Patent Application
20050026304
The invention relates to the field of microarrays and more particularly to an apparatus and method for separating and identifying and quantitating chemical moieties using arrays.
Polynucleotide arrays (such as DNA or RNA arrays) are known and are used, for example, as diagnostic or screening tools. Such arrays include regions of usually different sequence polynucleotides arranged in a predetermined configuration on a substrate. These regions (sometimes referenced as “features”) are positioned at respective locations (“addresses”) on the substrate. In use, the arrays, when exposed to a sample, will exhibit an observed binding or hybridization pattern. This binding pattern can be detected upon interrogating the array. For example, all polynucleotide targets (for example, DNA) in the sample can be labeled with a suitable label (such as a fluorescent dye), and the fluorescence pattern on the array accurately observed following exposure to the sample. Assuming that the different sequence polynucleotides were correctly deposited in accordance with the predetermined configuration, then the observed binding pattern will be indicative of the presence and/or concentration of one or more polynucleotide components of the sample.
Biopolymer arrays can be fabricated by depositing previously obtained biopolymers (such as from synthesis or natural sources) onto a substrate, or by in situ synthesis methods. Methods of depositing obtained biopolymers include dispensing droplets to a substrate from dispensers such as pin or capillaries (such as described in U.S. Pat. No. 5,807,522) or such as pulse-jets (such as a piezoelectric inkjet head, as described in PCT publications WO 95/25116 and WO 98/41531, and elsewhere). For in situ fabrication methods, multiple different reagent droplets are deposited from drop dispensers at a given target location in order to form the final feature (hence a probe of the feature is synthesized on the array substrate). The in situ fabrication methods include those described in U.S. Pat. No. 5,449,754 for synthesizing peptide arrays, and described in WO 98/41531 and the references cited therein for polynucleotides. The in situ method for fabricating a polynucleotide array typically follows, at each of the multiple different addresses at which features are to be formed, the same conventional iterative sequence used in forming polynucleotides from nucleoside reagents on a support by methods of known chemistry. This iterative sequence is as follows: (a) coupling a selected nucleoside through a phosphite linkage to a functionalized support in the first iteration, or a nucleoside bound to the substrate (i.e. the nucleoside-modified substrate) in subsequent iterations; (b) optionally, but preferably, blocking unreacted hydroxyl groups on the substrate bound nucleoside; (c) oxidizing the phosphite linkage of step (a) to form a phosphate linkage; and (d) removing the protecting group (“deprotection”) from the now substrate bound nucleoside coupled in step (a), to generate a reactive site for the next cycle of these steps. The functionalized support (in the first cycle) or deprotected coupled nucleoside (in subsequent cycles) provides a substrate bound moiety with a linking group for forming the phosphite linkage with a next nucleoside to be coupled in step (a). Final deprotection of nucleoside bases can be accomplished using alkaline conditions such as ammonium hydroxide, in a known manner.
The foregoing chemistry of the synthesis of polynucleotides is described in detail, for example, in Caruthers, Science 230: 281-285, 1985; Itakura et al.; Ann. Rev. Biochem. 53: 323-356; Hunkapillar et al., Nature 310: 105-110, 1984; and in “Synthesis of Oligonucleotide Derivatives in Design and Targeted Reaction of Oligonucleotide Derivatives”, CRC Press, Boca Raton, Fla., pages 100 et seq., U.S. Pat. No. 4,458,066, U.S. Pat. No. 4,500,707, U.S. Pat. No. 5,153,319, U.S. Pat. No. 5,869,643, EP 0294196, and elsewhere.
As discussed above, there are a number of techniques for constructing microarrays. In addition, microarrays may be used to identify and quantitate different types of RNA, DNA or protein molecules in a sample. A microarray comprises a number of surface bound molecules that may be arranged in defined locations. For instance, a sample containing an unknown target is often labeled with a fluorescent dye, applied to the array and allowed to react or hybridize to a probe over a period of time. The array is then washed to remove unbound or inappropriately bound sample and scanned for fluorescent signal. The detected signal at each location is correlated to the probe identity.
In the above example, the array provides a few major functions. The first function is that it acts as a separation device that organizes molecules from the sample into known locations and allows the remainder to be discarded. Second, it is a platform to analyze how many sample molecules were detected at each location. The two functions are independent and each confers its own requirements on the assay design.
The separation function requires that the known probe molecule be attached to the surface in a known or defined location. The pattern of features can be in the form of a grid or a linear arrangement. The detection of these hybridizations is due largely to the use of fluorescent dyes coupled to target molecules. Labeling is typically performed during a sample preparation process that can add significant time to the assay completion. Secondly, the use of labels increases costs, and can potentially cross react with other molecules or probes. Therefore, there is a need for an array system, apparatus or technique that eliminates the need for using labels. There is also a need for such apparatus or method to provide a high level of specificity and reproducibility for identifying and separating small sample volumes or quantities.
Microarrays also suffer from the limitation that they can require multiple runs and may require extensive time to employ in an analysis. In addition, they may be limited by hybridization parameters such as requiring a 20 mer or smaller to obtain complete hybridizations. Each of these requirements, therefore, influences the effectiveness of microarrays effectiveness as a clinical or diagnostic device. Therefore, there is a need for analytical devices to be able to separate and identify targets at high speeds.
In contrast, nanopore technologies are now being developed to sequence genomes and nucleic acids, or proteins at high speeds. These techniques attempt to sequence the nucleic acid or protein when it passes through a defined nanopore or structure. The problem with such techniques is that they generally require nucleic acids that are free of other contaminants such as ribonucleic acid (RNA), proteins, or other molecules. Therefore, there is a need to purify or remove contaminants before the molecule to be sequenced reaches the nanopore. Otherwise, the extraneous material or contaminants will interfere with the quality of the overall results. Secondly, these high speed sequencing technologies require a way to easily and efficiently input the biomolecules to be sequenced. These problems and others are addressed by the present invention.
The invention provides an apparatus for identifying a chemical moiety from a sample solution. The system or apparatus comprises a substrate or housing having a channel with at least one microaarray for capturing a chemical moiety from a sample solution, and a nanopore system downstream from the substrate for identifying the chemical moiety received from the substrate channel after the chemical moiety has been released from the microaarray.
The invention also provides a method for separating and identifying a chemical moiety. The method comprises contacting a solution comprising a target molecule to a probe positioned in a micro fluidic channel, binding the target molecule to the probe to separate the target molecule from the solution, releasing the target molecule off of the probe, and identifying or sequencing the target molecule released from the probe. Sequencing or identification may be by way of a nanopore system.
Embodiments of the invention will now be described with reference to the drawings, in which:
Before describing the invention in detail, it must be noted that, as used in this specification and the appended claims, the singular forms “a,” “an,” and “the” include plural referents unless the context clearly dictates otherwise. Thus, for example, reference to “an array” includes more than one “array”. Reference to a “mass spectrometer” or “substrate” includes more than one “mass spectrometer” or “substrate”. In describing and claiming the present invention, the following terminology will be used in accordance with the definitions set out below.
A “biopolymer” is a polymer of one or more types of repeating units. Biopolymers are typically found in biological systems (although they may be made synthetically) and particularly include peptides or polynucleotides, as well as such compounds composed of or containing amino acid analogs or non-amino acid groups, or nucleotide analogs or non-nucleotide groups. This includes polynucleotides in which the conventional backbone has been replaced with a non-naturally occurring or synthetic backbone, and nucleic acids (or synthetic or naturally occurring analogs) in which one or more of the conventional bases has been replaced with a group (natural or synthetic) capable of participating in Watson-Crick type hydrogen bonding interactions. Polynucleotides include single or multiple stranded configurations, where one or more of the strands may or may not be completely aligned with another. A “nucleotide” refers to a sub-unit of a nucleic acid and has a phosphate group, a 5 carbon sugar and a nitrogen containing base, as well as functional analogs (whether synthetic or naturally occurring) of such sub-units which in the polymer form (as a polynucleotide) can hybridize with naturally occurring polynucleotides in a sequence specific manner analogous to that of two naturally occurring polynucleotides. For example, a “biopolymer” includes DNA (including cDNA), RNA, oligonucleotides, and PNA and other polynucleotides as described in U.S. Pat. No. 5,948,902 and references cited therein (all of which are incorporated herein by reference), regardless of the source. An “oligonucleotide” generally refers to a nucleotide multimer of about 10 to 100 nucleotides in length, while a “polynucleotide” includes a nucleotide multimer having any number of nucleotides. A “biomonomer” references a single unit, which can be linked with the same or other biomonomers to form a biopolymer (for example, a single amino acid or nucleotide with two linking groups one or both of which may have removable protecting groups). A “peptide” is used to refer to an amino acid multimer of any length (for example, more than 10, 10 to 100, or more amino acid units). A biomonomer fluid or biopolymer fluid references a liquid containing either a biomonomer or biopolymer, respectively (typically in solution).
A “set” or “sub-set” of any item (for example, a set of features) may contain one or more than one of the item (for example, a set of clamp members may contain one or more such members). An “array”, unless a contrary intention appears, includes any one, two or three dimensional arrangement of addressable regions bearing a particular chemical moiety or moieties (for example, biopolymers such as polynucleotide sequences) associated with that region. An array is “addressable” in that it has multiple regions of different moieties (for example, different polynucleotide sequences) such that a region (a “feature” or “spot” of the array) at a particular predetermined location (an “address”) on the array will detect a particular target or class of targets (although a feature may incidentally detect non-targets of that feature). Array features are typically, but need not be, separated by intervening spaces. In the case of an array, the “target” will be referenced as a moiety in a mobile phase (typically fluid), to be detected by probes (“target probes”) which are bound to the substrate at the various regions. However, either of the “target” or “target probes” may be the one that is to be evaluated by the other (thus, either one could be an unknown mixture of polynucleotides to be evaluated by binding with the other). An “array layout” refers collectively to one or more characteristics of the features, such as feature positioning, one or more feature dimensions, and some indication of a moiety at a given location. “Hybridizing” and “binding”, with respect to polynucleotides, are used interchangeably. When one item is indicated as being “remote” from another, this is referenced that the two items are at least in different buildings, and may be at least one mile, ten miles, or at least one hundred miles apart.
The term “adjacent” or “adjacent to” refers to a component or element that is near, next to or adjoining. For instance, an array may be adjacent to a nanopore system.
All patents and other cited references are incorporated into this application by reference.
The first substrate 115 may comprise a number of different materials well know in the art. For instance, the first substrate 115 may comprise a material selected from the group consisting of metals, plastics, polycarbonate materials, rubber, silica or silicone based materials, and composite materials. The first substrate 115 may comprise flexible or non-flexible materials. As mentioned the first substrate 115 may comprise one or more channels 118. The channel 118 may comprise a micro fluidic channel 118 having one or more probes 121 (See
The sample may comprise one or more targets 103 that are transported through the channel 118. Transport may be accomplished through osmotic pressure, fluidic pressure, Brownian motion, diffusion, osmotic gradient, electro-osmotic gradient, gravity, capillary action, active or passive transport, electrophoresis, pressure, suction or creation of a vacuum or artificial vacuum or other physical or mechanical forces that are well know in the art. The technique is not important. However, functionally it is important that the technique efficiently regulates and allows the targets 103 to bind to the probes 121 that are attached or positioned in the channel 118 of the first substrate 115.
The array 112 may comprise a microarray or similar type device. As discussed, the array 112 may be constructed on the interior wall of channel 118 (See
Referring now to
The array 112 may comprise a biopolymer or in particular a nucleic acid or nucleotide sequence. Other biopolymers know in the art may be employed such as proteins, peptides, amino acids, nucleotides, nucleosides, nucleic acids, RNA, DNA, single stranded RNA, single stranded DNA, double stranded DNA or RNA etc. may be employed with the present invention. The target 103 or probe 121 sequence may be known or unknown. The biopolymers may be arranged in any of a number of orders and/or orientations on the array 112. This allows for the capture and release of biopolymers in a defined order or sequence.
The nanopore system 120 is positioned downstream from the array 112 (See
Typical nanopore systems used with the present invention may comprise and not be limited to devices disclosed and discussed in U.S. Pat. No. 5,795,782, U.S. Pat. No. 6,015,714, WO 01/81896 A1, WO 01/81908 A1 and others. The nanopore system may employ a pore molecule such as the receptor for bacteriophage lambda (LamB) or alpha-hemolysin, to record the process of biopolymer injection or traversal through the channel pore when that channel has been isolated on a membrane patch or inserted into a synthetic lipid bilayer. The apparatus used for the nanopore system comprises: 1) an ion-conducting pore or channel, perhaps modified to include a linked or fused polymerizing agent; 2) the reagents necessary to construct and produce a linear polymer to be characterized, or the polymerized molecule itself; and 3) an amplifier and recording mechanism to detect changes in conductance of ions across the pore as the polymer traverses its opening. A variety of electronic devices are available which are sensitive enough to perform the measurements used in the invention, and computer acquisition rates and storage capabilities are adequate for the rapid pace of sequence data accumulation.
Channels and pores useful in the invention may vary (e.g., minimum pore size around 2-9 nm). Pore sizes across which polymers can be drawn may be quite small and do not necessarily differ for different polymers. Pore sizes through which a polymer is drawn will be e.g., approximately 0.5-2.0 nm for single stranded DNA; 1.0-3.0 nm for double stranded DNA; and 1.0-4.0 nm for polypeptides. These values are not absolute, however, and other pore sizes might be equally functional for the polymer types mentioned above.
Examples of bacterial pore-forming proteins which can be used in the invention include Gramicidin (e.g., Gramicidin A, B, C, D, or S, from Bacillus brevis; available from Fluka, Ronkonkoma, N.Y.); Valinomycin (from Streptomyces fulvissimus; available from Fluka), LamB (maltoporin), OmpF, OmpC, or PhoE from Escherichia coli, Shigella, and other Enterobacteriaceae, alpha-hemolysin (from S. aureus), Tsx, the F-pilus, and mitochondrial porin (VDAC). This list is not intended to be limiting.
A modified voltage-gated channel can also be used in the invention, as long as it does not inactivate quickly, e.g., in less than about 500 msec (whether naturally or following modification to remove inactivation) and has physical parameters suitable for e.g., polymerase attachment (recombinant fusion proteins) or has a pore diameter suitable for polymer passage. Methods to alter inactivation characteristics of voltage gated channels are well known in the art (see e.g., Patton, et al., Proc. Natl. Acad. Sci. USA, 89:10905-09 (1992); West, et al., Proc. Natl. Acad. Sci. USA, 89:10910-14 (1992); Auld, et al., Proc. Natl. Acad. Sci. USA, 87:323-27 (1990); Lopez, et al., Neuron, 7:327-36 (1991); Hoshi, et al., Neuron, 7:547-56 (1991); Hoshi, et al., Science, 250:533-38 (1990), all hereby incorporated by reference).
Appropriately sized physical or chemical pores may be induced in a water-impermeable barrier (solid or membranous) up to a diameter of about 9 nm, which should be large enough to accommodate most polymers (either through the pore or across its opening). Any methods and materials known in the art may be used to form pores, including track etching and the use of porous membrane templates that can be used to produce pores of the desired material (e.g., scanning-tunneling microscope or atomic force microscope related methods).
Chemical channels or pores can be formed in a lipid bilayer using chemicals (or peptides) such as Nystatin, as is well known in the art of whole-cell patch clamping (“perforated patch” technique); ionophores such as A23187 (Calcimycin), ETH 5234, ETH 157 (all chemicals available from Fluka, Ronkonkoma, N.Y.; this list is not intended to be limiting), peptide channels such as Alamethicin, etc.
To produce pores linked with polymerase, synthetic/recombinant DNA coding for a fusion protein can be transcribed and translated, then inserted into an artificial membrane in vitro. For example, the C-terminus of E. coli DNA polymerase I (and by homology, T7 polymerase) is very close to the surface of the major groove of the newly synthesized DNA. If the C-terminus of a polymerase is fused to the N-terminus of a pore forming protein such as colicin E1 and the colicin is inserted into an artificial membrane, one opening of the colicin pore should face the DNA's major groove and one should face the opposite side of the lipid bilayer. For example, the colicin molecule can be modified to achieve a pH optimum compatible with the polymerase as in Shiver et al. (J. Biol. Chem., 262:14273-14281 1987, hereby incorporated by reference). Both pore and polymerase domain can be modified to contain cysteine replacements at points such that disulfide bridges form to stabilize a geometry that forces the pore opening closer to the major groove surface and steadies the polymer as it passes the pore opening. The loops of the pore domain at this surface can be systematically modified to maximize sensitivity to changes in the DNA sequence.
Since channel events can be resolved in the microsecond range with the high resolution recording techniques available, the limiting issue for sensitivity with the techniques of our invention is the amplitude of the current change between bases. Resolution limits for detectable current are in the 0.2 pA range (1 pA=6.24.times.10.sup.6ions/sec). Each base affecting pore current by at least this magnitude is detected as a separate base. It is the function of modified bases to affect current amplitude for specific bases if the bases by themselves are poorly distinguishable.
The following specific examples of current based polymer characterization are presented to illustrate, not limit the invention. The LamB pore Maltoporin (LamB) is an outer membrane protein from E. coli that functions as a passive diffusion pore (porin) for small molecules and as a specific transport pore for passage of maltose and maltodextrins (Szmelcman et al., 1975, J. Bacteriol., 124:112-18). It is also the receptor for bacteriophage lambda (Randall-Hazelbauer and Schwartz, 1973, J. Bacteriol. 116:1436-1446). Three identical copies of the LamB gene product assemble to form the native pore. Each subunit (MW. about 48,000) is composed of predominantly beta-structure and is a pore in itself, though it is thought that the three pores fuse into one at the periplasmic side of the membrane (Lepault et al., 1988, EMBO, J., 7:261-68).
A protein folding model for LamB is available that predicts which portions of the mature protein reside on the external and periplasmic surfaces of the membrane (Charbit et al., 1991, J. Bacteriol., 173:262-75). Permissive sites in the protein have been mapped to several extra membranous loops that tolerate the insertion of foreign polypeptides without significantly disrupting pore properties (Boulain et al., 1986, Mol. Gen. Genet., 205:339-48; Charbit et al., 1986, EMBO J., 5:3029-37; Charbit et al., 1991, supra). The LamB protein has been crystallized and a high resolution structure derived (3.1 ANG.) (Schirmer et al., 1995, Science, 267:512-514).
The pore properties of wild type LamB and a few mutant proteins have been studied at low resolution in planar lipid bilayer single channel recordings (Benz et al., 1986, J. Bacteriol., 165:978-86; Benz et al., 1987, J. Membrane Biol., 100:21-29; Dargent et al., 1987, FEBS Letters, 220:136-42; Dargent et al., 1988, J. Mol. Biol., 201:497-506). The pore has a very stable conductance of 150 pS in 1M NaCl, and shows selectivity for maltose and maltodextrins. These molecules effectively block conductance of the pore. One LamB mutant (Tyr.sup.163.fwdarw.Asp) exhibits distinct sublevels of conductance (30 pS each).
The LamB pore is extremely stable, and high time resolution recordings can be made for use in this invention. The time resolution of channel conductance measurements with the conventional planar lipid bilayer technique is limited because of the background noise associated with the high electrical capacitance of bilayers formed on large diameter apertures (100-200 microns), but smaller apertures or insulated glass microelectrodes can improve the resolution of LamB channel recordings. Preferably, improved LamB conductance recordings will use the pipette bilayer technique (Sigworth et al., supra). Discussion and examples of the invention using the bacterial pore-forming protein alpha-hemolysin toxin (alpha-toxin or alpha-hemolysin) are below. This system operates as nucleic acid polymers are threaded through the toxin pore, and the monomeric charges and physical obstruction alter ionic conductance through the pore. Because the purine and pyrimidine bases in the polynucleotide have differing molecular sizes and chemical properties, a specific ionic current will flow as each nucleotide enters and passes through the channel, thus electro-sensing the monomer sequence in the linear polymer.
The bacterial pore-forming protein from S. aureus, α-hemolysin, spontaneously embeds in lipid bilayers to produce a large, heptameric, currentconducting channel α-hemolysin forms a robust channel which has the appropriate diameter to admit a single stranded DNA polymer. Furthermore, it can remain open for indefinite time periods when subjected to a continuous voltage gradient. Diphytanoyl phosphatidylcholine has been used to form lipid bilayer membranes across 0.2 mm holes in a Teflon film separating two compartments containing buffer solution of the following composition: 1M NaCl, 10 mM Tris, pH 7.4 (Montal et al., 1972, PNAS, 69:3561). In initial, multi-channel experiments, alpha.-hemolysin has been added to the cis side of the bilayer and allowed to incorporate into the bilayer before excess alpha.-hemolysin is removed. Voltage can be applied across the bilayer that are varied from 0 mV to 140 mV. Under the buffer conditions used, the channels continuously open before addition of polynucleotide. After addition of poly A to the cis chamber, the channels begin to exhibit transient blockades at potentials greater than 100 mV. Similar effects can be seen with poly C and poly U polymer additions. Significantly, the blockades occur when the voltage is applied in the direction expected to produce electrophoretic movements of a poly-anion like RNA from the cis to the trans side of the channel, i.e., only when the trans side is positive.
Further experiments with single channels demonstrate many well-resolved individual channel blockades in the presence of poly A, poly C, or poly U molecules. Qualitatively, the number of transient blockades is proportional to the concentration of the polynucleotide. Typical-current blockades exhibited 85-90% reductions of current amplitude and last up to several milliseconds. Because the polynucleotide preparations often contain a range of molecular weights, blockade duration to polynucleotide length is not generally quantitated. But qualitatively, average blockade duration is often greater when using solutions containing longer RNA polymers (MW 140 kb-1700 kb) than when using solutions containing shorter polymers (MW 77 kb-160 kb). Occasionally, long-lived blockades of several seconds or more can be observed. These often clear spontaneously, but can be cleared by briefly reversing the voltage polarity. Again, there is virtually no effect on the magnitude of channel conductance when the trans side is negative. To verify that the polynucleotides are producing the long-lived blockades, RNAse can be added to the RNA in the cis chamber to gradually hydrolyze it. When RNAse is added to poly U in the cis chamber while transient blockades are being observed, the duration of the transient blockades, but not their amplitude, gradually decreased over a period of several minutes, eventually becoming too short to be detectable. Having described the apparatus of the invention and a sample nanopore system, a description of the method of assembling or making the array hybridization apparatus is now in order.
While a significant benefit of the apparatus is to avoid the use of labels, it may be advantageous in certain instances to combine detection techniques. A labeled sample allows for fluorescent detection in-situ. A follow up elution or mass spectrometry measurement may provide more detailed information or confirmation of the measurements. Alternatively, it may be desirable to elute the target and analyze by gel eletrophoresis. This secondary and more expensive approach may be of interest for a reference laboratory or a central research facility.
Having described the apparatus of the invention, a description of the method of assembling or making the array hybridization apparatus is now in order.
Referring now to
The RNA sample comprising unlabeled RNA and known control DNA targets is fragmented to lengths of approximately 200 mer using methods known in the art. Using a pipette, the channel is filled or nearly filled with the target. The chip is placed into an instrument that removably seals valve-controlled fluidic lines to each of the openings in the chip. In addition, the instrument controls the temperature of the chip.
The input valve 135 and exit valve 137 are adjusted so that each end of the chip is connected to a source of variable and controllable pressure that may be alternated to be above and below standard pressure as needed. The pressure sources are alternated to cause the sample to move back and forth in the channel such that the area with the features is never dry, but the sample is moved over the features. This sample movement process overcomes the limitations of diffusion and exposes more of the total sample to each feature. The mixing or sample movement process is continued continuously or periodically throughout the hybridization process. Additionally, the instrument heats the chip to the desired hybridization temperature, typically 37-65° C. and maintains the temperature for 1 to 24 hours, typically overnight.
After the hybridization period is complete, the instrument's valve at the inlet of the glass chip switches from the pressure pulses to the first wash fluid. The valve switches from pressure to the waste container. The first wash fluid is pumped through the channel driving the sample to the waste container and washing the array surface to remove unbound or non-specially bound sample. The wash fluid is generally not recirculated, although it may be. Next, the input valve 135 is switched to a second wash fluid that is added by way of wash buffer inlet port 138 as required by the assay. The wash fluid may be pumped through the channel for several minutes. During the wash protocol, the chip's temperature is generally returned to room temperature.
At the conclusion of the wash protocol, the input valve 135 is switched to the elution buffer. Elution buffer is pumped into the channel by way of the elution buffer inlet port 140 until the wash buffer is removed to waste. Then the exit valve 137 closes preventing any further fluid movement. The temperature of the system is raised above the melting point of the probes 121 driving the target from the probes 121 and into the elution buffer.
The exit valve 137 switches to the electrospray tip 130 and the electrospray mass spectrometer is then activated. The elution buffer is driven through the electrospray tip 130 into the mass spectrometer. The amount of target 103 eluted at each time point is quantitated. Since the flow rate is known, the signal at each time point can be correlated to each feature on the array for target identification. The control targets are used to establish the starting and ending points of the array as well as validate the timing along the array.
In summary, the method of the present invention operates for separating and detecting a chemical moiety such as a biopolymer. The steps of the method comprise contacting a sample comprising a target molecule to a probe positioned in a channel of a substrate, capturing the target molecule by contacting it with a probe, releasing the target molecule from the probe in a defined order and detecting the target molecule released from the probe in the defined order.
Clearly, minor changes may be made in the form and construction of the invention without departing from the scope of the invention defined by the appended claims. It is not, however, desired to confine the invention to the exact form herein shown and described, but it is desired to include all such as properly come within the scope claimed.
