WO2009047805A2 - Micro chip - Google Patents

Micro chip Download PDF

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Publication number
WO2009047805A2
WO2009047805A2 PCT/IN2008/000666 IN2008000666W WO2009047805A2 WO 2009047805 A2 WO2009047805 A2 WO 2009047805A2 IN 2008000666 W IN2008000666 W IN 2008000666W WO 2009047805 A2 WO2009047805 A2 WO 2009047805A2
Authority
WO
WIPO (PCT)
Prior art keywords
chip
micro
heater
reaction chamber
sample
Prior art date
Application number
PCT/IN2008/000666
Other languages
French (fr)
Other versions
WO2009047805A3 (en
Inventor
Kishore Krishna Kumar
Raviprakash Jayaraman
Sankaranand Kaipa Narasimha
Renjith Mahiladevi Radhakrishnan
Sathyadeep Viswanathan
Chandrasekhar Bhaskaran Nair
Pillarisetti Venkata Subbarao
Manjula Jagannath
Shilpa Chennakrishnaiah
Original Assignee
Bigtec Private Limited
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority to LTEP08838206.4T priority Critical patent/LT2212691T/en
Priority to CA2702418A priority patent/CA2702418C/en
Priority to ES08838206T priority patent/ES2714559T3/en
Priority to AP2010005240A priority patent/AP2930A/en
Priority to EP08838206.4A priority patent/EP2212691B1/en
Priority to DK08838206.4T priority patent/DK2212691T3/en
Priority to CN200880116740.4A priority patent/CN101868722B/en
Priority to NZ584592A priority patent/NZ584592A/en
Priority to PL08838206T priority patent/PL2212691T3/en
Priority to EA201070390A priority patent/EA027913B1/en
Priority to MX2010003978A priority patent/MX2010003978A/en
Priority to SI200832046T priority patent/SI2212691T1/en
Application filed by Bigtec Private Limited filed Critical Bigtec Private Limited
Priority to JP2010528533A priority patent/JP5226075B2/en
Priority to BRPI0816357-0A priority patent/BRPI0816357B1/en
Priority to AU2008310526A priority patent/AU2008310526B2/en
Priority to US12/682,581 priority patent/US9044754B2/en
Publication of WO2009047805A2 publication Critical patent/WO2009047805A2/en
Publication of WO2009047805A3 publication Critical patent/WO2009047805A3/en
Priority to IL204997A priority patent/IL204997A/en
Priority to ZA2010/02535A priority patent/ZA201002535B/en
Priority to TN2010000157A priority patent/TN2010000157A1/en
Priority to MA32809A priority patent/MA31803B1/en
Priority to HK11103632.5A priority patent/HK1149327A1/en
Priority to HRP20190418TT priority patent/HRP20190418T1/en
Priority to CY20191100260T priority patent/CY1121430T1/en

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Classifications

    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L7/00—Heating or cooling apparatus; Heat insulating devices
    • B01L7/52—Heating or cooling apparatus; Heat insulating devices with provision for submitting samples to a predetermined sequence of different temperatures, e.g. for treating nucleic acid samples
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2300/00—Additional constructional details
    • B01L2300/06—Auxiliary integrated devices, integrated components
    • B01L2300/0627—Sensor or part of a sensor is integrated
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2300/00—Additional constructional details
    • B01L2300/08—Geometry, shape and general structure
    • B01L2300/0848—Specific forms of parts of containers
    • B01L2300/0851—Bottom walls
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2300/00—Additional constructional details
    • B01L2300/08—Geometry, shape and general structure
    • B01L2300/0887—Laminated structure
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2300/00—Additional constructional details
    • B01L2300/16—Surface properties and coatings
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L2300/00—Additional constructional details
    • B01L2300/18—Means for temperature control
    • B01L2300/1805—Conductive heating, heat from thermostatted solids is conducted to receptacles, e.g. heating plates, blocks
    • B—PERFORMING OPERATIONS; TRANSPORTING
    • B01—PHYSICAL OR CHEMICAL PROCESSES OR APPARATUS IN GENERAL
    • B01L—CHEMICAL OR PHYSICAL LABORATORY APPARATUS FOR GENERAL USE
    • B01L3/00—Containers or dishes for laboratory use, e.g. laboratory glassware; Droppers
    • B01L3/50—Containers for the purpose of retaining a material to be analysed, e.g. test tubes
    • B01L3/502—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures
    • B01L3/5027—Containers for the purpose of retaining a material to be analysed, e.g. test tubes with fluid transport, e.g. in multi-compartment structures by integrated microfluidic structures, i.e. dimensions of channels and chambers are such that surface tension forces are important, e.g. lab-on-a-chip

Definitions

  • the disclosure is related to a micro PCR (Polymerase chain reaction) chip comprising a plurality of layers made of low temperature co-fired ceramics (LTCC).
  • LTCC low temperature co-fired ceramics
  • the disclosure also provides for a portable real-time PCR device with disposable LTCC micro PCR chip.
  • PCR is a molecular biology method for the in-vivo amplification of nuclear acid molecules.
  • the PCR technique is rapidly replacing other time consuming and less sensitive techniques for identification of biological species and pathogens in forensic, environmental, clinical and industrial samples.
  • biotechniques PCR has become the most important analytical step in life sciences laboratories for a large number of molecular and clinical diagnostics. Important developments made in PCR technology like real-time PCR, have led to rapid reaction processes compared to conventional methods.
  • An object of the present invention was to provide for a micro chip allowing faster PCR performance.
  • Another object of the present invention was to provide for an improved micro chip.
  • One of the main objects of the invention is to develop a micro chip comprising plurality of layers of LTCC.
  • Still another object of the instant invention is to develop a method of fabricating the micro chip.
  • Yet another object of the instant invention is to develop a micro PCR device comprising the micro chip.
  • Still another object of the present invention is to develop a method of diagnosing disease conditions using the micro-PCR device.
  • a micro chip comprising a plurality of layers made of low temperature co-fired ceramics (LTCC), wherein a reaction chamber is formed in a plurality of reaction chamber layers for loading a sample, a conductor is embedded iri at least one conductor layer placed below the reaction chamber and a heater is embedded in at least one heater layer placed below the conductor layer(s); a method of fabricating a micro chip comprising the steps: (a) arranging plurality of layers made of low temperature co-fired ceramics (LTCC) and having a well to form a reaction chamber, (b) placing at least one layer of LTCC comprising heater below the chamber, (c) placing one or several conductor layer(s) between the heater and the reaction chamber, and (d) interconnecting the layers to form the micro chip; a micro PCR device comprising: (a) a micro chip comprising plurality of layers of LTCC, wherein a reaction chamber is formed in a plurality of layers for loading sample, conductor is embedded in atl
  • Figure 1 shows an orthographic view of an embodiment of the LTCC micro PCR chip.
  • Figure 2 shows a cross-section of an embodiment of the LTCC micro PCR chip.
  • Figure 3 shows a layer-by-layer design of an embodiment of the LTCC micro PCR chip.
  • Figure 4 shows a block diagram of an embodiment of the circuit controlling the heater and thermistor.
  • Figure 5 shows a model of the chip reaction chamber design fabricated.
  • Figure 6 shows melting of lambda-636 DNA fragment on chip using the integrated heater/thermistor, controlled by the handheld unit.
  • Figure 7 shows PCR amplification of lambda-311 DNA fragment on chip, (a) Realtime fluorescence signal from the chip; (b) Image of the gel confirming the amplification product.
  • Figure 8 shows an image of a gel of processed blood and plasma PCR for 16S ribosomal unit of salmonella.
  • Figure 9 shows an image of a gel of direct blood PCR for 16S ribosomal unit of salmonella.
  • Figure 10 shows an image of a gel direct plasma PCR for 16S ribosomal unit of salmonella.
  • Figure 11 shows PCR amplification of gene of Salmonella using microchip, (a) Realtime fluorescence signal from the chip; (b) Image of the gel confirming the amplification product.
  • Figure 12 shows time taken for amplifying Hepatitis B Viral DNA using LTCC chip
  • Figure 13 shows melting curve of LTCC chip for derivative of the fluorescence signal for melting of ⁇ -31 1 DNA.
  • the present invention relates to a micro chip comprising a plurality of layers made of low temperature co-fired ceramics (LTCC), wherein a reaction chamber is formed in a plurality of reaction chamber layers for loading a sample, a conductor is embedded in at least one conductor layer placed below the reaction chamber and a heater is embedded in at least one heater layer placed below the conductor layer(s).
  • LTCC low temperature co-fired ceramics
  • the reaction chamber is covered with a transparent sealing cap.
  • the chip comprises a temperature sensor.
  • the temperature sensor is embedded in at least one sensor layer of the chip.
  • the temperature sensor is a thermistor.
  • the chip provide for contact pads to connect external control circuit to the temperature sensor and the heater.
  • the temperature sensor is placed outside the chip to measure the chip temperature.
  • the reaction chamber is surrounded with conductor rings.
  • the conductor rings are connected to the conductor layer(s) with posts.
  • the conductor is made of material selected from group comprising gold, silver, platinum and palladium or alloys thereof.
  • the sample is food or a biological sample selected from a group comprising blood, serum, plasma, tissues, saliva, sputum and urine.
  • the reaction chamber has a volume ranging from about 1 ⁇ l to about 25 ⁇ l.
  • the present invention also relate to a method of fabricating a micro chip comprising the steps: a) arranging plurality of layers made of low temperature co-fired ceramics (LTCC) and having a well to form a reaction chamber, b) placing at least one layer of LTCC comprising heater below the chamber, c) placing one or several conductor layer(s) between the heater and the reaction chamber, and d) interconnecting the layers to form the micro chip.
  • LTCC low temperature co-fired ceramics
  • the chamber is surrounded with conducting rings.
  • One embodiment of the present invention provides posts to connect the conducting rings to the conductor layer(s).
  • the present invention also relates to a micro PCR device comprising: a) a micro chip comprising plurality of layers of LTCC, wherein a reaction chamber is formed in a plurality of layers for loading sample, conductor is embedded in atleast one layer placed below the reaction chamber and heater is embedded in atleast one layer placed below the conductor layer(s); b) a temperature sensor embedded in the micro chip or placed outside the chip to measure the chip temperature, c) a control circuit to control the heater based on the temperature sensor input; and d) an optical system to detect fluorescence signal from the sample.
  • the device is a hand held device.
  • the device is controlled with a portable computing platform.
  • the device is arranged in an array to carry out multiple PCRs.
  • the micro chip is releasable from the device.
  • the present invention also relates to a method of detecting an analyte in a sample or diagnosing a disease condition using a micro-PCR device, the method comprising steps of: a) loading a sample comprising nucleic acid onto a micro chip comprising plurality of LTCC layers, b) amplifying the nucleic acid by running the micro-PCR device; and c) determining the presence or absence of the analyte based on a fluorescence reading of the amplified nucleic acid, or determining the presence or absence of a pathogen based on a fluorescence reading of the amplified nucleic acid to diagnose the disease condition.
  • the nucleic acid is either DNA or RNA.
  • the method provides for both qualitative and quantitative analysis of the amplified products.
  • the sample is food or biological sample.
  • the biological sample is selected from a group comprising blood, serum, plasma, tissues, saliva, sputum and urine.
  • the pathogen is selected from a group comprising viruses, bacteria, fungi, yeasts and protozoa.
  • reaction chamber layer in the disclosure refers to any layer of the micro chip involved in the formation of the reaction chamber and that comes into contact with a sample.
  • conductor layer in the disclosure refers to any layer of the micro chip having a conductor embedded in it.
  • cooler layer in the disclosure refers to any layer of the micro chip having a heater embedded in it.
  • PCR Polymerase Chain Reaction
  • Thermus aquaticus Taq
  • Thermus aquaticus can synthesize a complimentary strand to a given DNA strand in a mixture containing four DNA bases and two primer DNA fragments flanking the target sequence.
  • the mixture is heated to separate the strands of double helix DNA containing the target sequence and then cooled to allow the primers to find and bind to their complimentary sequences on the separate strands and the Taq polymerase to extend the primers into new complimentary strands. Repeated heating and cooling cycles multiply the target DNA exponentially, since each new double strand separates to become two templates for further synthesis.
  • a typical temperature profile for the polymerase chain reaction is as follows: 1. Denaturation at 93 0 C for 15 to 30 seconds 2. Annealing of Primer at 55 0 C for 15 to 30 seconds 3. Extending primers at 72 0 C for 30 to 60 seconds
  • the solution in the first step, is heated to 90-95 0 C so that the double stranded template melts ("denatures") to form two single strands.
  • it is cooled to 5O-55°C so that short specially synthesized DNA fragments ("primers”) bind to the appropriate complementary section of the template (“annealing”).
  • primers short specially synthesized DNA fragments
  • annealing the solution is heated to 72°C when a specific enzyme (“DNA polymerase”) extends the primers by binding complementary bases from the solution.
  • DNA polymerase a specific enzyme
  • the primer extension step has to be increased by roughly 60sec/kbase to generate products longer than a few hundred bases.
  • the above are typical instrument times; in fact, the denaturing and annealing steps occur almost instantly, but the temperature rates in commercial instruments usually are less than I 0 C /sec when metal blocks or water are used for thermal equilibration and samples are contained in plastic microcentrifuge tubes.
  • LTCC Low Temperature Co-fired Ceramics
  • LTCC Low Temperature Co-fired Ceramics
  • It is the modern version of thick film technology that is used in electronic component packaging for automotive, defense, aerospace and telecommunication industry. It is an alumina based glassy ceramic material that is chemically inert, bio-compatible, thermally stable (>600°C), has low thermal conductivity ( ⁇ 3W/mK), good mechanical strength and provides good hermiticity. It is conventionally used in packaging chip level electronic devices where in they serve both structural and electrical functions.
  • the present inventors have recognized the suitability of LTCC to be used for micro PCR chip applications, and, to the best knowledge of the inventors, LTCC has not been used before for such purpose.
  • the basic substrates in LTCC technology is preferably unfired (green) layers of glassy ceramic material with a polymeric binder. Structural features are formed by cutting/punching/drilling these layers and stacking multiple layers. Layer by layer process enables creating three-dimensional features essential for MEMS (Micro Electro Mechanical Systems). Features down to 50 microns can be readily fabricated on LTCC. Electrical circuits are fabricated by screen-printing conductive and resistive paste on each layer. Multiple layers are interconnected by punching vias and filling them with conducting paste. These layers are stacked, compressed and fired. Processing of stacks of up to 80 layers has been reported in the literature 1. The fired material is dense and has good mechanical strength.
  • PCR product is analyzed using gel electrophoresis.
  • DNA fragments after PCR are separated in an electric field and observed by staining with a fluorescent dye.
  • a more suitable scheme is to use a fluorescent dye that binds specifically to double strand DNA to monitor the reaction continuously (real-time PCR).
  • An example of such a dye is SYBR GREEN that is excited by 490nm blue light and emits 520nm green light when bound to DNA. The fluorescence intensity is proportional to the amount of double stranded product DNA formed during PCR and hence increases with cycle number.
  • Figure 1 shows an orthographic view of an embodiment of the micro PCR chip indicating reaction chamber (11) or well.
  • the figure indicates the assembly of the heater (12) and a temperature sensor thermistor (13) inside the LTCC Micro PCR chip.
  • the heater conductor lines (15) and the thermistor conductor lines (14) are also indicated. These conductor lines will help in providing connection to the heater and the thermistor embedded in the hip with external circuitry.
  • Figure 2 which shows a cross-sectional view of an embodiment of the LTCC micro PCR chip wherein (16a & 16b) indicate the contact pads for the heater (12) and (17a & 17b) indicate the contact pad for the thermistor (13)
  • FIG 3 which shows the layer-by-layer design of an embodiment of the LTCC micro PCR chip wherein the chip, consists of 12 layers of LTCC tapes.
  • the reaction chamber layers (36) consist of six layers as shown.
  • the conductor layer (33) is also provided between the heater and the thermistor layers.
  • the heater conductor line (33) and the thermistor conductor lines (32) are also indicated. In the figure shows the conductor lines (32) is placed in either side of the thermistor layer (34).
  • the heater design can be of any shape like “ladder”, “serpentine”, “line”, “plate”. Etc. with size varying from 0.2mm x 3mm to 2mm x 2mm.
  • the size and shape of the heater can be selected based on the requirements. The requirements could be like depending on the size of the reaction chamber or the sample been tested or the material been used as a conductor layer.
  • FIG 3 shows the layer wise design and an image of an embodiment of the packaged chip fabricated.
  • the LTCC chip has well volume of 1 to 25 ⁇ l and a resistance variation (heater and thermistor) of around 50%.
  • the resistance values of the heater ( ⁇ 40 ⁇ ) and thermistor (-1050 ⁇ ) were consistent with the estimated values.
  • the heater is based on thick film resistive element that is employed in conventional LTCC packages.
  • the thermistor system with alumina is used for fabrication of embedded temperature sensors.
  • the measured TCR of the chip was between 1 and 2 ⁇ /°C.
  • the chip was fabricated on DuPont 951 green system.
  • the thermistor layer can be placed any were in the chip or a temperature sensor can be placed outside the chip instead of thermistor inside the chip.
  • FIG 4 shows the block diagram of an embodiment of the circuit controlling the heater and thermistor wherein the thermistor in the LTCC Micro PCR Chip (10) acts as one of the arms in the bridge (46).
  • the amplified output of the bridge from the bridge amplifier (41) is given as input to the PID controller (43), where it is digitized and the PID algorithm provides a controlled digital output.
  • the output is again converted back to analog voltage and this drives the heater using a power transistor present in the heater driver (46).
  • it is cheaper to process LTCC when compared to silicon processing.
  • the invention also provides to improve the conventional PCR systems in analysis time, portability, sample volume and the ability to perform throughput analysis and quantification. This is achieved with a portable micro PCR device, with real-time in- situ detection / quantification of the PCR products which comprises the following:
  • Disposable PCR chip consisting of reaction chamber/s, embedded heater and a temperature sensor with a transparent sealing cap.
  • a handheld electronics unit consisting of the following units o Control circuit for the heater and the temperature sensor. o Fluorescence optical detection system.
  • a smart phone or PDA personal digital assistant running a program to control the said handheld unit.
  • the disposable PCR chip consists of a reaction chamber that is heated by an embedded heater and monitored by an embedded thermistor. It is fabricated on Low Temperature Cofired Ceramic (LTCC) system and packaged suitably with a connector with contacts for heater and temperature sensor.
  • LTCC Low Temperature Cofired Ceramic
  • the embedded heater is made of resistor paste like CF series from DuPont compatible to LTCC. Any green ceramic tape system can be used such as DuPont 95, ESL
  • the said embedded temperature sensor is a thermistor fabricated using a PTC (Positive Temperature Coefficient) resistance thermistor paste (E.g.: 509X D, are ESL 2612 from ESL Electroscience) for Alumina substrates.
  • PTC Positive Temperature Coefficient
  • NTC Negative Temperature Coefficient of resistance paste like NTC 4993 from EMCA Remex can also be used.
  • the transparent (300 to lOOOnm wavelength) sealing cap is to prevent evaporation of the sample from the said reaction chamber and is made of polymer material.
  • the control circuit would consist of an on/off or a PID (Proportional Integral Differential) control circuit, which would control the heater based on the output from a bridge circuit of which the embedded thermistor would form a part.
  • PID Proportional Integral Differential
  • the fluorescence optical detection system would comprise of an excitation source of a LED (Light Emitting Diode) and the fluorescence detected by a photodiode.
  • the system would house optical fibers which would be used to project the light on to the sample.
  • Optical fiber can also be used to channel light on to the photodiode.
  • the LED and the photodiode are coupled to optical fiber thought appropriate band pass filter. Accurate measurement of the output signal from the photodetector requires a circuit that has extremely good signal to noise ratio.
  • the fluorescence detection system disclosed here is only an example. This should not be considered as the only way to detect or the limitation. Any fluorescence detector would work unless it is not able to project itself on the sample.
  • the invention provides a marketable handheld PCR system for specific diagnostic application.
  • PDA has control software running to provide a complete handheld PCR system with real time detection and software control.
  • Figure 12 shows time taken for amplifying Hepatitis B Viral DNA using LTCC chip of instant invention.
  • the PCR was run for 45 cycles and were able to achieve amplification within 45 minutes. Further, the amplification was observed when the PCR was run for 45 cycles in 20 minutes and 15 minutes also. Conventional PCR duration for HBV (45 cycles) would take about 2 hours. Miniaturization allows accurate readings with smaller sample sizes and consumption of smaller volumes of costly reagents.
  • the Micro chip translated into a handheld device, thereby removes the PCR machine from a sophisticated laboratory, thus increasing the reach of this extremely powerful technique, be it for clinical diagnostics, food testing, blood screening at blood banks or a host of other application areas.
  • the analysis or quantification of the PCR products is realized by practical integration of a real-time fluorescence detection system. This system could also be integrated with quantification and sensing systems to detect diseases like Hepatitis B ( Figure 12), AIDS, tuberculosis, etc. Other markets include food monitoring, DNA analysis, forensic science and environmental monitoring.
  • Figure 5 shows the micro chip in 3 dimensional views showing its various connections with the heater, conductor rings, thermistor, and conducting rings (52). It also shows posts (51) that are connecting the conductor rings (52) to the conductor plate (33).
  • Figure 6 shows a comparative plot of the melting of ⁇ -636 DNA fragment on chip using the integrated heater and thermistor.
  • Figure 7 shows the increase in fluorescence signal associated with amplification of ⁇ - 311 DNA.
  • the thermal profile was controlled by the handheld unit and the reaction was performed on a chip (3 ⁇ l reaction mixture and 6 ⁇ l oil). The fluorescence was monitored using conventional lock-in amplifier.
  • Instant invention also provides for diagnostic system.
  • the procedure adopted for developing the diagnostic system has been to initially standardize thermal protocols for a couple of problems and then functionalize the same on the chip.
  • Figures 7 and 11 shows the gel picture of the amplified ⁇ -311 DNA and salmonella gene using micro-chip.
  • a unique buffer has been formulated for direct PCR with blood or plasma samples. Using this unique buffer system direct PCR amplification with blood & plasma has been achieved. With this buffer system, amplification has been obtained up to 50% for blood & 40% for plasma (see Figures 9 and 10) using LTCC chip of instant invention. In figure 9, gel electrophoresis image shows
  • the unique buffer comprises a buffer salt, a chloride or sulphate containing bivalent ion, a non-ionic detergent, a stabilizer and a sugar alcohol.
  • Figure 13 shows melting curve of LTCC chip for derivative of the fluorescence signal for melting of ⁇ -311 DNA.
  • the figure also provides a comparison between the instant invention (131) and the conventional PCR device (132).
  • Sharper peak: peak value/width (x axis) @ half peak value 1.2/43
  • Shallower peak: peak value/width (x axis) @ half peak value 0.7/63
  • Higher ratio indicates a sharper peak.
  • the y-axis is the derivative (slope of the melting curve), higher slope indicates sharper melting.

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Abstract

Instant invention is about a micro chip comprising plurality of layers of LTCC wherein a reaction chamber is formed in plurality of top layers to load samples. A heater embedded in atleast one of the layers below the reaction chamber and a temperature sensor is embedded in atleast one of the layers between the heater and the reaction chamber for analyzing the sample. The temperature sensor can be placed outside the chip to measure the chip temperature.

Description

MICRO CHIP
FIELD OF INVENTION
The disclosure is related to a micro PCR (Polymerase chain reaction) chip comprising a plurality of layers made of low temperature co-fired ceramics (LTCC). The disclosure also provides for a portable real-time PCR device with disposable LTCC micro PCR chip.
BACKGROUND OF THE INVENTION
Recent advances in molecular and cell biology have taken place as a result of the development of rapid and efficient analytical techniques. Due to miniaturization and multiplexing techniques like gene chip or biochip enable the characterization of complete genomes in a single experimental setup. PCR is a molecular biology method for the in-vivo amplification of nuclear acid molecules. The PCR technique is rapidly replacing other time consuming and less sensitive techniques for identification of biological species and pathogens in forensic, environmental, clinical and industrial samples. Among the biotechniques, PCR has become the most important analytical step in life sciences laboratories for a large number of molecular and clinical diagnostics. Important developments made in PCR technology like real-time PCR, have led to rapid reaction processes compared to conventional methods. During the past several years, microfabrication technology has been expanded to the miniaturization of the reaction and analysis system such as PCR analysis with the intention of further reducing analysis time and consumption of reagents. Several research groups have been working on the 'lab-on-a-chip' devices and have led to number of advances in the fields of miniaturized separation and reaction systems.
In most PCR's available now, instantaneous temperature changes are not possible because of sample, container, and cycler heat capacities, and extended amplification times of 2 to 6 hours result. During the periods when sample temperature is making a transition from one temperature to another, extraneous, undesirable reactions occur that consume important reagents and create unwanted interfering compounds. OBJECTS OF INVENTION
An object of the present invention was to provide for a micro chip allowing faster PCR performance.
Another object of the present invention was to provide for an improved micro chip.
One of the main objects of the invention is to develop a micro chip comprising plurality of layers of LTCC.
Still another object of the instant invention is to develop a method of fabricating the micro chip.
Yet another object of the instant invention is to develop a micro PCR device comprising the micro chip.
Still another object of the present invention is to develop a method of diagnosing disease conditions using the micro-PCR device.
STATEMENT OF INVENTION
Accordingly the invention provides for a micro chip comprising a plurality of layers made of low temperature co-fired ceramics (LTCC), wherein a reaction chamber is formed in a plurality of reaction chamber layers for loading a sample, a conductor is embedded iri at least one conductor layer placed below the reaction chamber and a heater is embedded in at least one heater layer placed below the conductor layer(s); a method of fabricating a micro chip comprising the steps: (a) arranging plurality of layers made of low temperature co-fired ceramics (LTCC) and having a well to form a reaction chamber, (b) placing at least one layer of LTCC comprising heater below the chamber, (c) placing one or several conductor layer(s) between the heater and the reaction chamber, and (d) interconnecting the layers to form the micro chip; a micro PCR device comprising: (a) a micro chip comprising plurality of layers of LTCC, wherein a reaction chamber is formed in a plurality of layers for loading sample, conductor is embedded in atleast one layer placed below the reaction chamber and heater is embedded in atleast one layer placed below the conductor layer(s); (b) a temperature sensor embedded in the micro chip or placed outside the chip to measure the chip temperature, (c) a control circuit to control the heater based on the temperature sensor input; and (d) an optical system to detect fluorescence signal from the sample; and a method of detecting an analyte in a sample or diagnosing a disease condition using a micro-PCR device, the method comprising steps of: (a) loading a sample comprising nucleic acid onto a micro chip comprising plurality of LTCC layers, (b) amplifying the nucleic acid by running the micro-PCR device; and (c) determining the presence or absence of the analyte based on a fluorescence reading of the amplified nucleic acid, or determining the presence or absence of a pathogen based on a fluorescence reading of the amplified nucleic acid to diagnose the disease condition.
BRIEF DESCRIPTION OF THE ACCOMPANYING DRAWINGS
The invention will now be described with reference to the accompanying drawings: Figure 1 shows an orthographic view of an embodiment of the LTCC micro PCR chip.
Figure 2 shows a cross-section of an embodiment of the LTCC micro PCR chip.
Figure 3 shows a layer-by-layer design of an embodiment of the LTCC micro PCR chip.
Figure 4 shows a block diagram of an embodiment of the circuit controlling the heater and thermistor.
Figure 5 shows a model of the chip reaction chamber design fabricated.
Figure 6 shows melting of lambda-636 DNA fragment on chip using the integrated heater/thermistor, controlled by the handheld unit.
Figure 7 shows PCR amplification of lambda-311 DNA fragment on chip, (a) Realtime fluorescence signal from the chip; (b) Image of the gel confirming the amplification product.
Figure 8 shows an image of a gel of processed blood and plasma PCR for 16S ribosomal unit of salmonella.
Figure 9 shows an image of a gel of direct blood PCR for 16S ribosomal unit of salmonella.
Figure 10 shows an image of a gel direct plasma PCR for 16S ribosomal unit of salmonella. Figure 11 shows PCR amplification of gene of Salmonella using microchip, (a) Realtime fluorescence signal from the chip; (b) Image of the gel confirming the amplification product.
Figure 12 shows time taken for amplifying Hepatitis B Viral DNA using LTCC chip Figure 13 shows melting curve of LTCC chip for derivative of the fluorescence signal for melting of λ-31 1 DNA.
DETAILED DESCRIPTION OF THE INVENTION
The present invention relates to a micro chip comprising a plurality of layers made of low temperature co-fired ceramics (LTCC), wherein a reaction chamber is formed in a plurality of reaction chamber layers for loading a sample, a conductor is embedded in at least one conductor layer placed below the reaction chamber and a heater is embedded in at least one heater layer placed below the conductor layer(s).
In one embodiment of the present invention, the reaction chamber is covered with a transparent sealing cap.
In one embodiment of the present invention, the chip comprises a temperature sensor.
In one embodiment of the present invention, the temperature sensor is embedded in at least one sensor layer of the chip.
In one embodiment of the present invention, the temperature sensor is a thermistor.
In one embodiment of the present invention, the chip provide for contact pads to connect external control circuit to the temperature sensor and the heater.
In one embodiment of the present invention, the temperature sensor is placed outside the chip to measure the chip temperature.
In one embodiment of the present invention, the reaction chamber is surrounded with conductor rings.
In one embodiment of the present invention, the conductor rings are connected to the conductor layer(s) with posts. In one embodiment of the present invention, the conductor is made of material selected from group comprising gold, silver, platinum and palladium or alloys thereof.
In one embodiment of the present invention, there is a gap between the reaction chamber base and the heater, and said gap is ranging from about 0.2mm to about 0.7mm.
In one embodiment of the present invention, the sample is food or a biological sample selected from a group comprising blood, serum, plasma, tissues, saliva, sputum and urine.
In one embodiment of the present invention, the reaction chamber has a volume ranging from about 1 μl to about 25 μl.
The present invention also relate to a method of fabricating a micro chip comprising the steps: a) arranging plurality of layers made of low temperature co-fired ceramics (LTCC) and having a well to form a reaction chamber, b) placing at least one layer of LTCC comprising heater below the chamber, c) placing one or several conductor layer(s) between the heater and the reaction chamber, and d) interconnecting the layers to form the micro chip.
In one embodiment of the present invention, wherein placing at least one layer of LTCC comprising a temperature sensor between the heater and the reaction chamber or below the heater.
In one embodiment of the present invention, the chamber is surrounded with conducting rings.
One embodiment of the present invention provides posts to connect the conducting rings to the conductor layer(s).
The present invention also relates to a micro PCR device comprising: a) a micro chip comprising plurality of layers of LTCC, wherein a reaction chamber is formed in a plurality of layers for loading sample, conductor is embedded in atleast one layer placed below the reaction chamber and heater is embedded in atleast one layer placed below the conductor layer(s); b) a temperature sensor embedded in the micro chip or placed outside the chip to measure the chip temperature, c) a control circuit to control the heater based on the temperature sensor input; and d) an optical system to detect fluorescence signal from the sample.
In one embodiment of the present invention, the device is a hand held device.
In one embodiment of the present invention, the device is controlled with a portable computing platform.
In one embodiment of the present invention, the device is arranged in an array to carry out multiple PCRs.
In one embodiment of the present invention, the micro chip is releasable from the device.
The present invention also relates to a method of detecting an analyte in a sample or diagnosing a disease condition using a micro-PCR device, the method comprising steps of: a) loading a sample comprising nucleic acid onto a micro chip comprising plurality of LTCC layers, b) amplifying the nucleic acid by running the micro-PCR device; and c) determining the presence or absence of the analyte based on a fluorescence reading of the amplified nucleic acid, or determining the presence or absence of a pathogen based on a fluorescence reading of the amplified nucleic acid to diagnose the disease condition.
In one embodiment of the present invention, the nucleic acid is either DNA or RNA. In one embodiment of the present invention, the method provides for both qualitative and quantitative analysis of the amplified products.
In one embodiment of the present invention, the sample is food or biological sample.
In one embodiment of the present invention, the biological sample is selected from a group comprising blood, serum, plasma, tissues, saliva, sputum and urine.
In one embodiment of the present invention, the pathogen is selected from a group comprising viruses, bacteria, fungi, yeasts and protozoa.
The term "reaction chamber layer" in the disclosure refers to any layer of the micro chip involved in the formation of the reaction chamber and that comes into contact with a sample.
The term "conductor layer" in the disclosure refers to any layer of the micro chip having a conductor embedded in it.
The term "heater layer" in the disclosure refers to any layer of the micro chip having a heater embedded in it.
The Polymerase Chain Reaction (PCR) is a technique discovered to synthesize multiple copies of a specific fragment of DNA from a template. The original PCR process is based on heat stable DNA polymerase enzyme from Thermus aquaticus (Taq), which can synthesize a complimentary strand to a given DNA strand in a mixture containing four DNA bases and two primer DNA fragments flanking the target sequence. The mixture is heated to separate the strands of double helix DNA containing the target sequence and then cooled to allow the primers to find and bind to their complimentary sequences on the separate strands and the Taq polymerase to extend the primers into new complimentary strands. Repeated heating and cooling cycles multiply the target DNA exponentially, since each new double strand separates to become two templates for further synthesis.
A typical temperature profile for the polymerase chain reaction is as follows: 1. Denaturation at 930C for 15 to 30 seconds 2. Annealing of Primer at 550C for 15 to 30 seconds 3. Extending primers at 720C for 30 to 60 seconds
As an example, in the first step, the solution is heated to 90-950C so that the double stranded template melts ("denatures") to form two single strands. In the next step, it is cooled to 5O-55°C so that short specially synthesized DNA fragments ("primers") bind to the appropriate complementary section of the template ("annealing"). Finally the solution is heated to 72°C when a specific enzyme ("DNA polymerase") extends the primers by binding complementary bases from the solution. Thus two identical double strands are synthesized from a single double strand.
The primer extension step has to be increased by roughly 60sec/kbase to generate products longer than a few hundred bases. The above are typical instrument times; in fact, the denaturing and annealing steps occur almost instantly, but the temperature rates in commercial instruments usually are less than I0C /sec when metal blocks or water are used for thermal equilibration and samples are contained in plastic microcentrifuge tubes.
By micromachining thermally isolated, low mass PCR chambers; it is possible to mass- produce a much faster, more energy efficient and a more specific PCR instrument. Moreover, rapid transitions from one temperature to another ensure that the sample spends a minimum amount of time at undesirable intermediate temperatures so that the amplified DNA has optimum fidelity and purity.
Low Temperature Co-fired Ceramics (LTCC) is the modern version of thick film technology that is used in electronic component packaging for automotive, defense, aerospace and telecommunication industry. It is an alumina based glassy ceramic material that is chemically inert, bio-compatible, thermally stable (>600°C), has low thermal conductivity (<3W/mK), good mechanical strength and provides good hermiticity. It is conventionally used in packaging chip level electronic devices where in they serve both structural and electrical functions. The present inventors have recognized the suitability of LTCC to be used for micro PCR chip applications, and, to the best knowledge of the inventors, LTCC has not been used before for such purpose. The basic substrates in LTCC technology is preferably unfired (green) layers of glassy ceramic material with a polymeric binder. Structural features are formed by cutting/punching/drilling these layers and stacking multiple layers. Layer by layer process enables creating three-dimensional features essential for MEMS (Micro Electro Mechanical Systems). Features down to 50 microns can be readily fabricated on LTCC. Electrical circuits are fabricated by screen-printing conductive and resistive paste on each layer. Multiple layers are interconnected by punching vias and filling them with conducting paste. These layers are stacked, compressed and fired. Processing of stacks of up to 80 layers has been reported in the literature 1. The fired material is dense and has good mechanical strength.
Typically the PCR product is analyzed using gel electrophoresis. In this technique, DNA fragments after PCR are separated in an electric field and observed by staining with a fluorescent dye. A more suitable scheme is to use a fluorescent dye that binds specifically to double strand DNA to monitor the reaction continuously (real-time PCR). An example of such a dye is SYBR GREEN that is excited by 490nm blue light and emits 520nm green light when bound to DNA. The fluorescence intensity is proportional to the amount of double stranded product DNA formed during PCR and hence increases with cycle number.
Figure 1 shows an orthographic view of an embodiment of the micro PCR chip indicating reaction chamber (11) or well. The figure indicates the assembly of the heater (12) and a temperature sensor thermistor (13) inside the LTCC Micro PCR chip. The heater conductor lines (15) and the thermistor conductor lines (14) are also indicated. These conductor lines will help in providing connection to the heater and the thermistor embedded in the hip with external circuitry. Referring to Figure 2 which shows a cross-sectional view of an embodiment of the LTCC micro PCR chip wherein (16a & 16b) indicate the contact pads for the heater (12) and (17a & 17b) indicate the contact pad for the thermistor (13)
Referring to Figure 3, which shows the layer-by-layer design of an embodiment of the LTCC micro PCR chip wherein the chip, consists of 12 layers of LTCC tapes. There are two base layers (31), three mid layers having the heater layer (32), a conductor layer (33) and a layer having thermistor (34) whereas (35) forms the interface layer to the reaction chamber (11). The reaction chamber layers (36) consist of six layers as shown. The conductor layer (33) is also provided between the heater and the thermistor layers. The heater conductor line (33) and the thermistor conductor lines (32) are also indicated. In the figure shows the conductor lines (32) is placed in either side of the thermistor layer (34). The heater design can be of any shape like "ladder", "serpentine", "line", "plate". Etc. with size varying from 0.2mm x 3mm to 2mm x 2mm. The size and shape of the heater can be selected based on the requirements. The requirements could be like depending on the size of the reaction chamber or the sample been tested or the material been used as a conductor layer.
Figure 3 shows the layer wise design and an image of an embodiment of the packaged chip fabricated. The LTCC chip has well volume of 1 to 25 μl and a resistance variation (heater and thermistor) of around 50%. The resistance values of the heater (~40 Ω) and thermistor (-1050 Ω) were consistent with the estimated values. The heater is based on thick film resistive element that is employed in conventional LTCC packages. The thermistor system with alumina is used for fabrication of embedded temperature sensors. The measured TCR of the chip was between 1 and 2 Ω/°C. The chip was fabricated on DuPont 951 green system. The thermistor layer can be placed any were in the chip or a temperature sensor can be placed outside the chip instead of thermistor inside the chip.
Referring to Figure 4, which shows the block diagram of an embodiment of the circuit controlling the heater and thermistor wherein the thermistor in the LTCC Micro PCR Chip (10) acts as one of the arms in the bridge (46). The amplified output of the bridge from the bridge amplifier (41) is given as input to the PID controller (43), where it is digitized and the PID algorithm provides a controlled digital output. The output is again converted back to analog voltage and this drives the heater using a power transistor present in the heater driver (46). In addition, it is cheaper to process LTCC when compared to silicon processing.
The invention also provides to improve the conventional PCR systems in analysis time, portability, sample volume and the ability to perform throughput analysis and quantification. This is achieved with a portable micro PCR device, with real-time in- situ detection / quantification of the PCR products which comprises the following:
■ Disposable PCR chip consisting of reaction chamber/s, embedded heater and a temperature sensor with a transparent sealing cap.
■ A handheld electronics unit consisting of the following units o Control circuit for the heater and the temperature sensor. o Fluorescence optical detection system.
■ A smart phone or PDA (personal digital assistant) running a program to control the said handheld unit.
The disposable PCR chip consists of a reaction chamber that is heated by an embedded heater and monitored by an embedded thermistor. It is fabricated on Low Temperature Cofired Ceramic (LTCC) system and packaged suitably with a connector with contacts for heater and temperature sensor.
The embedded heater is made of resistor paste like CF series from DuPont compatible to LTCC. Any green ceramic tape system can be used such as DuPont 95, ESL
(41XXX series), Ferro (A6 system) or Haraeus. The said embedded temperature sensor is a thermistor fabricated using a PTC (Positive Temperature Coefficient) resistance thermistor paste (E.g.: 509X D, are ESL 2612 from ESL Electroscience) for Alumina substrates. NTC: Negative Temperature Coefficient of resistance paste like NTC 4993 from EMCA Remex can also be used.
The transparent (300 to lOOOnm wavelength) sealing cap is to prevent evaporation of the sample from the said reaction chamber and is made of polymer material. The control circuit would consist of an on/off or a PID (Proportional Integral Differential) control circuit, which would control the heater based on the output from a bridge circuit of which the embedded thermistor would form a part. The method of controlling the heater and reading the thermistor value disclosed here is only an example. This should not be considered as the only way to controller or the limitation. Other means and method to control the heater and reading the thermistor value is well applicable to the instant discloser.
The fluorescence optical detection system would comprise of an excitation source of a LED (Light Emitting Diode) and the fluorescence detected by a photodiode. The system would house optical fibers which would be used to project the light on to the sample. Optical fiber can also be used to channel light on to the photodiode. The LED and the photodiode are coupled to optical fiber thought appropriate band pass filter. Accurate measurement of the output signal from the photodetector requires a circuit that has extremely good signal to noise ratio. The fluorescence detection system disclosed here is only an example. This should not be considered as the only way to detect or the limitation. Any fluorescence detector would work unless it is not able to project itself on the sample.
The invention provides a marketable handheld PCR system for specific diagnostic application. PDA has control software running to provide a complete handheld PCR system with real time detection and software control.
By reducing thermal mass and improved heating /cooling rates using the device, the time taken from 2 to 3 hours to finish a 30 to 40-cycle reaction, even for a moderate sample volume of 5-25 μl, was reduced to less than 30 minutes. Figure 12 shows time taken for amplifying Hepatitis B Viral DNA using LTCC chip of instant invention. The PCR was run for 45 cycles and were able to achieve amplification within 45 minutes. Further, the amplification was observed when the PCR was run for 45 cycles in 20 minutes and 15 minutes also. Conventional PCR duration for HBV (45 cycles) would take about 2 hours. Miniaturization allows accurate readings with smaller sample sizes and consumption of smaller volumes of costly reagents. The small thermal masses of Microsystems and the small sample sizes allows rapid low-power thermal cycling increasing the speed of many processes such as DNA replication through micro PCR. In addition, chemical processes that depend on surface chemistry are greatly enhanced by the increased surface to volume ratios available on the micro-scale. The advantages of micro fluidics have prompted calls for the development of integrated microsystem for chemical analysis.
The Micro chip translated into a handheld device, thereby removes the PCR machine from a sophisticated laboratory, thus increasing the reach of this extremely powerful technique, be it for clinical diagnostics, food testing, blood screening at blood banks or a host of other application areas.
Existing PCR instruments with multiple reaction chambers provide multiple DNA experiment sites all running the same thermal protocol and hence are not time efficient. The need arises, to minimize reaction time and intake sample volume.
Instant PCR is designed in future, could have an array of devices with very quick thermal response and highly isolated from the adjacent PCR chips to be able to effectively and independently run multiple reactions with different thermal protocols with minimum cross talk.
The analysis or quantification of the PCR products is realized by practical integration of a real-time fluorescence detection system. This system could also be integrated with quantification and sensing systems to detect diseases like Hepatitis B (Figure 12), AIDS, tuberculosis, etc. Other markets include food monitoring, DNA analysis, forensic science and environmental monitoring.
After determining the uniformity of the temperature profile with in the chip, PCR reactions were carried out on these chips. Lambda DNA fragments and salmonella DNA has been successfully amplified using these chips. Figure 5 shows the micro chip in 3 dimensional views showing its various connections with the heater, conductor rings, thermistor, and conducting rings (52). It also shows posts (51) that are connecting the conductor rings (52) to the conductor plate (33).
Figure 6 shows a comparative plot of the melting of λ-636 DNA fragment on chip using the integrated heater and thermistor.
Figure 7 shows the increase in fluorescence signal associated with amplification of λ- 311 DNA. The thermal profile was controlled by the handheld unit and the reaction was performed on a chip (3μl reaction mixture and 6μl oil). The fluorescence was monitored using conventional lock-in amplifier.
Instant invention also provides for diagnostic system. The procedure adopted for developing the diagnostic system has been to initially standardize thermal protocols for a couple of problems and then functionalize the same on the chip. Primers designed for 16S ribosomal DNA amplified ~ 300 - 400 bp fragment from E. coli and Salmonella while the primers for the stn gene amplified ~ 200 bp fragment from Salmonella typhi.
The products obtained were confirmed by SYBR green fluorescence detection as well as agarose gel electrophoresis. Figures 7 and 11 shows the gel picture of the amplified λ-311 DNA and salmonella gene using micro-chip.
Thermal profile for amplification of λ-311 DNA:
Denaturation: 94°C (90s)
940C (30s) - 500C (30s) - 72°C (45s)
Extension: 72°C (120s)
Thermal profile for amplification of Salmonella gene:
Denaturation: 94°C (90s)
94°C (30s) - 55°C (30s) - 72°C (30s)
Extension: 72°C (300s)
PCR with processed blood and plasma
Blood or plasma were treated with a precipitating agent that can precipitate the major
PCR inhibitory substances from these samples. The clear supernatant was used as a template. Using this protocol amplifications were obtained for ~ 200 bp fragment from Salmonella typhi (figure 8). In figure 8, gel electrophoresis image shows
1. control reaction,
2. PCR product- blood without processing, 3. PCR product- processed blood
4. PCR product- processed plasma
Blood direct PCR buffer
A unique buffer has been formulated for direct PCR with blood or plasma samples. Using this unique buffer system direct PCR amplification with blood & plasma has been achieved. With this buffer system, amplification has been obtained up to 50% for blood & 40% for plasma (see Figures 9 and 10) using LTCC chip of instant invention. In figure 9, gel electrophoresis image shows
1. PCR product- 20% blood,
2. PCR product- 30% blood, 3. PCR product- 40% blood,
4. PCR product- 50% blood; and in figure 10, gel electrophoresis image shows,
1. PCR product- 20% plasma,
2. PCR product- 30% plasma, 3. PCR product- 40% plasma,
4. PCR product- 50% plasma,
5. control reaction
The unique buffer comprises a buffer salt, a chloride or sulphate containing bivalent ion, a non-ionic detergent, a stabilizer and a sugar alcohol.
Figure 13 shows melting curve of LTCC chip for derivative of the fluorescence signal for melting of λ-311 DNA. The figure also provides a comparison between the instant invention (131) and the conventional PCR device (132). Sharper peak: peak value/width (x axis) @ half peak value = 1.2/43 Shallower peak: peak value/width (x axis) @ half peak value = 0.7/63 Higher ratio indicates a sharper peak. Also in the graph, the y-axis is the derivative (slope of the melting curve), higher slope indicates sharper melting.

Claims

We claim:
1. A micro chip comprising a plurality of layers made of low temperature co-fired ceramics (LTCC), wherein a reaction chamber is formed in a plurality of reaction chamber layers for loading a sample, a conductor is embedded in at least one conductor layer placed below the reaction chamber and a heater is embedded in at least one heater layer placed below the conductor layer(s).
2. The micro chip as claimed in claim 1, wherein the reaction chamber is covered with a transparent sealing cap.
3. The micro chip as claimed in claim 1, wherein the chip comprises a temperature sensor.
4. The micro chip as claimed in claim 3, wherein the temperature sensor is embedded in at least one sensor layer of the chip.
5. The micro chip as claimed in claim 4, wherein the temperature sensor is a thermistor.
6. The micro chip as claimed in claims 1 and 4, wherein the chip provide for contact pads to connect external control circuit to the temperature sensor and the heater.
7. The micro chip as claimed in claim 3, wherein the temperature sensor is placed outside the chip to measure the chip temperature.
8. The micro chip as claimed in claim 1, wherein the reaction chamber is surrounded with conductor rings.
9. The micro chip as claimed in claims 1 and 8, wherein the conductor rings are connected to the conductor layer(s) with posts.
10. The micro chip as claimed in claims 1, 8 and 9, wherein the conductor is made of material selected from group comprising gold, silver, platinum and palladium or alloys thereof.
11. The micro chip as claimed in claim 1, wherein there is a gap between the reaction chamber base and the heater, and said gap is ranging from about 0.2mm to about 0.7mm.
12. The micro chip as claimed in claim 1, wherein the sample is food or a biological sample selected from a group comprising blood, serum, plasma, tissues, saliva, sputum and urine.
13. The micro chip as claimed in claim 1, wherein the reaction chamber has a volume ranging from about 1 μl to about 25 μl.
14. A method of fabricating a micro chip comprising the steps: a) arranging plurality of layers made of low temperature co-fired ceramics (LTCC) and having a well to form a reaction chamber, b) placing at least one layer of LTCC comprising heater below the chamber, c) placing one or several conductor layer(s) between the heater and the reaction chamber, and d) interconnecting the layers to form the micro chip.
15. The method as claimed in claim 14, wherein placing at least one layer of LTCC comprising a temperature sensor between the heater and the reaction chamber or below the heater.
16. The method as claimed in claim 14, wherein the chamber is surrounded with conducting rings.
17. The method as claimed in claims 14 and 16, wherein providing posts to connect the conducting rings to the conductor layer(s).
18. A micro PCR device comprising: a) a micro chip comprising plurality of layers of LTCC, wherein a reaction chamber is formed in a plurality of layers for loading sample, conductor is embedded in atleast one layer placed below the reaction chamber and heater is embedded in atleast one layer placed below the conductor layer(s); b) a temperature sensor embedded in the micro chip or placed outside the chip to measure the chip temperature, c) a control circuit to control the heater based on the temperature sensor input; and d) an optical system to detect fluorescence signal from the sample.
19. The micro PCR device as claimed in claim 18, wherein the device is a hand held device.
20. The micro PCR device as claimed in claim 18, wherein the device is controlled with a portable computing platform.
21. The micro PCR device as claimed in claim 18, wherein the device is arranged in an array to carry out multiple PCRs.
22. The micro PCR device as claimed in claim 18, wherein the micro chip is releasable from the device.
23. A method of detecting an analyte in a sample or diagnosing a disease condition using a micro-PCR device, the method comprising steps of: a) loading a sample comprising nucleic acid onto a micro chip comprising plurality of LTCC layers amplifying the nucleic acid by running the micro-PCR device; and b) determining the presence or absence of the analyte based on a fluorescence reading of the amplified nucleic acid, or determining the presence or absence of a pathogen based on a fluorescence reading of the amplified nucleic acid to diagnose the disease condition.
24. The method as claimed in claim 23, wherein the nucleic acid is either DNA or RNA.
25. The method as claimed in claim 23, wherein the method provides for both qualitative and quantitative analysis of the amplified products.
26. The method as claimed in claim 23, wherein the sample is food or biological sample.
27. The method as claimed in claim 24, wherein the biological sample is selected from a group comprising blood, serum, plasma, tissues, saliva, sputum and urine.
28. The method as claimed in claim 23, wherein the pathogen is selected from a group comprising viruses, bacteria, fungi, yeasts and protozoa.
PCT/IN2008/000666 2007-10-12 2008-10-13 Micro chip WO2009047805A2 (en)

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IL204997A IL204997A (en) 2007-10-12 2010-04-11 Micro chip made of low temperature co-fired ceramics layers, methods of fabricating the same and uses thereof
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