with reference now to a more detailed description of a number of embodiments of the present invention and variations thereon , the heart of the invention and the method of using the same is referred to as a nanoscale optofluidic sensor array ( nosa ). the nosa is preferably employed for nucleic acid biosensing , but can be used to detect any molecular interaction that results in a shift of the resonant wavelength of an optical resonator sensor . broadly speaking , the technique relies on shrinking the nanofluidic system down to the same scale as that of the wavelength of light and using a unique nanophotonic resonator sensor to both gain access to the evanescent optical field and provide attoliter scale spatial localization of the reaction site . two specific embodiments of the nosa array are disclosed herein , although it will be understood that the invention is not limited to these and other implementations could be devised . as will be discussed below , both embodiments have the same basic operational architecture but a slightly different detector design . the use of nanoscale fluidics not only enables individual nanowell addressability , but also provides spatial confinement of the targets near the reaction site , increasing the number of target : probe collisions and ensuring that each molecule has an opportunity to become hybridized . as will also be outlined in greater detail below , the use of an electrokinetic transport mechanism not only increases the throughput capabilities ( since the flow velocity is largely independent of channel size ) it also enables use of a recently developed technique for electrokinetic based specificity which has proven successful down to the single nucleotide level . the two stage nanofluidic approach enables unique probe functionalization and target addressing of each nanowell . the first embodiment of the invention is referred to as the side resonator embodiment and is illustrated in fig1 a and 1b . with reference first to fig1 a , a 4 × 5 nosa 10 is shown which includes a group of 4 parallel bus waveguides 12 for receiving incident optical excitation beams 14 . in this embodiment , a series of 5 nanophotonic optical resonator sensors 16 lie to the side of and are evenly spaced from each of the waveguides 12 . as an example , 4 samples can be independently tested against the 5 required probe sites ( one for each serotype and a negative control ) using the nosa 10 . the nosa 10 is preferably formed using silicon on insulator ( soi ) technology where the waveguides 12 and resonator sensors 16 are formed from silicon on a silicon dioxide wafer or substrate 18 . with reference to the close - up view of fig1 b , each of the resonator sensors 16 is formed of first and second 1 - d photonic crystals ( pcs ) 20 and 22 , each of which is formed of first and second groups of spaced nanowells or holes 24 and 26 , respectively . the nanowells 24 and 26 have a different dielectric permittivity than that of the surrounding silicon . the resulting periodic variation in dielectric permittivity results in a band of wavelengths in the bandgap of the pcs 20 and 22 which are not allowed to propagate . in this manner , the pcs 20 and 22 each act as a mirror to these wavelengths . each resonator sensor 16 is easily tunable by adjusting the length of a central defect cavity 28 , which acts both as a resonator and a reaction site or sensing element . light couples evanescently from the adjacent waveguide 12 into the cavity mode of the resonator sensor 16 . the nosa 10 can be easily multiplexed by adding more resonator sensors along the same waveguide , since each resonator sensor generates a characteristic signature in the output spectrum . in the configuration employed in the side resonator embodiment , light at the resonant wavelength of one of the resonator sensors 16 , which is initially traveling in the waveguide 12 , is evanescently coupled into that one of the resonator sensors 16 . the result is a dip in the output spectrum at that given wavelength . this operating principle is graphically depicted in fig2 in which one of the side resonator sensors 16 is shown with fdtd simulations showing a light intensity pattern 30 at resonance which is induced in the resonator cavity 28 by evanescent coupling of the incident light beam 14 passing through the adjacent bus waveguide 12 . this resonance results in a dip in the output power spectrum of the light beam passing out of the waveguide 12 as illustrated . evanescent coupling ensures that the resonator sensor bandgap does not interfere with the light transmission through the waveguide 12 because the resonator sensors 16 lie to the side of the waveguides 12 . as a result , multiplexing along any single one of the waveguides 12 is obtained simply by placing a large number of the side resonator sensors 16 along the waveguide 12 , each of which has a slightly different resonant wavelength . the graph of fig3 shows experimentally obtained resonant dips in the output spectrum of one of the bus waveguides 12 of the nosa 10 of fig1 a . each of the 5 dips corresponds to , and thus acts as a signature for , one of the 5 adjacent resonator sensors 16 . although the embodiment of fig1 a employs 5 of the resonator sensors 16 for each of the waveguides 12 , it should be understood that any suitable number of resonator sensors can be employed . based on the results of the experiments conducted on the side resonator embodiment of the invention , it is expected to be able to multiplex at least 25 resonator sensors along a single waveguide and still be able to distinguish the characteristic signatures of each resonator sensor . when a complementary target is introduced to one of the resonator sensors 16 , molecular binding increases the mass of organics in the cavity 28 and thus the local refractive index is also increased . the result is a red shift of the resonant dip similar to that shown in the graph of fig4 , which shows the change in resonant dip location in response to change in local refractive index . the initial graph shows the initial 5 resonator sensor system of the nosa 10 of fig1 a , where each resonator sensor is addressed with a separate microchannel filled with water ( n = 1 . 33 ). the second graph with the section for channel 2 shifted to the right shows red shift in the dip induced by the second resonator sensor in response to the introduction of a ˜ 1m cacl 2 solution . fig5 is a graph depicting sensitivity experiments on the nosa of fig1 a showing the shift in resonant dip as a function of local refractive index . these experiments confirm the ability of the nosa 10 to detect and identify the location of molecular interactions that occur at any of the resonator sensors 16 . fig6 is a schematic illustration of multi - layer soft - lithography coupling with nanophotonics which is employed to fluidically address and tune photonic structures at the nanoscale in the embodiments of the present invention . as shown , a nosa constructed in accordance with the preferred embodiments includes three main structural components : a photonics layer 40 , a fluidics layer 42 and a valve layer 44 . the photonics layer 40 is what is shown in fig1 a , for example , while the flow and valve layers are employed to carry out two operational stages of the nosa : functionalization of the reaction sites and screening of the sites to deliver samples thereto for binding detections . fig7 a - 7e are graphical illustrations showing the two different operational stages of the first preferred embodiment of the present invention . fig7 a and the close up of 7 b show a functionalization stage in which oligonucleotide probe immobilization is conducted in the optical cavities of the side resonator sensors 16 by aligning pdms fluidics 42 opposite to the direction of the bus waveguides 12 . fig7 c is an illustration of one section of the nosa 10 of fig1 a showing the bus waveguide 12 and 3 of the side resonator sensors 16 with the pdms fluidics 42 graphically shown as defining the location of first , second and third functionalization channels . fig7 d and the close up of 7 e illustrate a screening stage in which delivery fluidics are aligned and sealed and one sample is introduced per resonator sensor 16 . during the first functionalization stage , probe immobilization is conducted by first activating the surface of the resonator cavities with a dendrimer chemistry , then aligning the pdms nanofluidics 42 perpendicular to the direction of the waveguides 12 and finally flowing through a solution of the edc coupling agent and oligonucleotide probes . this allows one to spatially localize the binding sites to the optical cavity of the side resonator sensors 16 . using this technique , each of the resonator sensors 16 along the length of each bus waveguide 12 is functionalized with a different probe . more specifically , the dendrimer chemistry involves the use of either piranha etch or plasma oxidation to generate surface silanol groups , to which the amine - terminated silane aptms ( aminopropyltrimethoxysilane ) are coupled . carboxylic acid terminated dendrimers ( 64 functionalities per dendrimer ) are then covalently linked to amine - functionalized surfaces via water soluble carbodiimide chemistry to increase the surface probe density . the functionalization fluidics 42 are then aligned with the resonator sensors 16 and attached to the nosa 10 . amine - terminated capture dna with sequences specific to the serotypes of interest is then flown over the resonator sensors 16 , bonding with the open groups on the dendrimers . in one experiment , this was characterized by using tamra tagged probes and equating the relative intensity of the florescence signal to the surface probe density . in the actual detection experiments , a 0 . 2 % pvp ( polyvinylpyrrolidone ) surface passivation step was also used in an effort to limit non - specific dna adsorption . after functionalization , the original fluidics 42 are removed , screening fluidics 48 are applied and the sample is introduced as illustrated in fig7 d and 7e . facile exchange in this manner is only possible through the use of elastomeric ( e . g . pdms ) based fluidics which provide the required conformable and reversible sealing to the photonic structures . the screening nanofluidics 48 preferably consist of one nanochannel per photonic test waveguide and are used to deliver the samples directly into the nanowell sites . a recently developed , unique architecture for integrating active nanofluidic elements with silicon - on - insulator photonic crystals is preferably employed ( see erickson , d ., t . rockwood , t . emery , a . scherer , and d . psaltis , nanofluidic tuning of photonic crystal circuits . optics letters , 2006 . 31 ( 1 ): p . 59 - 61 ). this architecture enables fluidic addressability of individual sub - wavelength scale photonic elements ( volume of 5 attoliters ). the ability to address volumes this small within a photonic structure is key to achieving the mass sensitivity required . for target delivery , electrokinetic transport is preferably employed . this facilitates transport in the nanochannels since the front velocity is largely independent of channel size but more importantly it provides a simple technique by which non - specific binding can be reduced and reaction specificity ensured to the single nucleotide level . applying an electrokinetic driving potential allows for precise manipulation of the thermal ( through joule heating ), shear ( through electroosmotic flow ) and electrical ( through electrophoresis ) forces enabling the snp to be discriminated . in another recent work ( erickson , d ., x . z . liu , r . venditti , d . q . li , and u . j . krull , electrokinetically based approach for single - nucleotide polymorphism discrimination using a microfluidic device . analytical chemistry , 2005 . 77 ( 13 ): p . 4000 - 4007 ) it has been demonstrated that through proper control over the shear , electrophoretic and thermal energies within the electrical double layer ( a region extending ˜ 50 nm into the liquid environment from the surface ) one can control reaction specificity down to the single nucleotide level . the technique relies on applying sufficient local energy to the system such that dna hybrids that differ from the target strand by a single base pair are pulled apart , while perfectly matched hybrids remain bound . experiments have confirmed that nearly perfect discrimination is obtained with a very strong signal obtained at the complementary probe site and no appreciable signal obtained at the probes with a single nucleotide difference . kinetic measurements should also be able to be made with this arrangement . fig8 a and 8b illustrate a second embodiment of the invention referred to herein as the inline resonator embodiment . in this embodiment , a nosa 50 is provided , which as in the first embodiment , comprises a plurality of parallel waveguides 52 . however , the inline resonator embodiment differs from the side resonator embodiment in that a single optical resonator sensor 54 is formed in each of the waveguides 52 . the optical resonator sensor 54 includes first and second photonic crystals 56 and 58 , in each of which is formed of a plurality of nanowells 60 and 62 , respectively . as illustrated in fig9 , the nosa 50 employs a unique optical cavity 64 which contains a plurality of reaction sites or wells 66 , 68 , 70 and 72 of increasing size . when a change in refractive index in one of the reaction sites or wells is observed , the effective optical length of the cavity 64 is increased along with the wavelength of the resonant modes . in this embodiment , each successive reaction site or well is twice the length of the previous reaction site or well . because of this relationship , the amount that the resonant wavelength peak shifts can be uniquely related to the combination of the reaction sites or wells 66 - 72 in which a binding reaction has occurred . to illustrate the operating principle of this embodiment and to quantitatively estimate device sensitivity , a series of 2 - d finite different time domain ( fdtd ) simulations were conducted . the simulation domain consisted of a 470 nm wide silicon waveguide ( n = 3 . 5 ) excited over a range of wavelengths . the nanowells 60 and 62 , which define the resonator band gap , were assigned the properties of silica ( n = 1 . 5 ) and the reaction wells were assumed to have an initial refractive index of 1 . 33 ( consistent with that of an aqueous solution ). the reaction nanowells in the simulation were all 250 nm wide and l from fig9 was 200 nm . the extended cavity resulted in multiple resonant peaks within the bandgap . though the cavity is multimode , as long as the peaks are sufficiently well separated , they do not pose an inherent problem . fig1 is a graph showing the shift in resonant peak due to a change in refractive index of 0 . 001 in the 4 different sized reaction sites or wells of the resonator sensor of fig9 . as shown , a change in refractive index in any of the reaction sites or wells increases the optical length of the cavity and thus the wavelength of the resonant peak . since the reaction site or well sizes are selected such that each is double the size of its predecessor , a refractive index change in any combination of the reaction sites or wells causes a shift to a unique location . more specifically , a change in refractive index of δn = 10 − 3 in the first reaction site or well results in a shift of approximately 0 . 007 nm . the reason for this is that the increase in refractive index effectively increases the overall optical length of the cavity . when a similar refractive index change is induced in the second and third reaction sites or wells ( which are 2 and 4 times as long ), shifts of approximately twice ( not shown ) and four times ( shown ) that obtained for the first reaction site or well were obtained . this result extends to the case when a refractive index change is observed in multiple reaction sites or wells . for example , a change in reaction sites or wells two and three results in a shift of approximately 6 times that observed for the first reaction site or well . this unique relationship allows one to design the sensor structure such that a positive binding event in any reaction site or well or combination of reaction sites or wells causes a unique spectral shift . for example positive binding events in reaction sites or wells 1 , 2 and 3 would result in a shift of 1 + 2 + 4 = 7 times that of the base shift whereas a reaction in reaction sites or wells 1 and 4 would cause a shift of 1 + 8 = 9 times . note that while these simulations were conducted for δn = 10 − 3 , further simulations suggest detection levels on the order of δn = 10 − 4 should be possible at the resolution limit of the existing tunable infrared laser . although this embodiment of the invention provides the ability to multiplex detections , the first , side resonator embodiment can generate more detections per waveguide because the side resonator configuration does not affect the bandgap of the incident light beam as does the inline embodiment . fig1 illustrates an optofluidic detection system 100 which employs a nosa 102 that is constructed in accordance with any of the embodiments of the present invention or variations thereon . the system 100 includes a reusable structure 104 which performs all signal processing , communications , etc . and includes a low power 1550 nm laser 106 , silicon - on - insulator ( soi ) waveguides 108 , optical switches 110 , optical power sensor 112 , signal processing and control circuitry 114 and a low power system 116 for electrokinetic sample transport . the optical switches 110 allow the light from the laser 106 to be selectively directed to each of the waveguides 108 which are interfaced to each of the waveguides in the nosa 102 . it should be understood , however , that multiple lasers could be employed , if desired , to eliminate the need for the optical switches 110 . the system 100 also includes a disposable optofluidic cartridge 118 which contains micro / nano - fluidics channels 120 , nanoneedles for sample collection and the nosa 102 . mems latches 124 are provided to couple the reusable structure 104 and the disposable optofluidic cartridge 118 . in addition , optical interconnects 126 and chip - chip electrical interconnects 128 are provided to interconnect the various components of the system 100 . the fabrication procedure for a nosa constructed in accordance with any embodiments of the invention employs conventional e - beam lithographic and pdms casting techniques . as already discussed in conjunction with fig6 , each nosa structure includes 3 main structural components : a photonics layer structure , a nanofluidics layer structure and a valve layer structure . the photonics structure is fabricated by defining a pattern on an soi wafer with an e - beam , followed by developing of the resist and dry etching to define the photonics structure . similarly , the nanofluidics structure is formed in the same manner , but also includes additional photolithography to add microfluidics . casting and curing of the pdms is then carried out . finally , photolithography is also employed to define valves and then the pdms is cast , cured and removed . in summary , the nosa sensor platform described herein represents a substantial improvement in the state of the art . calculations suggest that the platform has the potential for as much as a 100 fold increase in the mass sensitivity over the state of the art . functionalization of the surface should not reduce sensitivity since the shift is based on changes in δn ( i . e . surface functionalization will represent a shift in the base state , but it is not significantly expected to reduce overall sensitivity ). one of the major thrusts in biosensor design is in decreasing the mass limit of detection ( lod ) to enable earlier pathogen detection or to detect more obscure biomarkers . a refractive index change of δn eff = 0 . 009 has been reported for an oligonucleotide surface density of 112 ng / cm 2 probed using an evanescent technique . translating this to the cavity surface area in the nosa and a measured sensitivity of ˜ 150 nm / riu , this suggests that 1 attogram of adsorbed mass will result in a wavelength shift of δλ = 0 . 005 nm , which is well above the resolution of the laser ( δλ = 10 − 4 nm ) used in the experiments on the preferred embodiments . this places the lod well below most resolution liquid phase nanosensor platforms ). in initial nucleic acid detection experiments , a 4 resonator nosa sensor was functionalized with probes specific to ( r1 ) dengue virus serotype 3 , ( r2 ) a control sequence and ( r3 ) dengue virus serotype 1 ( the fourth resonator sensor was used as a refractive index calibrator ). after removal of the functionalization fluidics , a solution containing serotype 3 targets in 4 × ssc buffer , containing formamide and ficoll was introduced . after a 15 minute hybridization time and buffer wash , a shift of approximately 0 . 35 nm was measured at the complimentary site compared with approximately 0 . 05 nm at the control and 0 . 15 nm at the non - complementary serotype . this result confirms that the embodiments of the invention do work as expected and readily detected the larger wavelength shift imparted by the complementary site where the binding of the probe and target sample was expected to occur . although the invention has been disclosed in terms of a number of preferred embodiments and variations thereon it will be understood that numerous other variations and modifications could be made thereto without departing from the scope of the invention as defined in the following claims . for example , although the preferred embodiments are particularly useful for detecting binding of biological probes and targets , the invention can be used to detect any type of optically detectable molecular interaction or reaction that changes the resonant wavelength of the resonant sensors . further , although variation of the resonant wavelength of the sensors through variation of the index of refraction , which induces a change in the effective cavity length of the sensor , is preferred , other techniques , such as temperature changes , could be employed to change the resonant wavelength through actual change of the optical cavity length . in addition , while the use of different cavity lengths is preferred in the embodiments of the invention , different materials having different indexes of refraction to begin with could be employed to provide each reaction site with a different , detectable signature .