href="https://www-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55705/BoomTest.ino" target="_blank">Please click here to download &#34;BoomTest.ino&#34;.</a> 
<a href="https://www-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55705/ThresholdTest.ino" target="_blank">Please click here to download &#34;ThresholdTest.ino&#34;.</a> 
<a href="https://www-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55705/Feather-Featherbase.stl" target="_blank">Please click here to download &#34;Feather-Featherbase.stl&#34;.</a> 
<a href="https://www-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55705/Feather-Feathermid.stl" target="_blank">Please click here to download &#34;Feather-Feathermid.stl&#34;.</a> 
<a href="https://www-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55705/Feather-Feathertop.stl" target="_blank">Please click here to download &#34;Feather-Feathertop.stl&#34;.</a> 
<a href="https://www-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55705/Myo-Myobase.stl" target="_blank">Please click here to download &#34;Myo-Myobase.stl&#34;.</a> 
<a href="https://www-jove-com.remotexs.ntu.edu.sg/files/ftp_upload/55705/Myo-Myolid.stl" target="_blank">Please click here to download &#34;Myo-Myolid.stl&#34;.</a> 
&#160;

Watch this Scientific Journal Video about The Bionic Clicker Mark I & II at JoVE.com

The Bionic Clicker Mark I & II

A device was created to demonstrate electromyography-based control to a lay audience. After the success of the initial device, a second device was made with greater flexibility in functionality for demonstration and research purposes. This protocol describes the process of building and calibrating both devices.

The Bionic Clicker Mark I &amp; II

In this manuscript, we present two 'Bionic Clicker' systems, the first designed to demonstrate electromyography (EMG) based control systems for ...

Nanyang Technological University

Research

JoVE Journal

Bioengineering

16.4K Views.  University College London. A device was created to demonstrate electromyography-based control to a lay audience. After the success of the initial device, a second device was made with greater flexibility in functionality for demonstration and research purposes. This protocol describes the process of building and calibrating both devices.

Video: The Bionic Clicker Mark I & II

An Experimental Platform to Study the Closed-loop Performance of Brain-machine Interfaces

The non-stationary nature and variability of neuronal signals is a fundamental problem in brain-machine interfacing. We developed a brain-machine interface to assess the robustness of different control-laws applied to a closed-loop image stabilization task. Taking advantage of the well-characterized fly visuomotor pathway we record the electrical activity from an identified, motion-sensitive neuron, H1, to control the yaw rotation of a two-wheeled robot. The robot is equipped with 2 high-speed video cameras providing visual motion input to a fly placed in front of 2 CRT computer monitors. The activity of the H1 neuron indicates the direction and relative speed of the robot's rotation. The neural activity is filtered and fed back into the steering system of the robot by means of proportional and proportional/adaptive control. Our goal is to test and optimize the performance of various control laws under closed-loop conditions for a broader application also in other brain machine interfaces.

We use a closed-loop fly-machine interface to investigate general principles in neuronal control.

The non-stationary nature and variability of neuronal signals is a fundamental problem in brain-machine interfacing. We developed a brain-machine ...

Neuroscience

Assessing Functional Performance in the Mdx Mouse Model

Duchenne muscular dystrophy (DMD) is a severe and progressive muscle wasting disorder for which no cure is available. Nevertheless, several potential pharmaceutical compounds and gene therapy approaches have progressed into clinical trials. With improvement in muscle function being the most important end point in these trials, a lot of emphasis has been placed on setting up reliable, reproducible, and easy to perform functional tests to pre clinically assess muscle function, strength, condition, and coordination in the mdx mouse model for DMD. Both invasive and noninvasive tests are available. Tests that do not exacerbate the disease can be used to determine the natural history of the disease and the effects of therapeutic interventions (e.g. forelimb grip strength test, two different hanging tests using either a wire or a grid and rotarod running). Alternatively, forced treadmill running can be used to enhance disease progression and/or assess protective effects of therapeutic interventions on disease pathology. We here describe how to perform these most commonly used functional tests in a reliable and reproducible manner. Using these protocols based on standard operating procedures enables comparison of data between different laboratories.

Assessing Functional Performance in the Mdx Mouse Model

The primary outcome measure in clinical trials for neuromuscular disorders is generally improved muscle function. Therefore, assessing the effect of potential therapeutic compounds on muscle performance pre clinically in mouse models is of great importance. We here describe several functional tests to address this.

Duchenne muscular dystrophy (DMD) is a severe and progressive muscle wasting disorder for which no cure is available. Nevertheless, several potential ...

Behavior

Novel Object Exploration as a Potential Assay for Higher Order Repetitive Behaviors in Mice

Restricted, repetitive behaviors (RRBs) are a core feature of autism spectrum disorder (ASD) and disrupt the lives of affected individuals. RRBs are commonly split into lower-order and higher-order components, with lower order RRBs consisting of motor stereotypies and higher order RRBs consisting of perseverative and sequencing behaviors. Higher order RRBs are challenging to model in mice. Current assays for RRBs in mice focus primarily on the lower order components, making basic biomedical research into potential treatments or interventions for higher-order RRBs difficult. Here we describe a new assay, novel object exploration. This assay uses a basic open-field arena with four novel objects placed around the perimeter. The test mouse is allowed to freely explore the arena and the order in which the mouse investigates the novel objects is recorded. From these data, patterned sequences of exploration can be identified, as can the most preferred object for each mouse. The representative data shared here and past results using the novel object exploration assay illustrate that inbred mouse strains do demonstrate different behavior in this assay and that strains with elevated lower order RRBs also show elevated patterned behavior. As such, the novel object exploration assay appears to possess good face validity for higher order RRBs in humans and may be a valuable assay for future studies investigating novel therapeutics for ASD.

Higher order restricted, repetitive behaviors (RRBs) disrupt the lives of affected individuals. These behaviors are challenging to model in rodents, making basic biomedical research into potential treatments or interventions for RRBs difficult. Here we describe novel object exploration as a potential assay for higher order RRBs in mice.

Restricted, repetitive behaviors (RRBs) are a core feature of autism spectrum disorder (ASD) and disrupt the lives of affected individuals.  RRBs are ...

Introducing Clicker Training as a Cognitive Enrichment for Laboratory Mice

Establishing new refinement strategies in laboratory animal science is a central goal in fulfilling the requirements of Directive 2010/63/EU. Previous research determined a profound impact of gentle handling protocols on the well-being of laboratory mice. By introducing clicker training to the keeping of mice, not only do we promote the amicable treatment of mice, but we also enable them to experience cognitive enrichment. Clicker training is a form of positive reinforcement training using a conditioned secondary reinforcer, the "click" sound of a clicker, which serves as a time bridge between the strengthened behavior and an upcoming reward. The effective implementation of the clicker training protocol with a cohort of 12 BALB/c inbred mice of each sex proved to be uncomplicated. The mice learned rather quickly when challenged with tasks of the clicker training protocol, and almost all trained mice overcame the challenges they were given (100% of female mice and 83% of male mice). This study has identified that clicker training for mice strongly correlates with reduced fear in the mice during human-mice interactions, as shown by reduced anxiety-related behaviors (e.g., defecation, vocalization, and urination) and fewer depression-like behaviors (e.g., floating). By developing a reliable protocol that can be easily integrated into the daily routine of the keeping of laboratory mice, the lifetime experience of welfare in the mice can be improved substantially.

The development of new refinement strategies for laboratory mice is a challenging task that contributes towards fulfilling the 3R principle. This protocol introduces clicker training as a cognitive enrichment program for laboratory mice.

Establishing new refinement strategies in laboratory animal science is a central goal in fulfilling the requirements of Directive 2010/63/EU. Previous ...

Battery of Behavioral Tests Assessing General Locomotion, Muscular Strength, and Coordination in Mice

Behavioral testing is used in pre-clinical trials to assess the phenotypic effects and outcomes that a particular disease or treatment has on the animal&#39;s wellbeing and health. There are numerous behavioral tests that may be applied. We selected a test for general locomotion, the open field test (OFT); a test for muscular strength, the mesh test (MT); and a test for coordination, the rotarod test (RR). Testing can be accomplished on a weekly or monthly basis. As a test for general locomotion, the OFT works by objectively monitoring movement parameters while the mouse is in an open field apparatus. The field is generally a 2&#39; x 2&#39; box, and the movements are recorded through laser sensing or through video capture. The mouse is placed in the center of the open field and allowed to move freely for the test. The MT uses the latency for a mouse to fall off an inverted screen as a measure of muscular strength. A mouse is placed on a screen, which is inverted over a clear box, and is timed for their latency to fall. Three trials are performed, with the best of the three trials scored for that day. A score of 60 s is the maximum time a mouse is left inverted. Mice are given a 5-min rest period between mesh test trials. Lastly, an accelerated protocol on the RR assesses motor coordination and endurance. During a trial, a mouse walks on a rotating rod as it increases in speed from 4 rpm to 40 rpm over 5 min. The trial ends when the mouse touches the magnetized pressure sensor upon falling. Each mouse undergoes three trials, and the best trial is scored for that day. This combined behavioral data allows for the global assessment of mobility, coordination, strength, and movement of the test animals. At least two out of the three behavioral testing measures must show improvement for an animal to qualify as having overall improved motor function.

Behavioral testing is used in pre-clinical trials to assess the phenotypic effects of a disease or treatment on an animal's wellbeing. In order to globally assess motor functioning, we selected tests for general locomotion, muscular strength, and coordination: the open field test, the mesh test, and the rotarod test, respectively.

Behavioral testing is used in pre-clinical trials to assess the phenotypic effects and outcomes that a particular disease or treatment has on the ...

Using Clicker Training and Social Observation to Teach Rats to Voluntarily Change Cages

Cage cleaning is a routinely performed husbandry procedure and is known to induce stress in laboratory rats. As stress can have a negative impact on well-being and can affect the comparability and reproducibility of research results, the amount of stress experienced by laboratory animals should be minimized and avoided when possible. Further, the direct contact between the rat and animal caretaker during the cage change bears hygiene risks and therefore possibly negatively impacts the well-being of the rats and the quality of the research. 
Our protocol aims to improve the routinely performed cage changing procedure. For this reason, we present a feasible protocol that enables rats to learn via clicker training and observation to voluntarily change to a clean cage. This training helps to reduce stress caused by the physical disturbance and handling associated with the cage changes and concurrently enables a reduction in direct contact between animal and animal caretaker after the training phase is completed.
The implementation of clicker training to rats is fast and easy. Rats are generally interested in the training and efficiently learn the desired behavior, which entails changing cages through a pipe. Even without training, the rats learn to perform the desired behavior by observation, as 80% of the observational learning group successfully changed cages when tested. The training further helps to establish a relationship of trust between trainer and animal. As hygiene and well-being are both very important in animal experiments, this protocol might also help to improve high-quality research.

This protocol introduces a method of cage change for rats via clicker training. Rats learn the desired behavior not only by direct training but also by observational learning. The implementation of this fast and easy protocol might help to improve well-being and hygiene in rodent facilities.

Cage cleaning is a routinely performed husbandry procedure and is known to induce stress in laboratory rats. As stress can have a negative impact on ...

Transition of Farm Pigs to Research Pigs using a Designated Checklist followed by Initiation of Clicker Training - a Refinement Initiative

Implementation of 3R initiatives is important. To refine the life of laboratory pigs, we focused on the time period prior to inclusion of animals in experiments. We improved the checklist during the development. By using the checklist each individual pig&#39;s progress was documented. This aids the caretakers so they remain focused on the actions necessary to socialize the animals and limit the animal&#39;s stress and anxiety level. During this phase, the pigs become calm and ready to commence additional clicker training to further limit stress during the experimental period. The pigs will readily allow basic outcome measures to be collected without sedation or fixation.
The protocol is divided in two. First the transition phase that begins as the pigs arrive at the research facility. Introducing treats and gradually closer contact to the caretakers are the first steps. Then, the caretaker introduces actions to be able to touch the head and hind, to mimic e.g. manipulating the ear to take a blood sample or the hind to obtain a rectal temperature. A strong foundation is established in the animal-caretaker relationship and this swiftly minimizes the stress the pigs express after arrival. Secondly, the positive reinforcement training commences to teach the animal how to carry out more complex tasks without becoming stressed. A clicker is introduced as a secondary reinforcer.
Time, structure, education and thorough communication seem to be the most important criteria to succeed in the application of this protocol. In addition to having calm and compliant pigs, the caretakers report that they enjoy the focus they are allowed to give each individual pig, adding to their overall job satisfaction. Having caretakers with a strong commitment, and a focus on the transition progress and welfare of each pig, additionally strengthens the department&#39;s Culture of Care.

Refinement of porcine studies is achieved by introducing a standardized checklist and positive reinforcement training using a clicker. This work supports the collection of samples and the conduct of daily chores related to the animals.

Implementation of 3R initiatives is important. To refine the life of laboratory pigs, we focused on the time period prior to inclusion of animals in ...

A Method for Evaluating Timeliness and Accuracy of Volitional Motor Responses to Vibrotactile Stimuli

Artificial sensory feedback (ASF) systems can be used to compensate for lost proprioception in individuals with lower-limb impairments. Effective design of these ASF systems requires an in-depth understanding of how the parameters of specific feedback mechanism affect user perception and reaction to stimuli. This article presents a method for applying vibrotactile stimuli to human participants and measuring their response. Rotating mass vibratory motors are placed at pre-defined locations on the participant's thigh, and controlled through custom hardware and software. The speed and accuracy of participants' volitional responses to vibrotactile stimuli are measured for researcher-specified combinations of motor placement and vibration frequency. While the protocol described here uses push-buttons to collect a simple binary response to the vibrotactile stimuli, the technique can be extended to other response mechanisms using inertial measurement units or pressure sensors to measure joint angle and weight bearing ratios, respectively. Similarly, the application of vibrotactile stimuli can be explored for body segments other than the thigh.

This article describes a technique for applying vibrotactile stimuli to the thigh of a human participant, and measuring the accuracy and reaction time of the participant&#39;s volitional response for various combinations of stimulation location and frequency.

Artificial sensory feedback (ASF) systems can be used to compensate for lost proprioception in individuals with lower-limb impairments.  Effective design ...

Tracking Individual Running Metrics in Mice Using a Voluntary Wheel Running Protocol that Minimizes Social Isolation

Voluntary wheel running (VWR) in rodents is used to evaluate performance and endurance and to simulate exercise. In contrast to other exercise paradigms that require aversive stimulus to induce active movement, wheel running is voluntary. VWR generally consists of placing a running wheel inside the mouse home cage. However, analyzing exercise parameters can typically only be conducted when mice are individually housed, while overall cage effects can be reported when mice are group-housed. Therefore, the current models force experimenters to choose between measuring individual exercise parameters in single-housed mice or measuring group effects in group-housed mice; depending on the research question and model, this could be limiting. 
Therefore, the goal of this method is to demonstrate a protocol that assesses VWR in a mouse model by quantifying running parameters in individual mice, with minimal isolation. We report on device design, preoperative preparations, and experiment setup. Results of a 6-week training protocol using this VWR model suggest it provides sufficient stimulus to increase spatial object recognition memory, comparable to the clinical effect of exercise. This simple and inexpensive model facilitates investigation into the effect of VWR on multiple measurements of wheel activity, minimizing factors that could limit or affect experimental outcomes.

This protocol describes an effective voluntary wheel-running model that can be implemented in various research contexts. Unlike other voluntary running models, this method avoids isolation housing while tracking running metrics in individual mice.

Voluntary wheel running (VWR) in rodents is used to evaluate performance and endurance and to simulate exercise. In contrast to other exercise paradigms ...

Comprehensive Understanding of Inactivity-Induced Gait Alteration in Rodents

It is well known that disuse affects neural systems and that joint motions become altered; however, which outcomes properly exhibit these characteristics is still unclear. The present study describes a motion analysis approach that utilizes three-dimensional (3D) reconstruction from video captures. Using this technology, disuse-evoked alterations of walking performances were observed in rodents exposed to a simulated microgravity environment by unloading their hindlimb by their tail. After 2 weeks of unloading, the rats walked on a treadmill, and their gait motions were captured with four charge-coupled device (CCD) cameras. 3D motion profiles were reconstructed and compared to those of control subjects using the image processing software. The reconstructed outcome measures successfully portrayed distinct aspects of distorted gait motion: hyperextension of the knee and ankle joints and higher position of the hip joints during the stance phase. Motion analysis is useful for several reasons. First, it enables quantitative behavioral evaluations instead of subjective observations (e.g., pass/fail in certain tasks). Second, multiple parameters can be extracted to fit specific needs once the fundamental datasets are obtained. Despite hurdles for broader application, the disadvantages of this method, including labor intensity and cost, may be alleviated by determining comprehensive measurements and experimental procedures.

The present protocol describes three-dimensional motion tracking/evaluation to depict gait motion alteration of rats after exposure to a simulated disuse environment.

It is well known that disuse affects neural systems and that joint motions become altered; however, which outcomes properly exhibit these characteristics ...

The Bionic Clicker Mark I & II

Summary

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Using Clicker Training and Social Observation to Teach Rats to Voluntarily Change Cages

Transition of Farm Pigs to Research Pigs using a Designated Checklist followed by Initiation of Clicker Training - a Refinement Initiative

A Method for Evaluating Timeliness and Accuracy of Volitional Motor Responses to Vibrotactile Stimuli

Tracking Individual Running Metrics in Mice Using a Voluntary Wheel Running Protocol that Minimizes Social Isolation

Comprehensive Understanding of Inactivity-Induced Gait Alteration in Rodents