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Nanopore sensors have attracted considerable interest for high-throughput sensing of individual nucleic acids and proteins without the need for chemical labels or complex optics. A prevailing problem in nanopore applications is that the transport kinetics of single biomolecules are often faster than the measurement time resolution. Methods to slow down biomolecular transport can be troublesome and are at odds with the natural goal of high-throughput sensing. Here we introduce a low-noise measurement platform that integrates a complementary metal-oxide semiconductor (CMOS) preamplifier with solid-state nanopores in thin silicon nitride membranes. With this platform we achieved a signal-to-noise ratio exceeding five at a bandwidth of 1 MHz, which to our knowledge is the highest bandwidth nanopore recording to date. We demonstrate transient signals as brief as 1 μs from short DNA molecules as well as current signatures during molecular passage events that shed light on submolecular DNA configurations in small nanopores.
Single-molecule measurements are attractive not only for their extremely high sensitivity but also for the insight that they offer into molecular features that are masked in ensemble measurements. Over the past several decades, a variety of fluorescence-based techniques have enabled both in vivo and in vitro studies of the structure, function and dynamics of single molecules1. However, optical single-molecule techniques generally cannot directly resolve temporal changes that occur on sub-millisecond timescales, as imaging times must accommodate the relatively slow rate of photon emission from a single fluorophore.
In contrast, non-optical techniques that offer direct transduction to ion or electron flux can enable studies of dynamic single-molecule processes on microsecond or nanosecond timescales. Nanopore sensors have emerged as one such tool with potential for observing single molecules at high throughput and with fine temporal resolution. A nanopore sensor comprises an insulating membrane with a single nanometer–scale aperture. When both sides of the membrane are exposed to electrolyte solutions, a solitary electrolyte junction forms at the nanopore. An electrode is placed in each solution, and an applied voltage results in a steady-state ionic flux through the pore. The presence of a single analyte molecule causes a transient change in the ionic conductance of the pore, which one observes as an electrical current pulse for each passing molecule. The shape and statistical properties of these pulses are useful for analyzing a biomolecular species in solution. Nanopores can be constructed by a variety of techniques, including biological pores formed by transmembrane proteins2 and synthetic pores fabricated from various materials3.
In addition to their use for biophysical studies, nanopores are a candidate for improved DNA sequencing platforms4, potentially offering extremely high throughput and very long read lengths. However, the transient nature of nanopore signals presents a major limitation; typical velocities of nucleic acids passing through solid-state nanopores, for example, are 10–1,000 ns per base. Despite ongoing efforts to reduce translocation speeds, ‘fast’ translocations are often cited as a critical barrier to the progress of nanopore sensing applications5. Recent work using an enzyme molecule as a molecular ratchet6 appears particularly promising in this respect. Although the signals from nanopores represent a flux of several billion ions per second, in practice nanopore measurements have been constrained to bandwidths below 100 kHz owing to comparatively high background noise.
In this work we consider the bandwidth limitations of conventional nanopore measurements and demonstrate a CMOS-integrated nanopore platform (CNP) that supports signal bandwidths exceeding 1 MHz by exploiting a custom micrometer-scale amplifier optimized for nanopore sensing, integrated in immediate proximity to the pore. We demonstrated the utility of this platform by detecting, to our knowledge for the first time, single-microsecond interactions of individual molecules with nanopores, which enabled us to observe multiple distinct configurations of a short DNA molecule during its passage through a solid-state nanopore.
The CNP centers around a custom-designed, low-noise current preamplifier and a high-performance solid-state nanopore. The preamplifier circuitry occupies 0.2 mm2 in a 0.13-μm mixed-signal CMOS process and is positioned directly inside the fluid chamber (Fig. 1). We placed a thin silicon nitride nanopore7 in the chamber above the amplifier (Online Methods). This design considerably reduced parasitic capacitances, resulting in lower high-frequency noise than in traditional platforms that rely on external electrophysiology amplifiers such as the Axopatch 200B (Molecular Devices) or EPC-10 (HEKA Electronik). The CNP’s planar amplifier design is also well-suited to parallelization, and with the addition of fluidics to isolate the trans chambers of an array of nanopores, the platform can support multichannel detection.
Analysis of bandwidth in nanopore sensing systems is similar to the analysis of voltage-clamp electrophysiology recordings8,9, except that the magnitudes of contributing elements can vary considerably. Both of these systems produce weak ionic currents, and their useful signal bandwidths are generally constrained not by small-signal frequency response but by the signal-to-noise ratio (SNR). Detailed treatments of noise in ion-channel recordings8 often address scenarios with signal amplitudes of 10 pA or less, for which relevant bandwidths are typically less than 10 kHz. However, nanopore sensors often use more concentrated electrolytes and higher holding potentials, producing current pulses of 100 pA from α-hemolysin2, 300 pA for MspA10 and upward of 4 nA for solid-state nanopores7.
A nanopore can be modeled as an ionic resistance, RP, in series with an access resistance, RA11, along with a capacitance from its supporting membrane, CM (Fig. 2a). In addition, capacitance is associated with the measurement electronics (Fig. 2b,c), with contributions from the electrode wiring (CW), the amplifier input (CI) and the amplifier feedback elements (CF). Current (I) signals from nanopores are usually transient and described by their depth (ΔI) and duration (τ) (Fig. 2d).
In the low-frequency regime (<100 Hz), nanopore noise power spectral density is dominated by flicker noise arising from fluctuations in the pore’s ionic conductance12. At moderate frequencies (100–10,000 Hz), sources of white noise in the pore13 or measurement electronics may appear, along with noise generated by energy dissipation in non-ideal dielectric materials (Fig. 2e). Finally, at frequencies >10 kHz, the dominant noise source is the interaction of the amplifier’s voltage noise with the total capacitance at the input. In this regime, the input-referred power spectral density is
and root-mean-squared current noise is
where vn is the voltage noise density (V/√Hz) of the input amplifier, and B is the measurement bandwidth.
To arrive at an SNR metric, previous studies12,14 have defined the signal as ΔI, the average change in current caused by the presence of a molecule in the pore. The corresponding metric is then SNR(B) = ΔI/IRMS(B). To more accurately evaluate performance for brief events, we instead redefined SNR(B,τ) as a function of both bandwidth and pulse duration (Supplementary Discussion). One consequence of this modification is that if a signal contains brief transient events, the SNR may increase for wider bandwidths despite greater IRMS values.
From this analysis, we can define the maximum bandwidth (Bmax) at which the SNR exceeds a minimum value (SNRmin). If τ < 100 μs and B > 1/(2τ), this upper bound is given by
The minimum tolerable SNR will vary, but to avoid substantial false event detection rates it can be reasonable to require an SNR of 5 or more (Supplementary Discussion). Regardless of the exact requirements, it is clear that the available bandwidth increases for larger signal levels (ΔI) and decreases for larger capacitances and amplifier voltage noise. All of the capacitances in this expression are extrinsic to the nanopore and, therefore, eligible for improvement without affecting the properties of the pore itself.
Nanopore signal fidelity is extremely sensitive to parasitic electronic elements at the amplifier input, including any capacitance from the pore membrane (Fig. 2a). Solid-state nanopores are fabricated in thin dielectric membranes, and CM can be modeled by the parallel-plate capacitance of the constituent elements of the membrane (Supplementary Discussion). Early silicon nitride nanopores had CM > 300 pF12. For the nanopores used here (Fig. 1), a thin SiN film was supported by a thick SiO2 layer, and additionally the surface of the membrane chip was covered with a silicone elastomer, leaving only a minimal area exposed to the electrolyte (Online Methods). As a result, CM was reduced to <6 pF. Additional fabrication efforts should allow CM to be reduced below 0.5 pF15.
The close integration of the measurement electronics also reduces CW. In conventional platforms, CW results from any capacitive coupling to other nodes (often >2 pF) from the short length (<10 cm) of wire that connects one electrode to the amplifier input. In the CNP design, a silver–silver chloride (Ag/AgCl) electrode is fabricated on the surface of the amplifier and this wiring distance is less than 100 μm. However, the exposure of the amplifier to the fluid chamber means that the ions in the electrolyte can capacitively couple to the internal wiring of the integrated circuit. To minimize this effect, we covered most of the amplifier surface with a thick layer of epoxy-based photoresist (Online Methods). The resulting CW was <1 pF.
A central component of the CNP is a 3 mm × 3 mm custom integrated circuit fabricated in a 0.13 μm CMOS process. It contains eight low-noise preamplifiers that each occupy 0.2 mm2 and implement a voltage-clamped transimpedance circuit (Fig. 2b). For the experiments presented here, we used only one channel; however, the channels are independent and can be operated in parallel. We adapted several elements of a classical transimpedance topology to make the design suitable for modern integrated circuit technology. In particular, the design must function without the availability of a high-value feedback resistor (RF). Purely capacitive feedback would be appropriate if not for the considerable steady-state bias currents of nanopore sensors. Thus, in place of a traditional feedback resistor, the CNP implements a servo loop with an active low-noise current source16, producing a closed-loop circuit with a gain of 100 MΩ (Fig. 2c). A digitally selectable feedback capacitor CF and a gain element G prevented oscillation by reducing the closed-loop gain above 30 kHz, and the preamplifier was followed by a filter to restore a flat gain response to >1 MHz (Online Methods). We designed the input stage for negligible gate leakage and an input capacitance of CI = 1 pF, and commonly operated it with CF = 0.15 pF. The amplifier had vn = 5 nV √Hz−1, and it consumed 5 mW from a 1.5 V supply.
The measured baseline noise spectrum of the CNP system compared favorably with a similar open-headstage configuration of an Axopatch 200B (Fig. 3a–c). At measurement bandwidths below 10 kHz, the noise of the Axopatch was lower than that of the CNP, owing to the 100 fA2 Hz−1 white-noise density of the CNP’s on-chip current source (Fig. 2c) as compared to 33 fA2 Hz−1 from a discrete 500 MΩ feedback resistor in the Axopatch. However, for B > 10 kHz, the CNP delivered much lower noise. For the highest bandwidth supported by the Axopatch (100 kHz), the CNP had a noise floor of 3.2 pARMS, compared to 9 pARMS for the Axopatch. At the highest bandwidth characterized for the CNP (1 MHz), the noise level was 24 pARMS, in contrast with 247 pARMS modeled by extrapolating the Axopatch response beyond its supported range (Supplementary Discussion).
When we connected a nanopore to the amplifier input, flicker noise and membrane capacitance raised the noise spectrum above the baseline (Fig. 3d–f). We measured ~15 solid-state nanopores with the CNP, and observed considerable pore-to-pore SNR variability, owing to variations in the pore geometry and in CM. For the discussions that follow, we selected data from two representative nanopore devices for analysis. ‘Pore A’ (4.9 nm diameter, CM = 6 pF) had lower membrane capacitance than ‘pore B’ (3.5 nm diameter, CM = 25 pF).
With the lowest-capacitance nanopores measured, such as pore A, we observed noise of 12.9 pARMS and 155 pARMS for bandwidths of 100 kHz and 1 MHz, respectively. For B = 100 kHz, there was more than a factor-of-two reduction in input-referred noise power for the CNP as compared to the Axopatch. If the Axopatch could be measured at higher bandwidths, there would have been a factor-of-six noise power difference at 1 MHz.
Aside from the overall lower noise at high frequencies, we observed that polynomial fits to the noise power spectrum (Fig. 3d) did not contain a substantial linear component at moderate frequencies (>1 kHz), which dominated the high-frequency noise in earlier reports12,14. This is likely attributable to the high-quality dielectric properties of the thermal SiO2 passivation of the nanopore support chip (Supplementary Discussion).
To determine bandwidths that could be supported, we calculated the SNR for each pore as a function of signal bandwidth (Fig. 3g,h). For pore A, SNR was maintained above 10 beyond 600 kHz bandwidth and above 5 beyond 1 MHz. For pore B, SNR values of 10 and 5 were maintained up to 160 kHz and 320 kHz, respectively. In the limit of very small CM, the baseline amplifier noise floor corresponded to usable measurement bandwidth of several megahertz (Fig. 3i).
As an example of the short timescales observable with the CNP, we considered a current trace measured for pore B with 25 base pair (bp) dsDNA (Fig. 4). The pore was biased at 600 mV, digitized at 2.5 MS s−1, and then digitally filtered to both 500 kHz and 100 kHz bandwidths. The 500 kHz trace represents the maximum bandwidth for which SNR > 5 in these conditions (ΔI = 1.3 nA, n = 1,307 events), and we also filtered the data to 100 kHz to compare to the supported bandwidth of other platforms. In a 500-ms period (Fig. 4), 29 molecules translocated through the pore, producing pulses ranging in duration from 1.2 μs to 30.2 μs. Sample points were separated by intervals of 0.4 μs, but the rise and fall times were ~1 μs and ~5 μs for the 500-kHz trace and 100-kHz trace, respectively. Accordingly, events shorter than 10 μs were clearly visible in the 500-kHz trace, but their amplitude was attenuated at 100 kHz. Similarly sized oligomers have been previously measured with solid-state nanopores7,17, but observed pulse durations regularly saturate at the 10–100 μs temporal resolution of the measurements. In some prior instances, experiments have been performed at 0 °C, increasing the viscosity of the electrolyte and slowing the kinetics of surface interactions18. In contrast, we collected the data presented here at room temperature (20–23 °C).
Finer temporal resolution allowed us to consider the statistics of shorter duration events than have been previously characterized. At 3.5 nm diameter, pore B was small enough that oligomer translocation times were dominated by surface interactions rather than electrophoretic forces18,19. As such, we observed a wide variance in translocation times (Fig. 5). Analyisis of this dataset at several different signal bandwidths resulted in a useful illustration of the impact of measurement bandwidth on observed properties of events.
We observed a linear event rate trend with voltage that indicated a diffusion-limited capture regime above an energy barrier20 of 200 mV (Fig. 5a). Although the observed event rates were similar at 400-kHz and 100-kHz bandwidths, the apparent durations and depths of brief events were quite different. Events as short as 2 μs were clearly distinguished at 400 kHz, whereas at 100-kHz, events faster than 10 μs were strongly attenuated and distorted21. This had a marked effect on the observed statistics of the events, exaggerating the duration of short events in the 100-kHz dataset (Fig. 5b,c). Above 400 mV, we continued to observe events below the 2.5 μs response of the 400-kHz filter (Fig. 5d), implying that some of the observed pulses were likely sub-microsecond events that could be better resolved if the membrane capacitance were further decreased.
Although it is simplest to characterize nanopore current blockades as elementary pulses, it is generally acknowledged that, absent noise and bandwidth limitations, the current would be observed to vary within individual blockades owing to changes in the local structure and position of the captured molecule. Previous experiments have distinguished multiple current levels that correspond to folded polymers22, duplex dissociation23, distinct regions in a single polymer24 or conformations of adjacent protein complexes6.
Similarly, for small-diameter nanopores, both molecular-dynamics simulations19 and experiments18 have observed that even brief translocation events consist of several sequential processes. We extended the dataset from pore B with 50-bp dsDNA (Fig. 5) to 500 mV bias (Fig. 6). At this high voltage, we commonly observed translocations with an initial shallow blockage followed by a deeper tail immediately before completion. A reasonable explanation for this intra-event structure is a multistate process (Fig. 6a). First, a diffusing molecule is captured by the nanopore in a sideways orientation, which does not permit translocation, leading to shallow blockade. Then, after the molecule reorients lengthwise, it fully enters the pore and causes a deeper blockade. We observed this event structure more frequently at higher voltage bias (Fig. 6b), which is consistent with a model of an inflexible molecule becoming trapped near the pore opening by high electric fields and frictional forces (duplex DNA has a persistence length of 50 nm, and thus a 15-nm-long 50-bp molecule can be approximated as a rigid rod).
In the dataset derived from 50-bp DNA fragments, the deeper tail was often faster than 10 μs, and it was commonly obscured in low-bandwidth measurements. We analyzed the event tails by computing the mean current of the final 2 μs of each event, and we concluded that the depth of the tail was distinct from the depth of the event as a whole (Fig. 6c). The depth of the last 2 μs exhibited a linear relationship with bias voltage, whereas the remainder of the event did not (Fig. 6d). This supports the hypothesis that the deeper tail signaled the passage of the molecule through the pore, and that in strong electric fields it became increasingly likely that a molecule would be trapped at the mouth of the pore before translocating through it.
With commonly achieved temporal resolution of tens of microseconds, ion channels and nanopores already represent some of the highest bandwidth single-molecule sensing platforms available. By introducing a high-performance CMOS preamplifier directly into the electrochemical environment, we extended nanopore signal bandwidths by at least an order of magnitude. Similar optimizations are directly applicable to measurements of biological ion channels25, especially channels that may exhibit fast conductance fluctuations that are poorly resolved at lower bandwidths. Other electrochemical transducers, such as those based on tunneling junctions26, nanowires27 or carbon nanotubes28, rely on similar electronic circuits, and their larger signal currents could potentially bring single-molecule measurements deep into nanosecond temporal resolutions.
There are many basic research opportunities presented by high-bandwidth bioelectronic interfaces, including the ability to study fast reaction kinetics, single-molecule transport phenomena or rapid conformational changes of macromolecules. Extending single-molecule measurements to megahertz bandwidths can bridge the gap to molecular dynamics simulations, which are often limited to nanosecond timescales for computational reasons29. Benefits would be seen in single-molecule recapture systems30 or closed-loop electrostatic traps31, as the measurement latency in such a system limits its control of fast-diffusing small molecules. Higher bandwidth also allows more precise measurements of the relative timing of events in a multichannel system.
In the context of nanopore DNA sequencing, lower noise spectral density will yield more accurate base calls, and with sufficient signal amplitudes, wider signal bandwidth can support faster translocations and thus higher throughput. As even well-controlled polymer translocation may be somewhat stochastic6, faster measurements will also decrease the likelihood of deletions in a nanopore sequence output.
From a practical standpoint, an important aspect to the promise of nanopore sensors is the ability to scale to arrays of many devices operating in parallel. If implemented in a fully dense array, the design presented here would yield 500 preamplifiers per square centimeter, and additional optimizations would enable several thousand independent channels per square centimeter. Paired with appropriate fluidics and an array of biological or solid-state nanopores, this would represent an extraordinarily high-throughput single-molecule sensing platform.
The amplifier was a custom integrated circuit implemented using a commercial IBM 0.13-μm bulk CMOS mixed-signal process. The chip was designed and simulated using the Cadence Virtuoso software package.
The amplifier die was wirebonded to a 272-pin ball-grid array (BGA) package. Dam-and-fill doughnut epoxy encapsulation (Hysol FP4451 dam and FP4650 fill) covered the exposed gold wirebonds, leaving the die surface exposed.
By default, the amplifier chip surface had ~6-μm-thick passivation above the top metal interconnect layer. To reduce capacitive coupling to the electrolyte, after doughnut encapsulation the chip surface was passivated with the epoxy-based photoresist SU-8. Under yellow light, a drop of SU-8 2015 (Microchem) was manually applied to the surface of the amplifier die, filling the 300 μm-deep cavity formed by the epoxy dam. A light vacuum was applied in a dessicator for 15 min, followed by an overnight prebake in an oven at 80 °C. The chip was exposed in an MJB-3 UV contact aligner using a chrome-on-glass mask, 2,000 mW cm−2 dose, and 360 nm long-pass UV filter (Omega Optical). A post-exposure-bake for 30 min at 50 °C and development in SU-8 Developer (Microchem) yielded a layer of SU-8 ~200–300 μm thick with 300 μm × 300 μm square openings surrounding the 100 μm × 100 μm electrodes.
A watertight fluid chamber was constructed by fastening a 1 cm segment from a polypropylene tube to the top of the BGA package using polydimethylsiloxane (PDMS; Sylgard 184, Dow Corning).
After packaging the die, the aluminum was etched from the exposed surface electrodes by pipetting 500 μl of aluminum etchant (type A, Transene) into the fluid chamber for several minutes, followed by multiple rinses with deionized water.
The chip was mounted on a circuit board, powered on, and digital logic was applied to short-circuit the amplifier feedback element CF, clamping multiple channels’ electrodes at a constant voltage and providing a path for them to sink several micro-amperes of current. A small volume (~1 ml) of silver electroplating solution containing potassium silver cyanide (Transene), was added to the fluid chamber, and a silver wire counterelectrode was attached to a Keithley 2400 I–V meter and placed in the solution. The voltage was adjusted to achieve a counterelectrode current of 1 μA for several minutes, resulting in a deposition of ~10 μm of silver onto each electrode. After electroplating, the chamber was rinsed multiple times with deionized water.
The silver microelectrodes were converted to Ag/AgCl pseudo-reference electrodes by applying a drop of 10 μl 50 mM FeCl3 to the surface for 30 s (ref. 32). After several hours of experiments, the chlorination typically needed to be repeated. We found that the chlorination could be repeated several times before the silver electrode was exhausted.
Images of an electrode at several steps during this process are available in the Supplementary Discussion.
Nanopores in ultrathin silicon nitride membranes were fabricated in a similar manner as described else-where7. Briefly, a 500-μm-thick silicon wafer with <100> crystal orientation (in which the <> notation refers to a material’s three-dimensional crystal orientation) and 5 μm of thermal oxide was coated with 25 nm of low-stress chemical vapor deposition silicon nitride (SiN). Standard UV photolithography was used to pattern square openings on one side of the wafer, through which the nitride and oxide were etched using SF6 plasma. The photoresist was stripped, and an anisotropic KOH etch followed by removal of the oxide layer resulted in ~50 μm × 50 μm free-standing windows on the reverse side of the wafer.
A film of poly-(methyl methacrylate) (PMMA, Microchem) was spun onto the membrane side of the window, and electron-beam lithography was used to pattern a small square opening of 500 nm × 500 nm or smaller. A SF6 plasma etch locally thinned the SiN in this region to ~10–15 nm. The confined area of this ultrathin region helped to limit the capacitance of the membrane and maintain its mechanical integrity. The PMMA was removed by incubation in acetone. A single nanopore was drilled through the thinned region of the nitride membrane using a JEOL 2010F HR-TEM. Fabricated pores were 2–6 nm in diameter, but the best signals from duplex DNA were obtained for 3.5–4 nm pores.
The nanopore chip was cleaned in piranha acid using a procedure described previously33. After rinsing and drying the membrane, it was immediately mounted onto a custom Teflon fluid cell using KWIK-CAST silicone elastomer (World Precision Instruments). The silicone was carefully painted over the majority of the membrane-facing side of the chip, leaving an exposed <1 mm2 area around the membrane (Fig. 1e). Additionally, for these experiments, silicone was applied on the amplifier chip surface, leaving only one preamplifier channel exposed.
When testing with the Axopatch 200B, the Teflon cell was placed into a mating fluid cell containing 1 M KCl 10 mM Tris buffer, pH 8.0. Inside a Faraday cage, two homemade Ag/AgCl pellet electrodes were connected to the headstage input and ground, respectively.
For testing with the CNP amplifier, the circuit board was placed in a small grounded aluminum box and the lower (trans) reservoir was filled with 500 μl 1M KCl, pH 8.0. The upper (cis) chamber in the Teflon cell was filled with 200 μl electrolyte, and the cell was placed into the amplifier chamber. An Ag/AgCl pellet electrode was placed in the cis chamber. The amplifier input voltage was held constant, as the potential of the opposing electrode was varied to apply a bias across the nanopore.
The preamplifier with its attached fluid chamber was mounted in a compression-mount BGA socket (Emulation Technologies) on a 15 cm × 13 cm circuit board and placed in a small aluminum box. The circuit board contained power regulation, biasing circuitry, analog signal buffering and filters, all of which were carefully designed for low-noise operation. The digital inputs to this board were galvanically isolated, and its outputs were fully differential. The board was powered from four AAA batteries and drew 30 mA. A second interface board outside the aluminum box hosted digital isolators, antialiasing filters (4-pole differential Bessel filter, fc = 1 MHz) and data converters (operating between 2–4 MS s−1), as well as an FPGA module (Opal Kelly XEM3010) with a 32 MB hardware data buffer and a high-speed USB interface. The data acquisition and control of the system were managed in real time through a custom graphical interface written in Matlab (MathWorks).
The data were processed using custom Matlab software. Traces were generally digitally filtered with a 128- or 512-tap finite-impulse-response low-pass filter to a desired signal bandwidth while retaining the 2–4 MS s−1 sample rate. Events were typically identified with a two-state thresholding algorithm in Matlab, but for traces with low SNR, a modified algorithm was used to identify the events: First, samples were identified whose values were more than 5 s.d. below the mean open pore current. Next, a local search found the nearest sample points at which the signal was above the open pore current. Finally, event edge times were assigned at the first and last points in these bounds that the signal was more than 4 s.d. from the baseline current.
We thank K. Venta, M. Puster, K. Healy, V. Ray, C. Dean and L. Paninski for their assistance. K.L.S. acknowledges partial support from the Semiconductor Research Corporation through the Focus Center Research Program, the US National Institutes of Health (R33HG003089) and the Office of Naval Research (N00014-09-1-1117). M.D. acknowledges support from the National Institutes of Health (R21HG004767, American Recovery and Reinvestment Act Supplement to R21HG004767 and R21HG006313).
Note: Supplementary information is available on the Nature Methods website.
AUTHOR CONTRIBUTIONSJ.K.R., K.L.S. and M.D. developed the platform concept. J.K.R. designed the amplifier and measurement system. J.K.R., K.L.S., M.W. and M.D. planned experiments. M.W. and C.A.M. fabricated nanopores. J.K.R. and M.W. performed nanopore experiments and analyzed data. J.K.R. and K.L.S. wrote the manuscript. All authors edited the manuscript.
COMPETING FINANCIAL INTERESTS
The authors declare no competing financial interests.
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