Difference between revisions of "Team:Sheffield/project/device/microfluids"
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<h2>What is Microfluidics?</h2> | <h2>What is Microfluidics?</h2> | ||
| − | <p> | + | <p>Microfluidics is the flow and mixing of microlitre volumes of fluids via capillary action, where the fluids are contained within wells and channels made of glass and polydimethylsiloxane gel (PDMS). Figure 1 shows how the cured gel creates an enclosure between itself and the glass slide beneath. Essentially, this forms what you call a “lab-on-a-chip” device.</p> |
| + | |||
| + | <!--figure 1--> | ||
| + | |||
| + | <p class="modelcaption><i>Figure 1: Lab-on-a-chip.</i></p> | ||
| + | |||
<h2>Identifying Requirements</h2> | <h2>Identifying Requirements</h2> | ||
| − | <p> | + | <p>At the start of our project, it was identified that a device, which could mix reagents in the right order and at the correct times, was needed. In between mixings, the reagents needed to be left for a specified duration to allow any reactions to take place. We looked into microfluidics as a solution that could potentially meet these requirements. We also identified that an external pneumatic pump should not be used to drive flow in the chip as doctors would not have access to such a pump when using the chip in an ordinary clinical setting. |
| + | </p> | ||
| + | |||
| + | <!--figure 2--> | ||
| + | |||
| + | <p class="modelcaption><i>Figure 2: Photo of a microfluidics chip showing 3 channels.</i></p> | ||
| + | |||
| + | <p>A schematic diagram of the potential chip is shown in figure 3. The chip would require two inlets: one where the blood sample is deposited (Start chamber) and one where the stock solution is deposited (Middle chamber). The stock solution contains the siderophore-iron complexes that lipocalin in the blood sample would bind to. The two solutions would mix completely in the main channel before entering the end chamber where the bacteria will be contained. Once the mixed solution flows into the end chamber, it can stay there indefinitely until the bacteria takes up the siderophore-iron complexes and produces fluorescence. As an extension of this project, an albumin chelator could be added just before the Middle chamber in order to chelate albumin before it could come into contact with the siderophore-iron complexes.</p> | ||
| + | |||
| + | <!--figure 3--> | ||
| + | |||
| + | <p class="modelcaption><i>Figure 3: Schematic diagram of a potential microfluidics chip for detecting lipocalin.</i></p> | ||
| + | |||
<h2>Why Microfluidics?</h2> | <h2>Why Microfluidics?</h2> | ||
| − | <p> | + | <p>Not only did microfluidics enable our device requirements to be met, but also offered several additional advantages such as:</p> |
| + | |||
| + | <ul> | ||
| + | <li><u>Ease of use</u>: in order for the reactions to be carried out at the right times, one need only add the blood sample onto the chip in order for it to work.</li> | ||
| + | <li><u>Low cost</u>: a single chip only costs a few cents each to make, so it would be cheap to manufacture in bulk. The small volumes of reagents used would also result in costs savings.</li> | ||
| + | <li><u>Parallel processing</u>: if there needs to be a control during the diagnosis, a microfluidics chip could provide an easy means of conducting the two tests simultaneously.</li> | ||
| + | <li><u>Speed</u>: With the small size of a glass slide/chip, the total flow time within the chip should be no more than 20 minutes, which means this is a sure way to ensure that the reactions are within 20 mins.</li> | ||
| + | <li><u>Ease of coupling to a fluorometer</u>: due to the transparency of the materials, it is easy to connect a chip to a fluorometer/spectrometer in order to detect minute amounts of fluorescence/colour change.</li> | ||
| + | <li><u>Possibility of automation</u>: reagents can be added automatically and at the right times to the blood sample in the chip.</li> | ||
| + | <li><u>Biosafety</u>: the chip could contain bacteria and blood with less risk of contamination. It is also easy to dispose of when the test is done since all the reagents are contained within the chip.</li> | ||
| + | <li><u>Flexibility in testing</u>: it is quick and easy to make and test multiple designs. Each batch of test designs would take around 1 day to make and 1 day to test. Please click here for the <a href="https://2016.igem.org/Team:Sheffield/project/device/microfluids/">protocol</a> of the manufacturing process. Food colouring is used in place of blood and siderophore-iron solution to test how well the solutions mixed. | ||
| + | </li> | ||
| + | </ul> | ||
| + | |||
| + | <p>In order to determine the best microfluidics design for our project, we tested out different mixing designs as well as the fluid flow rate in different channel lengths.</p> | ||
</div> | </div> | ||
</div> | </div> | ||
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<h2>The Theory</h2> | <h2>The Theory</h2> | ||
| − | <p> | + | <p>Mixing in microfluidics occurs in two ways: via diffusion or the introduction of turbulence. In order to encourage mixing in a microfluidics chip, one must induce it in either or both ways.</p> |
| + | |||
| + | <p>Firstly, diffusion is the movement of particles from a region of higher concentration to a region of lower concentration. For instance, when the blood and stock solution are flowing side by side, lipocalin would move from the blood into the stock solution since there is higher concentration of lipocalin in the blood as compared to the stock solution. This also holds true for the siderophore-iron complexes, which diffuse from the stock solution into the blood. Over time, there is an equal concentration of reagents on both sides and thus the solutions are mixed. In order to increase the rate of diffusion and hence mixing, the distance that the particles need to diffuse across needs to be shortened by minimising the width of the channel. For the protocol <LINK> used, the minimum width that is feasible is 0.5 mm.</p> | ||
| + | |||
| + | <p>Introducing turbulence encourages mixing much like how stirring liquid in a mug helps to mix the contents.There are two types of flow: laminar and turbulent. Laminar flow is when the liquid particles travel in an orderly manner parallel to the channel length and in a single direction. The velocity of the liquid can be represented well using equations. In turbulent flow, the direction and speed at which each particle moves is unpredictable. The Reynolds number quantifies whether a flow is laminar or turbulent (Falkovich, 2011). It is defined as follows, where a higher Reynolds number indicates a more turbulent regime.</p> | ||
| + | |||
| + | <!--Eqn 1--> | ||
| + | |||
| + | <p>With respect to the lengths of a microfluidics chip (maximum 10 cm) , viscosity (3.5 × 10<sup>−3</sup> Pa.s) and density (1060 kg/M<sup>3</sup>) of blood, the Reynolds number is around 10 (Bruus, 2007), which indicates laminar flow with minimal turbulence. The viscosity and density of blood remains constant throughout the test and the velocity cannot be easily controlled. However, the flow can be made more turbulent by increasing the length of the channel.</p> | ||
| + | |||
<h2>The Design Ideas</h2> | <h2>The Design Ideas</h2> | ||
<p><u>Design 1: The Capillary Stop Valve Idea</u></p> | <p><u>Design 1: The Capillary Stop Valve Idea</u></p> | ||
| − | <p> | + | |
| + | <p>The initial design for mixing is shown in figure 4. Due to the surface tension of the liquid, the stock solution contained within the middle chamber would not flow out into the main channel. This design is called a capillary stop valve and has been shown to work in literature (Mastrangelo et al, 1998). The flow of liquid from the middle channel can only be initiated when the blood sample flows past it.</p> | ||
| + | |||
| + | <!--Figure 4--> | ||
| + | |||
| + | <p class="modelcaption"><i>Figure 4: Diagram of the mixing idea 1 containing a capillary stop valve. Surface tension holds the blue liquid in place like a valve until the red liquid flows past, pulling the blue liquid into the main channel where they mix.</i></p> | ||
| + | |||
| + | <p>This design allows the stock solution to be contained in a chamber prior to a blood sample being taken. The length of the main channel between the middle chamber and the end chamber can be specified so that the binding of siderophores to lipocalin would have reached equilibrium by the time the solution reaches the end chamber. A potential pitfall of this design is that the surface tension is inadequate to contain the stock solution.</p> | ||
| + | |||
<p><u>Design 2: The Well Idea</u></p> | <p><u>Design 2: The Well Idea</u></p> | ||
| − | <p> | + | |
| + | <p>The second design consists of two layers of PDMS (figure 5). The bottom layer has a well holding the stock solution (blue). The middle well needs to be filled to the brim but should not flow into the channels when the top layer is placed on it. This can be done by calculating the volume that the well can hold prior to adding the stock solution. The blood sample (here shown in yellow) will flow across the well, mix with the blue solution and flow out of the well as the mixed green solution.<p> | ||
| + | |||
| + | <p>This design is harder to manufacture, as two layers of PDMS have to be made and aligned with each other and this often incorporates considerable amount of human error and poor reproducibility. It has also not been seen in literature before, thus the effectiveness of this design is unknown. The advantage to this design is that it is a simple idea that does not depend on the quality of the manufactured PDMS, unlike capillary stop valves (design 1). The timing could also be easily controlled by varying the lengths of the channels.</p> | ||
| + | |||
| + | <!--Figure 5--> | ||
| + | |||
| + | <p class="modelcaption"><i>Figure 5: Diagram of how mixing design 2 should work. The yellow fluid flows over the bottom well and mixes with the blue fluid contained there before flowing to the end chamber.</i></p> | ||
| + | |||
<p><u>Design 3: The Mixing Chamber Idea</u></p> | <p><u>Design 3: The Mixing Chamber Idea</u></p> | ||
| − | <p> | + | |
| + | <p>The third design consists of a large mixing chamber where the two fluids will spread out over a larger area and thus flow over a longer distance, which would give them a higher chance of mixing. A longer distance to flow over also means we can extend the time for which the reagents are in contact, further promoting adequate mixing. The final channel is deliberately made to be long so that if the fluids are not mixed by the time they enter the final channel, they could mix via diffusion within the smaller width of the channel. When the fluid flows from the mixing chamber to the final chamber, the reduction in width of the channel promotes the fluid to reach the end chamber. This is important as one of the problems we faced in the lab was the fluid stopping in the final chamber mid-way before reaching the end.</p> | ||
| + | |||
| + | <!--Figure 6--> | ||
| + | |||
| + | <p class="modelcaption"><i>Figure 6: Diagram (top view) of mixing design 3 containing a large mixing chamber. The yellow and blue fluids should mix within the mixing chamber.</i></p> | ||
| + | |||
| + | <p>This design has already been shown to work in the lab before and thus should be more foolproof. However, there might be difficulty controlling when the 2 solutions mix, thus potentially resulting in one solution entering the end chamber before the mixed solution does. Since the blood can enter the last chamber without any adverse effects on the bacterial cells and the results obtained, this disadvantage can be mitigated by adding the blood before adding the siderophore-iron solution into their respective inlet chambers.</p> | ||
<h2>The Results</h2> | <h2>The Results</h2> | ||
Revision as of 16:45, 17 October 2016
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What is Microfluidics?
Microfluidics is the flow and mixing of microlitre volumes of fluids via capillary action, where the fluids are contained within wells and channels made of glass and polydimethylsiloxane gel (PDMS). Figure 1 shows how the cured gel creates an enclosure between itself and the glass slide beneath. Essentially, this forms what you call a “lab-on-a-chip” device.
A schematic diagram of the potential chip is shown in figure 3. The chip would require two inlets: one where the blood sample is deposited (Start chamber) and one where the stock solution is deposited (Middle chamber). The stock solution contains the siderophore-iron complexes that lipocalin in the blood sample would bind to. The two solutions would mix completely in the main channel before entering the end chamber where the bacteria will be contained. Once the mixed solution flows into the end chamber, it can stay there indefinitely until the bacteria takes up the siderophore-iron complexes and produces fluorescence. As an extension of this project, an albumin chelator could be added just before the Middle chamber in order to chelate albumin before it could come into contact with the siderophore-iron complexes.
In order to determine the best microfluidics design for our project, we tested out different mixing designs as well as the fluid flow rate in different channel lengths.
The Theory
Mixing in microfluidics occurs in two ways: via diffusion or the introduction of turbulence. In order to encourage mixing in a microfluidics chip, one must induce it in either or both ways.
Firstly, diffusion is the movement of particles from a region of higher concentration to a region of lower concentration. For instance, when the blood and stock solution are flowing side by side, lipocalin would move from the blood into the stock solution since there is higher concentration of lipocalin in the blood as compared to the stock solution. This also holds true for the siderophore-iron complexes, which diffuse from the stock solution into the blood. Over time, there is an equal concentration of reagents on both sides and thus the solutions are mixed. In order to increase the rate of diffusion and hence mixing, the distance that the particles need to diffuse across needs to be shortened by minimising the width of the channel. For the protocol used, the minimum width that is feasible is 0.5 mm.
Introducing turbulence encourages mixing much like how stirring liquid in a mug helps to mix the contents.There are two types of flow: laminar and turbulent. Laminar flow is when the liquid particles travel in an orderly manner parallel to the channel length and in a single direction. The velocity of the liquid can be represented well using equations. In turbulent flow, the direction and speed at which each particle moves is unpredictable. The Reynolds number quantifies whether a flow is laminar or turbulent (Falkovich, 2011). It is defined as follows, where a higher Reynolds number indicates a more turbulent regime.
With respect to the lengths of a microfluidics chip (maximum 10 cm) , viscosity (3.5 × 10−3 Pa.s) and density (1060 kg/M3) of blood, the Reynolds number is around 10 (Bruus, 2007), which indicates laminar flow with minimal turbulence. The viscosity and density of blood remains constant throughout the test and the velocity cannot be easily controlled. However, the flow can be made more turbulent by increasing the length of the channel.
The Design Ideas
Design 1: The Capillary Stop Valve Idea
The initial design for mixing is shown in figure 4. Due to the surface tension of the liquid, the stock solution contained within the middle chamber would not flow out into the main channel. This design is called a capillary stop valve and has been shown to work in literature (Mastrangelo et al, 1998). The flow of liquid from the middle channel can only be initiated when the blood sample flows past it.
Figure 4: Diagram of the mixing idea 1 containing a capillary stop valve. Surface tension holds the blue liquid in place like a valve until the red liquid flows past, pulling the blue liquid into the main channel where they mix.
This design allows the stock solution to be contained in a chamber prior to a blood sample being taken. The length of the main channel between the middle chamber and the end chamber can be specified so that the binding of siderophores to lipocalin would have reached equilibrium by the time the solution reaches the end chamber. A potential pitfall of this design is that the surface tension is inadequate to contain the stock solution.
Design 2: The Well Idea
The second design consists of two layers of PDMS (figure 5). The bottom layer has a well holding the stock solution (blue). The middle well needs to be filled to the brim but should not flow into the channels when the top layer is placed on it. This can be done by calculating the volume that the well can hold prior to adding the stock solution. The blood sample (here shown in yellow) will flow across the well, mix with the blue solution and flow out of the well as the mixed green solution.
This design is harder to manufacture, as two layers of PDMS have to be made and aligned with each other and this often incorporates considerable amount of human error and poor reproducibility. It has also not been seen in literature before, thus the effectiveness of this design is unknown. The advantage to this design is that it is a simple idea that does not depend on the quality of the manufactured PDMS, unlike capillary stop valves (design 1). The timing could also be easily controlled by varying the lengths of the channels.
Figure 5: Diagram of how mixing design 2 should work. The yellow fluid flows over the bottom well and mixes with the blue fluid contained there before flowing to the end chamber.
Design 3: The Mixing Chamber Idea
The third design consists of a large mixing chamber where the two fluids will spread out over a larger area and thus flow over a longer distance, which would give them a higher chance of mixing. A longer distance to flow over also means we can extend the time for which the reagents are in contact, further promoting adequate mixing. The final channel is deliberately made to be long so that if the fluids are not mixed by the time they enter the final channel, they could mix via diffusion within the smaller width of the channel. When the fluid flows from the mixing chamber to the final chamber, the reduction in width of the channel promotes the fluid to reach the end chamber. This is important as one of the problems we faced in the lab was the fluid stopping in the final chamber mid-way before reaching the end.
Figure 6: Diagram (top view) of mixing design 3 containing a large mixing chamber. The yellow and blue fluids should mix within the mixing chamber.
This design has already been shown to work in the lab before and thus should be more foolproof. However, there might be difficulty controlling when the 2 solutions mix, thus potentially resulting in one solution entering the end chamber before the mixed solution does. Since the blood can enter the last chamber without any adverse effects on the bacterial cells and the results obtained, this disadvantage can be mitigated by adding the blood before adding the siderophore-iron solution into their respective inlet chambers.
The Results
Design 1: The Capillary Stop Valve Idea
Some paragraph.
Design 2: The Well Idea
Some paragraph.
Design 3: The Mixing Chamber Idea
Some paragraph.
The Theory
This is some paragraph.
The Results
This is some paragraph
