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We demonstrate a low-power (<0.1 mW), low-voltage (<10 Vp-p) on-chip piezoelectrically actuated micro-sorter that can deflect single particles and cells at high-speed. With rhodamine in the stream, switching of flow between channels can be visualized at high actuation frequency (~1.7 kHz). The magnitude of the cell deflection can be precisely controlled by the magnitude and waveform of input voltage. Both simulation and experimental results indicate that the drag force imposed on the suspended particle/cell by the instantaneous fluid displacement can alter the trajectory of the particle/cell of any size, shape, and density of interest in a controlled manner. The open-loop E. Coli cell deflection experiment demonstrates that the sorting mechanism can produce a throughput of at least 330 cells/s, with a promise of a significantly higher throughput for an optimized design. To achieve close-loop sorting operation, fluorescence detection, real-time signal processing, and field-programmable-gate-array (FPGA) implementation of the control algorithms were developed to perform automated sorting of fluorescent beads. The preliminary results show error-free sorting at a sorting efficiency of ~70%. Since the piezoelectric actuator has an intrinsic response time of 0.1–1 ms and the sorting can be performed under high flowrate (particle speed of ~1–10 cm/s), the system can achieve a throughput of >1,000 particles/s with high purity.
Compared to conventional fluorescence-activated cell sorter (FACS), µFACS has the advantages of lower cost, reduced reagent usage, portability and rapid analysis time, which make them attractive for various biotechnological applications (e.g. bioanalysis and drug discovery) (Dittrich 2003). Due to the growing interest in the study of single living cells (e.g. effect of drugs and gene expression studies in cancer research (Sims and Allbritton 2007; Andersson and Berg 2003; Meredith et al. 2000), along with advances in microfabrication technology, significant progress has been made toward developing µFACS that can sort single cells with high efficiency and throughput.
Numerous types of µFACS based on the principle of continuous flow separation (i.e. continuous injection, monitoring detection, and sorting based on spatial separation (Pamme 2007) have been developed to sort various types of cells including yeast, bacterial, and blood cells. Among those published micro sorting techniques are electroosmotic (Fu et al. 2004; Fu et al. 1999), dielectrophoretic (DEP) (Lapizco-Encinas et al. 2004; Fiedler et al. 1998; Holmes et al. 2005; Doh and Cho 2005; Braschler et al. 2007; Hu et al. 2005), magnetic (Pamme 2006; Pamme and Wilhelm 2006), and hydrodynamic (Bang et al. 2006; Krüger et al. 2002; Wolff et al. 2003) sorting. Electroosmotic sorters can achieve precise flow switching, but such devices operate under high DC voltage (e.g. hundreds of volts), require frequent change of voltage settings due to ion depletion (Fu 2002), and suffer from low sorting rate (e.g. tens of particles per sec). On the other hand, DEP-based sorting exhibits precise manipulation down to single cell level, but the fabrication is highly complex and the cell differentiation capability is rather limited. For DEP-based sorters, particles and cells with similar dielectric properties cannot be easily separated from one another since they experience similar DEP forces. Magnetic sorting demonstrates high selectivity but requires labeling of magnetic particles, which cause irreversible cell damages. The aforementioned drawbacks may be resolved with hydrodynamic flow-switching methods such as sheath flow steering (Blankenstein and Lasen 1998) and integration of membrane valve to alter fluid flow (Fu et al. 2002). However, these techniques have long response time due to the inherent properties of the mechanical components. As a result, the sorting rate of these devices is low in general. Due to the advance in check valve technology, several groups (Bang et al. 2006, Wolff et al. 2003) have implemented high-speed off-chip flow-switching check valve (i.e. response time of 2.5 ms) to enhance sorting throughput (~12,000 cells/sec). However, due to the lack of precise electronics control and large electronics-induced timing jitter, both the recovery rate and purity of sorting can be low. Also, the use of bulky external actuators (syringe pumps, external check valves, etc) in this sorting scheme hinders miniaturization.
In this paper, we describe a micro-sorter with a piezoelectric/metal bi-morphous actuator. The piezoelectric film is made of lead zirconate titanate (PZT), and the metal may be copper or stainless steel. The piezoelectric actuator has a diameter of 20 mm and an intrinsic resonant frequency of around 5 kHz. This PZT actuator is integrated with the microfluidic channels using UV ozone assisted bonding process to be discussed later. Compared to hybrid systems, the integrated approach offers several advantages: 1) low voltage and low power consumption (<10 Vp-p and <0.1 mW), 2) precise control of the magnitude of transverse cell/particle deflection to enable single particle/cell sorting, 3) intrinsically much faster response (~0.1–1 ms) than conventional check or membrane valves. In addition, to suppress noise in fluorescence detection, we have designed a spatial filter and signal processing algorithm for signal-to-noise ratio enhancement and sorting verification (i.e. sorting error detection). To carry out automated sorting, characterize sorting efficiency and accuracy, and to reduce timing jitter to <10 µsec, the signal processing algorithms as well as the actuator control algorithms have been implemented in field-programmable-gate-array (FPGA).
With a PZT actuator integrated on a chip, transverse displacement of fluid of the order of nanoliters can be introduced by the bending action (upward or downward) of the actuator controlled by the waveform of the input voltage (Fig. 1). As the targeted particle enters the sorting junction, the particle is being deflected transversely by the drag force of the displaced fluid and consequently follows the hydrodynamic fluid flow down to one of the collection channels. Without PZT actuation, unwanted particles travel straight down to the waste channel. To achieve the desirable amount of particle deflection, PZT actuator needs to provide a sufficient fluid volume displacement and a bending rate following the ramp of voltage. These needs are easily met in our system by adjusting input waveform and voltage magnitude for the PZT actuator.
To visualize the trajectory of the particle subjecting to fluid deflection, a time-dependent simulation is conducted in Comsol 3.3 (Comsol Inc.). The dynamics of fluid flow is modeled using incompressible Navier-Stoke equation with water (with density = 1,000 kg/m3 and viscosity = 1.002×10−3) as the fluid. The inlet velocity profile is assumed to be parabolic with maximum center velocity of 5 cm/s and the outlet channels assume atmosphere pressure. Transverse fluid deflection by the PZT actuation is modeled as time-dependent sinusoidal pressure at the boundary wall of the sorting junction while rest of the channel walls assume rigid and no-slip boundary conditions. At the sorting junction, pressure is defined as
PA is the actuation pressure, t is time, f is the actuation frequency, and Po is the hydrodynamic pressure established by the flow. To see the effect of PZT actuator-induced flow response, 5-µm particles are released into the center of the flow stream at a velocity of 5 cm/s and the movements of the particles are modeled using Khan and Richardson’s force (Coulson et al. 1982). Time-dependent boundary parameters, PA, f, and Po, are set at 1.5 kPa, 250 Hz, and 0.63 kPa respectively.
The device is fabricated using the conventional micro replica molding technique (Xia and Whitesides 1998) in which device features are photolithographically defined by SU-8 photoresist mold (Fig. 2(a)) and then transferred to a polydimethylsiloxane (PDMS) substrate. For device assembly, the PDMS substrate and glass are surface treated in UV ozone chamber (Jelight Inc., Irvine) with a lamp output of 28 mW at 254 nm. Bonding occurs as they are put into physical contact. For the subsequent PZT actuator and PDMS substrate bonding, the mechanically polished stainless steel surface of the PZT actuator is exposed to UV ozone treatment for 10 min. After the actuation chamber of the PDMS substrate (Sylgard 184, Dow Corning) is created using a 16-mm diameter punch, both the PDMS substrate and the PZT actuator are UV ozone treated for another 5 min. Immediately after the UV o-zone treatment, the stainless steel surface of the PZT actuator is aligned to the PDMS actuation chamber and put in contact with the PDMS substrate for bonding. The bonding process is completed after the sample is baked at 85°C for 8 h (Fig. 2(b)). For the last step of device fabrication, Teflon tubings are inserted into the inlets and outlets of the device for fluid flow introduction. The device (Fig. 2(c)) is then primed using vacuuming filling under −30 inch Hg. The strong stainless steel-to-PDMS bonding prevents fluid leakage and optimizes power coupling from the PZT actuator to the fluidic channels.
The device is mounted on a microscope stage with a high-speed camera (Photron Fastcam, Photron Inc.) attached for visualization, and PZT actuation is driven by a function generator (Tektronix Inc.). 5 mM of Rhodamine 6G is introduced to the sample channel and hydrodynamically focused (1:10 sample to sheath flow). Once the fluid flow is stabilized, the PZT actuator is electrically modulated and the behaviors of stream under various voltage and frequency are analyzed. Similarly, 5-µm polystyrene beads (conc. ~3.2×105 beads/ml, from Bangs Lab) are introduced to the microfluidic channel under the same flow condition with PZT actuation operated at 250 Hz and 9 Vp-p. For both experiments, videos are taken at the sorting junction and recorded at 3,000 fps.
An E. Coli concentration of ~7×105 cells/ml is prepared and suspended in 1X PBS solution. For low speed sorting, the total volumetric flow rate is maintained at 2 µl/min, and the PZT actuator is operated under 3 Vp-p at 20 Hz frequency. To increase throughput, the flowrate is increased to 18 μl/min, and the applied voltage and frequency are increased to 6 Vp-p and 200 Hz. Again, videos are recorded at 6,000 fps, and the sorted E. Coli are enumerated using frame-by-frame images to characterize the cell deflection capability of the device.
To perform fluorescence-activated cell sorting, a closed-loop control system is built (Fig. 3). A 60 W Halogen lamp is employed as the excitation source. To detect 10-µm fluorescent beads (Bangs Laboratory), bandpass filters of 480 and 520 nm central wavelength are used for filtering excitation and emission lights. After passing through a specially designed spatial filter that allows fluorescence from specific locations in the channel to reach the photo-multiplier tube (PMT) detector, the fluorescent emission signal from the cell/particle being sorted is amplified, noise-suppressed, and used to produce a time-delayed actuating signal to drive the actuator, triggering the sorting action. In the following we describe the design and function of the three components critical to close-loop, automated sorting: spatial filter, signal processing (matched filter), and FPGA implementation of signal processing and actuator control algorithms.
A spatial filter allows only fluorescence from certain areas in the channel to reach the detector, thus cutting down the background and crosstalk. Using specially designed patterns, one can spatially encode a fluorescent signal and then transform the signal into a temporarily encoded signal as the targeted particle/cell travels at a speed. We use photolithographic transparency masks (Cad/art services, Inc.) to create spatial filters. The spatially encoded patterns have triple slits and double slits. The former encodes the detection signal and the latter the verification signal from the particles/cells sorted into the designated channel. The width of the slits is 0.25–0.5 mm, translated to 12.5–25 µm on the microfluidic channels before magnified by a 20x microscope objective (Fig. 4).
Real-time electronic control is programmed using Labview (National Instrument) with a programmable external driver (CompactRio, NI). The external driver has an independent operating system with an embedded field-programmable gate array (FPGA) chip. The measured jitter of the system is <10 µsec. The flow of the electronic control is shown in Fig. 5. The random high pulse noises of PMT (e.g. caused by sporadic discharge of the device) are removed before running the signal amplification algorithm based on finite impulse response (FIR) filtering. With an FIR matched filter, the signal-to-noise (SNR) ratio can be increased by 18 dB. After SNR enhancement, threshold and search of maximum signal criteria are applied to determine the presence of the detected particle. A signal above threshold indicates that a particle/cell to be sorted is found, triggering the following actions: (a) a delay counter delays the firing of the pulse generator, (b) a preprogrammed output voltage signal is fired to drive the PZT actuator, (c) at certain time period the system is ready to detect the “verification” signal from the sorted sample travelling through the “verification zone”, and (d) update record of the sorting efficiency and sorting error. The amount of time delay equals the travel time of the particle from the optical detection zone to the sorting junction. Until the sorted particle is verified, the PZT actuator will not be fired again. This avoids the problem of confusing the verification signal with the signal of particles traveling too close to the particle being sorted.
Flow switching of the focused rhodamine stream can be observed under PZT actuation. As PZT actuator pushes the fluid to the left under a rising bias voltage, the rhodamine stream temporarily gets deflected towards the left channel (Fig. 6(a)). Similarly the stream is temporarily shifted towards the right channel as a falling voltage is applied to the PZT actuator (Fig. 6(c)). Without actuation, the stream travels directly down to the center channel (Fig. 6(b)). Such controlled flow switching behaviors are observed at high actuation frequency up to ~1.7 kHz (at 20 Vp-p). The upper limit of the switching frequency has not been experimentally determined yet. However, the channel geometry has been optimized to minimize the viscous effect when subjecting to fluid movement. In order to find out the maximum sort rate at single particle level, further theoretical analysis needs to be investigated to determine the limit of flow response under actuation. Nonetheless, the current study shows that the design can potentially sort several thousand particles/cells per second at single particle/cell resolution.
The dynamic simulation shows the trajectory of a 5-μm bead subjecting to a time-dependent sinusoidal pressure at the right boundary wall (Fig. 7(b), (d), and (f)). As the particle reaches the sorting junction at a velocity of 5 cm/s, the pressure force deflects the flow pattern, which in turn carries the particle down to the left collection channel. Particles released at other times (not shown here) can follow different trajectories (e.g. deflected to the right channel or to the center channel) since they experience different pressure force depending on the time they enter the sorting junction. To verify the bead trajectory experimentally, 5-μm polystyrene beads are used. Figure 7(a), (c), and (e)) show how the single bead moves (~5 cm/s) when subjected to PZT actuator-induced fluid disturbance. Similar to the simulation result, as the PZT actuator bends down, the flow imposes a drag force on the bead to deflect the bead off the center stream to the left channel. Also, as the PZT actuator is turned off, the particle immediately resumes its undisturbed trajectory (down the center channel). The result shows that the sorter can impose sufficient drag force to alter particle trajectory in a predictable manner. Furthermore, it shows the promise that the sorter can sort single particles at relatively high speed under low power consumption (<0.1 mW).
To further characterize the sorting capability of the device, E. Coli cells are being introduced to the flow stream under PZT actuation. At 20 Hz, 3 Vp-p actuation, we analyze the E. Coli. cells that are being deflected into the left and right channels. At a low flow rate of ~2 μl/min, a sorting throughput of 24 cells/s is recorded. To increase the sorting throughput, we increase the total flow rate to 18 μl/min, corresponding to a travel speed of ~6 cm/s for cells in the center stream, as well as the actuation voltage and frequency to 5 Vp-p and 200 Hz. At this flow rate, the E. Coli cells pass through the sorting junction (~100 μm in length) in 1.7 ms. Figure 8 shows the E. Coli cell deflection result in the aforementioned experimental conditions. Individual peaks represent single cells entering the right/left collection channels at the specified times. With frame-by-frame analysis, we determine the cell deflecting rate to be 330 cells/s. Notice that all the red peaks occur within the rising cycle of the applied voltage, representing samples entering the left channel. Similarly, all the blue peaks occur within the falling cycles of the applied voltage, representing samples entering the right channel. This is in total agreement with the proposed sorting mechanism that a rising (falling) voltage bends the PZT downward (upward) to create a transient transverse flow towards the left (right) channel, which in turn directs the cells into the desired collection channel.
As a 10-µm fluorescent bead crosses the detection slits and is sorted to pass the verification slits, a 3-peak signal followed by a 2-peak signal are observed (Fig. 9). The distinctive nature of the peaks allows real-time monitoring of sorted and unsorted particles, which, to our best knowledge, has never been implemented in any µFACSs. The detected signals can be amplified using a real-time signal processing algorithm based on the concept of match filter. The mathematical model of the FIR match filter can be described as
where Y[n] is the output signal, x[n] is the input signal, bk is the filter coefficients, and M is the filter order, which specifies the number of taps (e.g. M+1) for the filter coefficients. Thus, in the proposed design, the match filter coefficients, which assume the shape similar to the detected signals (e.g. 3 sinusoidal lobes), are used to convolve with the detected signal, resulting in SNR enhancement of ~18 dB, as shown in Fig. 10.
To characterize the sorting efficiency, 10-µm fluorescent beads (Bangs Laboratory) with a concentration of ~1×105 particles/ml and excitation/emission wavelength of 480/520 nm are used. The beads are hydrodynamically focused under a sample-to-sheath flow ratio of 1:2 with velocities of ~8 cm/s. Square pulses of 10 Vp-p (1.5 ms pulse width) are used to drive the PZT actuator. The delay time (~1.5 ms) is estimated according to the velocity of the particle. The measurement data are recorded for a total period of 10 s. We use the setup to measure the sorting efficiency and the sorting error. The former refers to the success rate of a voltage pulse to direct the targeted particle into the designated channel; and the latter refers to the possibility for an unintended particle to enter the designated channel by mistake. A sorting efficiency less than 100% could be due to non-ideal timing control, limited flow response, or timing jitter. In most practical applications, this is less a concern than sorting error. On the other hand, a sorting error, caused likely by non-ideal flow disturbance due to actuation, could have a much more adverse effect. Therefore, a strategy is taken to achieve the lowest possible sorting error at some expense of sorting efficiency. From a subset of the measurements, Fig. 11 shows a sorting efficiency of ~70%. Other measurements consistently show similar results (70%±5%). The distinction between successfully and unsuccessfully sorted particles is by examining the presence and absence of the verification signal following the first detected signal. The verification signal is designed to have a lower intensity than the first detected signal because the spatial filter for the verification signal has only two slits, producing a less match to the triple-peak FIR filter. Nonetheless, the amount of SNR enhancement for the verification signal still allows clear identification. In the instance that two particles are spaced closely such that the second particle enters the detection region before the first particle is being verified downstream, to avoid misfiring of PZT actuation due to cross-talking between detection and verification signals, our algorithm is set up to keep the actuator inactive until the first particle is sorted and verified. This holding period (~3–4 ms) also contributes to the reduced sorting efficiency. From the data in Fig. 11 and a series of preliminary measurements, we have achieved 0% sorting error and the estimated minimum particle spacing to ensure error-free sorting is ~100 µm.
The current experiment uses filtered mercury lamp as the fluorescence excitation source. To increase sensitivity for sorting of fluorescently-tagged biological agents, 488 nm laser (~40 mW) will be used as the excitation source. These developments, in conjunction with integration of optical devices with microfluidic channels, could lead to high-throughput, high efficiency, and high accuracy microfabricated cell sorter at the single cell level.
We have demonstrated, for the first time, a microfluidic cell sorter with integrated piezoelectric actuator. The device is easy to fabricate and operates at less than 10 Vp-p. In the experiment of instantaneous flow switching, we have shown that the flow stream responds to the piezoelectric actuator at high frequency (~1.7 kHz) and the amount of deflection of cells/particles in the flow can be precisely controlled. Both simulation and experiment show that particles of any size, shape, and density of interest can be individually sorted in a controlled manner. In the experiment of E. Coli deflection, a sinusoidal voltage deflects cells at a rate of 330 cells/s and shows a highly repeatable operation consistent with the theory. Using a specially design spatial filter and a real-time signal processing algorithm implemented in FPGA, a closed-loop sorting system is demonstrated with zero error rate and a sorting efficiency of around 70%. Compared with other µFACS, our sorting system has advantages in three areas. First, the spatial filter design and the real-time signal processing algorithm enhance the signal-to-noise ratio by 18 dB and allow verification of sorting. Second, the PZT-actuated sorting module is easy to fabricate, consumes minimum power (0.1 mW), operates at low voltage (<10 Vpp), and has a much faster response (0.1–1 ms) than off-chip mechanical actuators such as check-valves and syringe pumps. Third, the FPGA-based electronics control enables real-time signal amplification, user-defined delay time, programmable output waveform, and low timing jitter (<10 µsec). These features contribute significantly to a low-cost sorter that can perform high-throughput cell sorting at a single-cell level.
The research is supported by the NIH grants 1R21RR024453-01 and 1R01HG004876. We would like to thank the Nano3 staff for their technical support.
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