Site-directed immobilisation of antibody fragments for detection of C-reactive protein

C-reactive protein, CRP antibody Fab'-fragments have been attached on pre-cleaned gold slides and protein repellent polymers have been used to block the remaining free space in between the antibody fragments. At optimal conditions the antibody fragments are site-directly immobilised on the surface and non-specific binding is reduced. The amount of Fab'-fragments in the polymer host monolayer has been optimised for various buffers. Binding of CRP to Fab'-fragment/polymer layers produced in phosphate buffered saline decreased with NaCl salt concentration. In a 1M NaCl phosphate buffer, the antibodies seem to be randomly oriented on the surface with a similar response to CRP as that of an antibody F(ab)(2)-fragment layer. In a 150 mM NaCl phosphate buffer, on the other hand, the fragments seem to be site-directly oriented and the response to CRP was fivefold. The highest response to CRP was obtained to a layer with a Fab'-fragment concentration of 60 microg/ml. CRP could be detected in a concentration range of 1 ng/ml to 50 microg/ml from a standard solution in phosphate buffer and in a range of 4 ng/ml to 50 microg/ml from serum/PBS. CRP was, moreover, successfully detected in patient samples with good reproducibility. The layer would thus be sensitive enough to analyse the CRP concentration in human serum for predicting cardiovascular disease.     

Development of antibody array for simultaneous detection of foodborne pathogens

Pathogenic bacterial contaminations present serious problems for food industry and public health. Rapid, accurate and affordable assays are needed. In this study, antibody arrays to simultaneously detect two foodborne pathogenic bacteria (Escherichia coli O157:H7 and Salmonella spp.) have been developed using chemiluminescent detecting system. Solid supports using nitrocellulose membrane and poly-l-lysine (PLL) glass slide were compared and optimized for antibody array construction. Many parameters including optimal concentrations of antibodies, blocking reagents, assay time, storage time, sensitivity and cross-reactivity were considered during optimization. This study revealed that the PLL slide was a more suitable support due to highly accurate results and the absence of non-specific background. Phosphate-buffered saline (PBS, pH 7.2) and 3% skim milk in PBS buffer were optimal spotting and blocking reagents, respectively. With the same sensitivity for bacterial detection as in a conventional ELISA (10(5)-10(6)CFU/ml for the E. coli O157:H7 and 10(6)-10(7)CFU/ml for Salmonella detections), this antibody array has advantages of a much shorter assay time of 1h and much lower required amounts of antibodies. Moreover, there was no cross-reactivity in the detection among bacteria tested in this study. Bacteria detection in food sample was feasible as demonstrated using bacteria-added milk.     

Microfluidic chips controlled with elastomeric microvalve arrays

Miniaturized microfluidic systems provide simple and effective solutions for low-cost point-of-care diagnostics and high-throughput biomedical assays. Robust flow control and precise fluidic volumes are two critical requirements for these applications. We have developed microfluidic chips featuring elastomeric polydimethylsiloxane (PDMS) microvalve arrays that: 1) need no extra energy source to close the fluidic path, hence the loaded device is highly portable; and 2) allow for microfabricating deep (up to 1 mm) channels with vertical sidewalls and resulting in very precise features.The PDMS microvalves-based devices consist of three layers: a fluidic layer containing fluidic paths and microchambers of various sizes, a control layer containing the microchannels necessary to actuate the fluidic path with microvalves, and a middle thin PDMS membrane that is bound to the control layer. Fluidic layer and control layers are made by replica molding of PDMS from SU-8 photoresist masters, and the thin PDMS membrane is made by spinning PDMS at specified heights. The control layer is bonded to the thin PDMS membrane after oxygen activation of both, and then assembled with the fluidic layer. The microvalves are closed at rest and can be opened by applying negative pressure (e.g., house vacuum). Microvalve closure and opening are automated via solenoid valves controlled by computer software.Here, we demonstrate two microvalve-based microfluidic chips for two different applications. The first chip allows for storing and mixing precise sub-nanoliter volumes of aqueous solutions at various mixing ratios. The second chip allows for computer-controlled perfusion of microfluidic cell cultures.The devices are easy to fabricate and simple to control. Due to the biocompatibility of PDMS, these microchips could have broad applications in miniaturized diagnostic assays as well as basic cell biology studies.     

A disposable bio-nano-chip using agarose beads for high performance immunoassays

This article reports on the fabrication of a disposable bio-nano-chip (BNC), a microfluidic device composed of polydimethylsiloxane (PDMS) and thiolene-based optical epoxy which is both cost-effective and suitable for high performance immunoassays. A novel room temperature (RT) bonding technique was utilized so as to achieve irreversible covalent bonding between PDMS and thiolene-based epoxy layers, while at the same time being compatible with the insertion of agarose bead sensors, selectively arranged in an array of pyramidal microcavities replicated in the thiolene thin film layer. In the sealed device, the bead-supporting epoxy film is sandwiched between two PDMS layers comprising of fluidic injection and drain channels. The agarose bead sensors used in the device are sensitized with anti-C-reactive protein (CRP) antibody, and a fluorescent sandwich-type immunoassay was run to characterize the performance of this device. Computational fluid dynamics (CFD) was used based on the device specifications to model the bead penetration. Experimental data revealed analyte penetration of the immunocomplex to 100 μm into the 280 μm diameter agarose beads, which correlated well with the simulation. A dose-response curve was obtained and the linear dynamic range of the assay was established over 1 ng/mL to 50 ng/mL with a limit of detection less than 1 ng/mL.     

Target delivery in a microfluidic immunosensor

A study is presented that examines the effect of microfluidic mixing elements on direct and sandwich assays performed in microchannels. Patterned grooves were embossed in the top of microchannels made in PDMS using soft lithography. The grooves redirected the fluid flowing in the channel, enhancing delivery of the target from the bulk fluid to the surface and preventing the formation of a depletion layer at the surface. Comparing assays in grooved and plain channels demonstrated that the mixers improved assay results by 26-46%. A computational flow analysis showed that the grooves caused virtual particles in the bulk flow to come close to the surface ( approximately 11 microm) which is consistent with the signal increase seen experimentally. Direct assays for several concentrations of CY5-labeled biotin were performed in the microchannels. The mixers also improved signal intensity in sandwich assays for botulinum toxin which required mixing of the reagents as well as the direction of the target to the surface.     

Development of low-cost microfluidic systems for lab-on-a-chip biosensor applications

In this work, we develop low-cost microfluidic systems based on polydimethylsiloxane (PDMS) for lab-on-a-chip applications. PDMS microfluidic structures have been fabricated by micromolding, PDMS casting, and plasma bonding processes. The micromolding technique is used to fabricate PDMS slabs with micro-sized grooves, and the complete microchannel is formed by bonding PDMS slab with glass or PDMS substrate. The molding procedure using SU-8 photoresist patterning on silicon wafer, PDMS microchannel fabrication, and PDMS surface treatment using oxygen plasma and TiO₂ coating, are discussed. The various parameters for oxygen plasma treatment including RF power and treatment time are studied in order to obtain conditions for good bonding with the glass substrate. The best condition for plasma treatment is found to be the low RF power (8 W) with 5 min treatment time. In addition, TiO₂ coating with oxygen plasma treatment has been applied to make PDMS surface more hydrophilic to improve aqueous solution compatilbility. The microfluidic channels for various applications, including sample injection cross channel, micropump channel, T and Y sample mixers, PCR thermocyling chamber and channel, capillary electrophoresis flow channel, and conductimetric systems have been fabricated. Finally, a typical application of the PDMS chip in a flow injection conductimetric system for sodium chloride detection has been demonstrated.     

Single cell level detection of Escherichia coli in microfluidic device

Detection of Escherichia coli K-12 in phosphate buffered saline (PBS) was demonstrated in a Y-channel polydimethylsiloxane (PDMS) microfluidic device through optical fiber monitoring of latex immunoagglutination. The latex immunoagglutination assay was performed for serially diluted E. coli solutions using 0.92-microm highly carboxylated polystyrene particles conjugated with polyclonal anti-E. coli. Pre-treatments such as cell lysis or culturing to enhance the signal were not used. Proximity optical fibers around the view cell of the device were used to quantify the increase in 45 degrees forward light scattering of the immunoagglutinated particles. In order to reduce false positive signals caused by antibodies binding to non-viable E. coli cells or free antigens in solution, target solutions were washed three times, and then the results were compared to non-washing treatments. The detection limit was found to be less than 10 cfu ml(-1) (1 cfu per device) without PBS washing (thus detecting non-viable cells and free antigens), or less than 40 cfu ml(-1) (4 cfu per device) with PBS washing (thus detecting viable E. coli cells only).     

Fabrication of lab-on chip platforms by hot embossing and photo patterning

In this paper, we review the approaches developed in our laboratory to fabricate polymer-based microfluidic devices to suit a range of applications in bio- or chemical analysis. Thermoplastic materials such as polycarbonate (PC) and poly(methyl methacrylate) (PMMA) are used to fabricate microfluidic devices via hot embossing. To emboss microchannels, we use hard stamps fabricated in silicon or soft stamps molded on poly(dimethylsiloxane) (PDMS). Hard stamps are fabricated on silicon wafers through photolithography and deep reactive ion etching (DRIE). Soft stamps are fabricated by casting PDMS prepolymer on silicon molds. To enclose the fluidic channels, direct fusion bonding was found to produce the highest bond strength with minimal structural deformation. One-step photolithographic methods have also been explored to produce via photochemical patterning microfluidic structures in photocurable materials. We use the photocurable capabilities of a PDMS copolymer, which incorporates a methacrylate crosslinker. Microfluidic channels are produced via one step-photopatterning processes by crosslinking the prepolymer mixture through a photomask. The smaller feature size attainable was 100 microm. Structures with higher spatial resolution are fabricated through a photoimprinting process whereby a mold is pressed against the precured mixture during UV crosslinking exposure. The application of the fabricated fluidic devices in electrophoretic ion analysis is also presented.     

A New Tool for Routine Testing of Cellular Protein Expression: Integration of Cell Staining and Analysis of Protein Expression on a Microfluidic Chip-Based System

The key benefits of Lab-on-a-Chip technology are substantial time savings via an automation of lab processes, and a reduction in sample and reagent volumes required to perform analysis. In this article we present a new implementation of cell assays on disposable microfluidic chips. The applications are based on the controlled movement of cells by pressure-driven flow in microfluidic channels and two-color fluorescence detection of single cells. This new technology allows for simple flow cytometric studies of cells in a microfluidic chip-based system. In addition, we developed staining procedures that work “on-chip,” thus eliminating time-consuming washing steps. Cells and staining-reagents are loaded directly onto the microfluidic chip and analysis can start after a short incubation time. These procedures require only a fraction of the staining reagents generally needed for flow cytometry and only 30,000 cells per sample, demonstrating the advantages of microfluidic technology. The specific advantage of an on-chip staining reaction is the amount of time, cells, and reagents saved, which is of great importance when working with limited numbers of cells, e.g., primary cells or when needing to perform routine tests of cell cultures as a quality control step. Applications of this technology are antibody staining of proteins and determination of cell transfection efficiency by GFP expression. Results obtained with microfluidic chips, using standard cell lines and primary cells, show good correlation with data obtained using a conventional flow cytometer.     

Application of on-chip cell cultures for the detection of allergic response

In this report, the development of a microfluidic cell chip for monitoring allergic response is described. A rat basophilic leukemia cell line (RBL-2H3), a tumor analog of rat mucosal mast cells, has been used as a model to observe its allergic response upon antigen stimulus. The cells were cultivated on a poly(dimethylsiloxane) (PDMS) chip, the surface of which was modified by several methods. The PDMS chip, which comprised a cell cultivation chamber and microfluidic channels, was fabricated by conventional molding methods. In order to detect the allergic response, a fluorescent dye, quinacrine, was introduced inside the cell compartment that included histamine. The cells were stimulated with dinitrophenylated bovine serum albumin (DNP-BSA) after incubation with anti-DNP IgE. When exocytosis events occurred, the microfluidic system detected the fluorescent signal of quinacrine, which was released from RBL-2H3 cells by using a photomultiplier tube (PMT) fitted onto a microscope.     

A fast cell loading and high-throughput microfluidic system for long-term cell culture in zero-flow environments

We present a simple technique for cell loading, culturing, and phenotypic study in a multi-chamber microfluidic device made of polydimethylsiloxane (PDMS). This technique is based on the use of degassing induced aspiration of PDMS which allows loading cells into micro-cavities within 1 min. A large number of triangle cavities are patterned aside main flow channels with narrow connections so that cells can be loaded by aspirating into each cavity. In our device, high throughput and long-term monitoring can be done with minimum shear force of the flow. As a demonstration, we show a controlled loading at single cell level and the phenotypic variation of gene expression of the yeast strain w303 as a function of copper ion concentration of the medium.     

Comparative modeling and analysis of microfluidic and conventional DNA microarrays

A theoretical analysis was developed to predict molecular hybridization rates for microarrays where samples flow through microfluidic channels and for conventional microarrays where samples remain stationary during hybridization. The theory was validated by using a multiplexed microfluidic microarray where eight samples were hybridized simultaneously against eight probes using 60-mer DNA strands. Mass transfer coefficients ranged over three orders of magnitude where either kinetic reaction rates or molecular diffusion rates controlled overall hybridization rates. Probes were printed using microfluidic channels and also conventional spotting techniques. Consistent with the theoretical model, the microfluidic microarray demonstrated the ability to print DNA probes in less than 1 min and to detect 10-pM target concentrations with hybridization times in less than 5 min.     

"Macromolecules to PDMS transfer" as a general route for PDMS biochips

"Macromolecules to PDMS transfer" technique relying on the direct entrapment of macromolecules spots during PDMS polymerisation is proposed as an alternative for the easy and simple PDMS surface modification. In the present work, the development of three different applications based on this procedure is presented as proof of the method potentialities. First, C-reactive protein (CRP) sandwich immunoassay using immobilised monoclonal anti-CRP antibodies was developed for sepsis diagnosis. The preserved integrity of the immobilised monoclonal immunoglobulin permitted the sensitive detection of free CRP in human sera (LOD=12.5 microg/L, detection ranging over two decades). Then, rheumatoid arthritis diagnosis through the rheumatoid factor (RF) detection based on rabbit immunoglobulins immobilisation allowed the detection of specific antibodies in human sera samples down to low RF levels (detection range 5.3-485 IU/mL). Finally, the "Macromolecules to PDMS transfer" procedure was used to easily and rapidly produce fibronectin-based cell culture arrays. The successful attachment of HeLa and BALB/3T3 cells was demonstrated with optical microscopy and specific staining of actin and vinculin.     

Quantification of Cardiovascular Biomarkers in Patient Plasma by Targeted Mass Spectrometry and Stable Isotope Dilution

Verification of candidate biomarkers requires specific assays to selectively detect and quantify target proteins in accessible biofluids. The primary objective of verification is to screen potential biomarkers to ensure that only the highest quality candidates from the discovery phase are taken forward into preclinical validation. Because antibody reagents for a clinical grade immunoassay often exist for a small number of candidates, alternative methodologies are required to credential new and unproven candidates in a statistically viable number of serum or plasma samples. Using multiple reaction monitoring coupled with stable isotope dilution MS, we developed quantitative, multiplexed assays in plasma for six proteins of clinical relevance to cardiac injury. The process described does not require antibodies for immunoaffinity enrichment of either proteins or peptides. Limits of detection and quantitation for each signature peptide used as surrogates for the target proteins were determined by the method of standard addition using synthetic peptides and plasma from a healthy donor. Limits of quantitation ranged from 2 to 15 ng/ml for most of the target proteins. Quantitative measurements were obtained for one to two signature peptides derived from each target protein, including low abundance protein markers of cardiac injury in the nanogram/milliliter range such as the cardiac troponins. Intra- and interassay coefficients of variation were predominantly <10 and 25%, respectively. The configured multiplex assay was then used to measure levels of these proteins across three time points in six patients undergoing alcohol septal ablation for hypertrophic obstructive cardiomyopathy. These results are the first demonstration of a multiplexed, MS-based assay for detection and quantification of changes in concentration of proteins associated with cardiac injury in the low nanogram/milliliter range. Our results also demonstrate that these assays retain the necessary precision, reproducibility, and sensitivity to be applied to novel and uncharacterized candidate biomarkers for verification of proteins in blood.Discovery of disease-specific biomarkers with diagnostic and prognostic utility has become an important challenge in clinical proteomics. In general, unbiased discovery experiments often result in the confident identification of thousands of proteins, hundreds of which may vary significantly between case and control samples in small discovery studies. However, because of the stochastic sampling of proteomes in discovery “omics” experiments, a large fraction of the protein biomarkers “discovered” in these experiments are false positives arising from biological or technical variability. Clearly discovery omics experiments do not lead to biomarkers of immediate clinical utility but rather produce candidates that must be qualified and verified in larger sample sets than were used for discovery (1).Traditional, clinical validation of biomarkers has relied primarily on immunoassays because of their specificity and sensitivity for the target analyte and high throughput capability. However, antibody reagents for a clinical grade immunoassay often only exist for a short list of candidates. The development of a reliable sandwich immunoassay for one target protein is expensive, has a long development time, and is dependent upon the generation of high quality protein antibodies. For the large majority of new, unproven candidate biomarkers, an intermediate verification technology is required that has shorter assay development time lines, lower assay cost, and effective multiplexing of dozens of candidates in low sample volumes. Ideally the approach should be capable of analyzing hundreds of samples of serum or plasma with good precision. The desired outcome of verification is a small number of highly credentialed candidates suitable for traditional preclinical and clinical validation studies.Multiple reaction monitoring (MRM)¹ coupled with stable isotope dilution (SID) MS has recently been shown to be well suited for direct quantification of proteins in plasma (2–4) and has emerged as the core technology for candidate biomarker verification. MRM assays can be highly multiplexed such that a moderate number of candidate proteins (in the range of 10–50) can be simultaneously targeted and measured in the statistically viable number of patient samples required for verification (hundreds of serum samples). However, sensitivity for unambiguous detection and quantification of proteins by MS-based assays is often constrained by sample complexity, particularly when the measurements are being made in complex fluids such as plasma.Many biomarkers of current clinical importance, such as prostate-specific antigen and the cardiac troponins, reside in the low nanogram/milliliter range in plasma and, until recently, have been inaccessible by non-antibody approaches. Our laboratory has recently shown for the first time that a combination of abundant protein depletion with limited fractionation at the peptide level prior to SID-MRM-MS provides robust limits of quantitation (LOQs) in the 1–20 ng/ml range with coefficient of variation (CV) of 10–20% at the LOQ for proteins in plasma (3).Here we demonstrate that this work flow can be extended to configure assays for a number of known markers of cardiovascular disease and, more importantly, can be deployed to measure their concentrations in clinical samples. We modeled a verification study comprising six patients undergoing alcohol septal ablation treatment for hypertrophic obstructive cardiomyopathy, a human model of “planned” myocardial infarction (PMI), and obtained targeted, quantitative measurements for moderate to low concentrations of cardiac biomarkers in plasma. This work provides additional evidence that MS-based assays can be configured and applied to verification of new protein targets for which high quality antibody reagents are not available.     

Microfluidic PDMS (polydimethylsiloxane) bioreactor for large-scale culture of hepatocytes

Microfluidics could provide suitable environments for cell culture because of the larger surface-to-volume ratio and fluidic behavior similar to the environments in vivo. Such microfluidic environments are now used to investigate cell-to-cell interactions and behaviors in vitro, emulating situations observed in vivo, for example, microscale blood vessels modeled by microfluidic channels. These emulated situations cannot be realized by conventional technologies. In our previous works, microfluidic channels composed of two PDMS (poly(dimethylsiloxane)) layers were successfully used for Hep G2 cell culture. To achieve physiologically meaningful functions in vitro, a culture with a larger number of cells and higher density must be performed. This will require bioreactors with larger surface areas for cell attachment and sufficient amounts of oxygen and nutrition supply. For those purposes, we fabricated a bioreactor by stacking 10 PDMS layers together, i.e., four cell culture chambers, and a chamber dedicated to the oxygen supply inserted in the middle of the 10-stacked layers. The oxygen supply chamber is separated from the microfluidic channels for the culture medium perfusion by thin 300-microm PDMS walls. The high gas permeability of PDMS allows oxygen supply to the microfluidic channels through the thin walls. On the basis of the measurement of glucose consumption and albumin production, it is shown that cellular activity exhibits a gradual increase and saturation throughout the culture. We clearly observed that in the case of the microfluidic bioreactor for large-scale cultures, the oxygen chamber is indispensable to achieve longer and healthy cultures. In the present bioreactor, the cell density was found to be about 3-4 x 10(7) cells/cm(3), which is in the same order of magnitude as the conventional macroscale bioreactors. Consequently, by stacking single culture chambers and oxygen chambers in between, we could have a scalable method to realize the microfluidic bioreactor for large-scale cultures.     

Flow sandwich-type immunoassay in microfluidic devices based on negative dielectrophoresis

Microparticles have been manipulated in a microfluidic channel by means of negative dielectrophoresis (n-DEP), and the approach applied to a heterogeneous immunoassay system. A microfluidic device, with three-dimensional (3-D) microelectrodes fabricated on two substrates, was used to manipulate particle flow in the channel and to capture the particles in the caged area that was enclosed by the collector electrodes. Polystyrene microparticles (6 microm diameters) modified with anti-mouse immunoglobulin G (IgG) were manipulated and captured in the caged area when surrounded by intense n-DEP electric fields. Specifically, particles were trapped when AC voltages with amplitudes of 6-15 V(peak) and frequencies over 500 kHz were applied to the two facing microelectrodes. A heterogeneous sandwich immunoassay was achieved by successively injecting a sample solution containing mouse antigen (IgG), and a solution containing a secondary antibody with a signal source (FITC-labeled anti-mouse IgG antibody), into the channel. The fluorescence intensity from captured particles in the caged area increased with increasing concentrations (10 ng/ml to 10 microg/ml) of mouse IgG. The described system enables mouse IgG to be assayed in 40 min. Thus, the automatic separation of free fractions from desired analytes and labeled antibodies can be achieved using a microfluidic device based on n-DEP.     

Demonstration of a homogeneous noncompetitive immunoassay based on bioluminescence resonance energy transfer

We describe a noncompetitive homogeneous bioluminescent immunoassay based on the antigen-dependent reassociation of antibody variable domains (open sandwich bioluminescent immunoassay, OS-BLIA). The reassociation of two chimeric proteins, an antibody heavy-chain fragment (V(H))-Renilla luciferase (Rluc) and an antibody light-chain fragment (V(L))-enhanced yellow fluorescent protein (EYFP), was monitored by a bioluminescence resonance energy transfer (BRET) between the two. Upon simple mixing of the reagents with the sample, an antigen-dependent increase in BRET was observed with a measurable concentration range of 0.1 to approximately 10 microg/ml antigen hen egg lysozyme. Compared with our comparable assays based on fluorescence resonance energy transfer (FRET), a 10-fold improvement in the sensitivity was attained, probably due to a reduction in reagent concentration.     

A chemiluminescence flow immunosensor based on a porous monolithic metacrylate and polyethylene composite disc modified with protein G

A generic, fast, sensitive and new type of flow immunosensor has been developed. The basis is a monolithic porous poly(glycidyl methacrylate-co-trimethylolpropane trimethacrylate) polymer disc modified with protein G, placed in a fountain type flow cell compartment, in close proximity to a photomultiplier tube (PMT). Analyte and HRP labelled analyte derivative (tracer) compete for anti-analyte antibody binding sites. The mixture is then injected into the flow immunosensor system where the formed analyte- and tracer-antibody complexes are trapped by the monolithic protein G disc. The amount of bound tracer, inversely related to the concentration of analyte in the sample, is determined in a second step by injection of luminol, p-iodophenol and H2O2, generating enhanced chemiluminescence (CL) with horseradish peroxidase (HRP). A third and final step is need for regeneration of the protein G disc so that a new analysis cycle can take place. The performance of the disc immunosensor system was compared with a one step continuous flow injection immunoassay (FIIA) system, using the same reagents and a protein G column, in terms of assay sensitivity and influence of matrix effects from various water samples (millipore-, tap- and surface water). The detection limit for the analyte atrazine in PBS and surface water (SW) was 0.208 +/- 0.004 microg l(-1) (PBS) and 0.59 +/- 0.120 microg l(-1) (SW) for the FIIA and 0.033 +/- 0.003 microg l(-1) (PBS) and 0.038+/-0.003 microg l(-1) (SW) for the disc immunosensor. Statistical comparison of the two systems shows that the disc immunosensor results were significantly less influenced by the sample matrix, which is explained by the fact that the sample in the FIIA arrives simultaneously with the matrix to the detector, whereas these are separated in time in the disc immunosensor system.     

Amplification of fluorescence with packed beads to enhance the sensitivity of miniaturized detection in microfluidic chip

This paper reports the pre-concentration of C-reactive protein (CRP) antigen with packed beads in a microfluidic chamber to enhance the sensitivity of the miniaturized fluorescence detection system for portable point-of-care testing devices. Although integrated optical systems in microfluidic chips have been demonstrated by many groups to replace bulky optical systems, the problem of low sensitivity is a hurdle for on-site clinical applications. Hence we integrated the pre-concentration module with miniaturized detection in microfluidic chips (MDMC) to improve analytical sensitivity. Cheap silicon-based photodiodes with optical filter were packaged in PDMS microfluidic chips and beads were packed by a frit structure for pre-concentration. The beads were coated with CRP antibodies to capture antigens and the concentrated antigens were eluted by an acid buffer. The pre-concentration amplified the fluorescence intensity by about 20-fold and the fluorescence signal was linearly proportional to the concentration of antigens. Then the CRP antigen was analyzed by competitive immunoassay with an MDMC. The experimental result demonstrated that the analytical sensitivity was enhanced up to 1.4 nM owing to the higher signal-to-noise ratio. The amplification of fluorescence by pre-concentration of bead-based immunoassay is expected to be one of the methods for portable fluorescence detection system.