Polymerase chain reaction (pcr) module and multiple pcr system using the same

BACKGROUND OF THE INVENTION

1. Field of the Invention

0001The present invention relates to a DNA polymerase chain reaction (hereinafter, simply referred to as PCR) module and a multiple PCR system using the same. More particularly, the present invention relates to a DNA PCR module with a combined PCR thermal cycler and PCR product detector, and a multiple PCR system using the same.

2. Description of the Related Art

0002The science of genetic engineering originated with the discovery of restriction enzymes. Similarly, PCR technology led to an explosive development in the field of biotechnology, and thus, it may be said that the PCR technology is a contributor to the golden age of biotechnology. PCR is a technology to amplify DNA copies of specific DNA or RNA fragments in a reaction chamber. Due to a very simple principle and easy applications, the PCR technology has been extensively used in medicine, science, agriculture, veterinary medicine, food science, and environmental science, in addition to pure molecular biology, and its applications are now being extended to archeology and anthropology.

0003PCR is performed by repeated cycles of three steps: denaturation, annealing, and extension. In the denaturation step, a double-stranded DNA is separated into two single strands by heating at 90°C or more. In the annealing step, two primers are each bound to the complementary opposite strands at an annealing temperature of 55 to 60°C for 30 seconds to several minutes. In the extension step, primer extension occurs by DNA polymerase. The time required for the primer extension varies depending on the density of template DNA, the size of an amplification fragment, and an extension temperature. In the case of using Thermusaquaticus (Taq) polymerase, which is commonly used, the primer extension is performed at 72°C for 30 seconds to several minutes.

0004Generally, PCR products are separated on a gel and the approximate amount of the PCR products is estimated. However, faster and more accurate quantification of PCR products is increasingly needed. Actually, an accurate measurement of the amount of target samples in gene expression (RNA) analysis, gene copy assay (quantification of human HER2 gene in breast cancer or HIV virus burden), genotyping (knockout mouse analysis), immuno-PCR, etc. is very important.

0005However, conventional PCR is end-point PCR for qualitative assay of amplified DNA by gel electrophoresis, which causes many problems such as inaccurate detection of the amount of DNA. To overcome the problems of the conventional end-point PCR, a quantitative competitive (QC) PCR method was developed. The QC-PCR is based on co-amplification in the same conditions of a target and a defined amount of a competitor having similar characteristics to the target. The starting amount of the target is calculated based on the ratio of a target product to a competitor product after the co-amplification. However, the QC-PCR is very complicated in that the most suitable competitor for each PCR must be designed, and multiple experiments at various concentrations for adjusting the optimal ratio range (at least a range of 1:10 to 10:1, 1:1 is an optimal ratio) of the target to the competitor must be carried out. The success probability for accurate quantification is also low.

0006In view of these problems of the conventional PCR methods, there has been introduced a real-time PCR method in which each PCR cycle is monitored to measure PCR products during the exponential phase of PCR. At the same time, there has been developed a fluorescence detection method for quickly measuring PCR products accumulated in a tube at each PCR cycle, instead of separation on a gel. UV light analysis of ethidium bromide-containing target molecules at each cycle and detection of fluorescence with a CCD camera were first reported by Higuchi et al. in 1992. Therefore, an amplification plot showing fluorescent intensities versus cycle numbers can be obtained.

0007However, in a conventional real-time PCR system, all wells or chips must be set to the same temperature conditions due to use of metal blocks such as peltier elements. Even though it may be advantageous to carry out repeated experiments using a large amount of samples at the same conditions, there are limitations on performing PCR using different samples at different temperature conditions. Also, since metal blocks such as peltier elements are used for temperature maintenance and variation, a temperature transition rate is as low as 1-3°C/sec, and thus, a considerable time for temperature transition is required, which increases the duration of PCR to more than 2 hours. In addition, the temperature accuracy of ±0.5°C limits fast and accurate temperature adjustment, which reduces the sensitivity and specificity of PCR.

SUMMARY OF THE INVENTION

0008The present invention provides a PCR module in which co-amplification of different samples at different temperature conditions can be carried out and monitored in real time.

0009The present invention also provides a multiple PCR system using the PCR module.

0010The present invention also provides a real-time PCR monitoring method using the PCR module or the multiple PCR system.

0011According to an aspect of the present invention, there is provided a PCR module including: a heater electrically connected to a temperature sensor; a PCR tube thermally contacting with the heater and comprising a PCR chamber containing a PCR solution; and a detection unit detecting a PCR product signal.

0012According to another aspect of the present invention, there is provided a multiple PCR system including: the PCR module; and a host computer controlling the PCR module, wherein the PCR module and the host computer are electrically connected through a wire or wireless mode.

0013According to still another aspect of the present invention, there is provided a multiple PCR system including: the PCR module; and a host computer controlling the PCR module, wherein the PCR module includes a computing unit and the computing unit of the PCR module and the host computer are electrically connected through a wire or wireless network.

0014According to still another aspect of the present invention, there is provided a real-time PCR monitoring method including: (a) loading a PCR solution in a PCR chamber of a PCR tube received in each of one or more PCR modules; (b) performing PCR independently in the PCR chamber of the PCR tube of each PCR module having an independently determined temperature condition; (c) detecting a PCR product signal based on PCR performed in each PCR module; and (d) displaying data about the PCR product signal of each PCR module.

BRIEF DESCRIPTION OF THE DRAWINGS

0015The above and other features and advantages of the present invention will become more apparent by describing in detail exemplary embodiments thereof with reference to the attached drawings in which: <ul id="ul0001" list-style="none" compact="compact"><li>FIG. 1A is a schematic block diagram of a DNA PCR module according to the present invention;</li><li>FIG. 1B is a schematic block diagram of a PCR module including a computing unit according to the present invention;</li><li>FIG. 2 is a schematic block diagram of a multiple PCR system including a host computer according to the present invention;</li><li>FIG. 3 is a schematic block diagram of a multiple PCR system including a host computer and a PCR module according to the present invention;</li><li>FIG. 4 is a schematic perspective view of a multiple PCR system according to an embodiment of the present invention;</li><li>FIG. 5 is a plan view of a microchip-type PCR tube installed in a multiple PCR system when a detection unit of FIG. 1 includes an optical source;</li><li>FIG. 6 is a sectional view taken along line V-V of FIG. 5;</li><li>FIG. 7 is a plan view of a microchip-type PCR tube when a detection unit of FIG. 1 includes an alternating power element for impedance measurement;</li><li>FIG. 8 is a rear view of a heater provided with a temperature sensor of FIG. 6;</li><li>FIG. 9 illustrates an electrophoretic result on a 2% TAE agarose gel after two-stage PCR in a microchip-type PCR tube;</li><li>FIG. 10A is a comparative view that illustrates the duration of PCR required for obtaining almost the same DNA concentration in the present invention and a conventional technology;</li><li>FIG. 10B is an enlarged view that illustrates only the DNA concentration of FIG. 10A;</li><li>FIG. 11A is a graph that illustrates a temperature profile of a conventional PCR system;</li><li>FIG. 11B is a graph that illustrates a temperature profile of a real-time PCR monitoring apparatus according to the present invention;</li><li>FIG. 12A is a view that illustrates real-time impedance values;</li><li>FIG. 12B is a graph that illustrates impedance values during extension versus the number of PCR cycles;</li><li>FIG. 13A is a view that illustrates real-time temperature profiles displayed on a screen of a real-time PCR monitoring apparatus according to the present invention;</li><li>FIG. 13B is a view that illustrates real-time S-curves displayed on a screen of a real-time PCR monitoring apparatus according to the present invention; and</li><li>FIG. 13C is a view that illustrates real-time melting curves displayed on a screen of a real-time PCR monitoring apparatus according to the present invention.</li></ul>

DETAILED DESCRIPTION OF THE INVENTION

0016Hereinafter, the present invention will be described in detail with reference to the accompanying drawings.

0017FIG. 1A is a schematic block diagram of a DNA PCR module according to the present invention. Referring to FIG. 1A, a PCR module 40 according to the present invention includes a PCR tube 10 having a PCR solution-containing PCR chamber 11 and a detection unit 30 for detecting a PCR product signal based on the amount of a PCR product of the PCR solution contained in the PCR chamber 11 of the PCR tube 10.

0018Here, the "the PCR tube 10" indicates a disposable or reusable device that is detachable from the PCR module 40, generally a microchip-type PCR tube. Preferably, the PCR tube 10 is mainly made of silicon. Therefore, heat generated by a heater 20 can be rapidly transferred, and thus, a temperature transition rate can be remarkably enhanced, relative to a conventional technology. Furthermore, PCR can be performed for smaller amounts of unconcentrated samples, unlike a conventional technology. Preferably, the PCR chamber 11 has a capacity of several tens microliters or less. If the capacity of the PCR chamber 11 exceeds several tens microliters, the content of a sample increases, thereby remarkably retarding PCR and increasing the size of the PCR tube 10. In this respect, the PCR chamber 11 with the capacity of more than several tens micrometers is not preferable with a view to the capacity of the entire system.

0019The PCR tube 10 includes the PCR chamber 11 as described above. The PCR chamber 11 contains a PCR solution. The PCR tube 10 also includes a temperature sensor (not shown) for measuring the temperature of the PCR solution. The PCR solution can be controlled to an appropriate temperature range by feedbacking the temperature of the PCR solution accurately measured by the temperature sensor. The temperature sensor may be disposed in the body of the PCR tube 10 or dipped in the PCR solution. An impedance measurement sensor is used to measure impedance in a PCR solution as a PCR product signal using a chip (10 of FIG. 7) for monitoring the impedance in real time and the detection unit 30 including an alternating power element, unlike the temperature sensor measuring the temperature of the PCR solution.

0020The heater 20 contained in the PCR module 40 is separately disposed from the PCR tube 10 and contacts with a lower surface of the PCR tube 10 to apply heat to the PCR tube 10. The heater 20 is provided with a temperature sensor 21 or a heat wire 22 on its lower surface to adjust on/off of the heater 20 so that the PCR tube 10 is maintained at an appropriate temperature. Preferably, the heater 20 is a microplate heater.

0021The PCR module 40 may further include a power supply unit 51 so that a fixed voltage is applied to the heater 20. The heater 20 can apply a uniform temperature to the PCR tube 10 for stable thermal transfer by electric power supplied from the power supply unit 51. However, in some cases, the power supply unit 51 can apply an electric power to the heater 20, together with another power supply unit connected to another device.

0022Preferably, the PCR module 40 may further include a cooler 43, in addition to the heater 20, so that the PCR solution in the PCR tube 10 is set to a desired temperature. That is, the cooler 43 is used to perform thermal circulation cycles by rapid temperature transition. As the cooler 43, there may be used a cooling fan for cooling an ambient air of the PCR module 40 to adjust the temperature of the PCR solution or a peltier device attached to the PCR tube 10 or the module 40 to adjust the temperature of the PCR solution. A water cooler may also be used. When needed, an airguide or a heatsink may be installed to enhance thermal conductivity.

0023The detection unit 30 of the PCR module 40 includes an optical source 31 or an alternating power element 33 and is used to detect a PCR product signal based on the amount of a PCR product. The principle and construction of the detection unit 30 will be described later.

0024FIG. 1B is a schematic block diagram of a PCR module 40 including a computing unit 41 according to the present invention. The PCR module 40 according to the present invention shown in FIG. 1A is operated in a passive mode. However, when the computing unit 41 is added to the PCR module 40, the whole processes of PCR can be automatically performed in a predetermined sequence or under real-time control. The computing unit 41 includes a central processing unit (CPU) 42, also known as microprocessor, an auxiliary memory 44, and a random access memory (RAM) 45 and controls a PCR procedure according to a determined program. The computing unit 41 independently performs real-time control of the detection unit 30, the PCR tube 10, the heater 20, the cooler 43, the power supply unit 51, and the like, through a data communication unit (not shown). The computing unit 41 performs appropriate computation based on data received from attachment sensors or the data communication unit and then performs a predetermined operation according to a determined program or an optional parameter value defined by a user. For example, the computing unit 41 can appropriately adjust the temperature of the PCR chamber 11 during PCR or determine the operating or suspending of the cooler 43 and the detection time interval of the detection unit 30. The computing unit 41 may further include a separate input/output unit 46 so that the PCR module 40 can be independently operated.

0025The computing unit 41 is operated according to a software program stored in the auxiliary memory 44. The auxiliary memory 44 is not particularly limited provided that it is that commonly used in the computation related field. For example, there may be used one or more selected from a hard disk, a floppy disk, an optical disk (CD, DVD, MD, etc.), a magnetic disk, and a flash memory card. CD used as the auxiliary memory 44 is used through a CD-ROM drive and a flash memory card used as the auxiliary memory 44 is used through a memory reader. The flash memory card is most preferable because of its small. size, easy use, and low power consumption. The flash memory card may be optionally selected from those known in the pertinent art. All types of flash memory cards such as Compact Flash (CF), Secure Digital (SD), Micro Drive (MD), memory stick, and extreme Digital (XD) can be used.

0026Preferably, a PCR software program for operating the computing unit 41 is stored in the auxiliary memory 44 as described above and used when needed. The auxiliary memory 44 also stores various data about user-defined parameters for PCR, i.e., PCR temperature and cycle number. A separate power supply unit may be connected to the computing unit 41.

0027FIGS. 2 and 3 illustrate schematic block diagrams of multiple PCR systems 1 in which the above-described PCR module 40, i.e., the PCR module 40 with or without the computing unit 41 is connected to a host computer 50.

0028The multiple PCR systems 1 according to the present invention include one or more PCR modules 40 and are used for PCR for different samples at different PCR conditions. That is, the multiple PCR systems 1 are used to independently and simultaneously perform the real-time control of several PCR procedures, thereby enhancing PCR efficiency.

0029With respect to a multiple PCR system 1 shown in FIG. 2, no computing units are not contained in one or more PCR modules 40. Here, the multiple PCR system 1 has a connection structure of the one or more PCR modules 40 to a data communication unit (not shown) of a host computer 50. That is, each of the PCR modules 40 includes a detection unit 30, a PCR tube 10, a heater 20, and the like, and these constitutional elements are controlled by received or transmitted data through data communication with the host computer 50. The PCR modules 40 are detachably installed in the multiple PCR system 1 so that they are connected to the host computer 50 when needed. There is no particular limitation on the number of the PCR modules 40. Preferably, the PCR modules 40 are composed of 2 to 24 numbers. If the number of the PCR modules 40 is too high, the host computer 50 may not appropriately control the PCR modules 40. In this regard, it is preferable to adjust the number of the PCR modules 40 according to the processing capability of the host computer 50.

0030The host computer 50 includes a CPU 52, an auxiliary memory 54, a RAM 55, and an input/output unit 60 and controls a PCR procedure according to a software program stored in the auxiliary memory 54. As described above, the auxiliary memory 54 may be one or more selected from a hard disk, an optical disk, a floppy disk, and a flash memory card. The software program stored in the auxiliary memory 54 has an additional management function for independently controlling the PCR modules 40, unlike the above-described computing unit 41 that has only a essential function for controlling constitutional elements of the module 40. That is, the software program stored in the auxiliary memory 54 can independently control the detection unit 30, the heater 20, and the PCR tube 10 contained in each of the PCR modules 40 so that PCR for different samples can be controlled at the different conditions. Furthermore, parameter values optionally defined by a user are stored in the auxiliary memory 54.

0031The host computer 50 includes the input/output unit 60, unlike the computing unit 41. The input/output unit 60 serves to input user-defined parameter values or display in real time various data received from the PCR modules 40. According to the input or displayed data, a PCR procedure can be appropriately controlled by changing or modifying in real time the user-defined parameter values. Preferably, a liquid crystal display is used as a display portion of the input/output unit 60 with a view to power consumption or dimension. In this case, it is more preferable to install a touch screen type input element on the display portion. Of course, a common keyboard, CRT, etc. may also be used.

0032The host computer 50 communicates with the PCR modules 40 via a data communication unit (not shown) through a wire or wireless mode. Common wire or wireless modes known in the pertinent art can be unlimitedly used. For example, a serial port such as RS-232C, a parallel port, a USB port, a 1394 port, etc. may be used for communication through the wire mode. It is preferable to use a USB port considering extendability. A radio frequency (RF) mode may be used for wireless communication.

0033In particular, the detection unit 30 in each of the PCR modules 40 detects a PCR product signal in the PCR tube 10 and transmits the detected signal to the host computer 50 through a wire or wireless mode. For example, the PCR product signal may be a fluorescence signal emitted from the PCR chamber 11 disposed in the PCR tube 10. The detection unit 30 acts as a fluorescence detector that detects a fluorescence signal and transmits the detected signal to the host computer 50. For this, the detection unit 30 includes an optical source 31 for applying light to the PCR solution. When light from the optical source 31 is applied to the PCR solution, the fluorescence emitted from the PCR solution is concentrated on a lens (not shown) and recorded after passing through a filter.

0034The PCR product signal may also be an electrical signal. In this case, the detection unit 30 includes a sensor (not shown) for sensing an electrical signal. The sensor is disposed in the PCR tube 10. The sensor detects a PCR product signal emitted when an alternating current is applied to the PCR solution in the PCR chamber 11 disposed in the PCR tube 10 and transmits the detected signal to the host computer 50. The received data is displayed on the display portion of the input/output unit 60 to be viewed by a user. For this, the detection unit 30 includes an alternating power element 33.

0035The host computer 50 may include a separate power supply unit (not shown) for stable power supply. The power supply unit can simultaneously perform power supply to the constitutional elements of the PCR modules 40. That is, the host computer 50 and the PCR modules 40 may receive an electric power from individual power supply units or a single common power supply unit. This is also applied to the detection unit 30 and the heater 20 contained in each of the PCR modules 40.

0036FIG. 3 illustrates a multiple PCR system 1 in which one or more PCR modules 40 include respective computing units 41. That is, in the multiple PCR system 1 shown in FIG. 3, the computing units 41 contained in the PCR modules 40 perform an essential function for substantially controlling a PCR procedure. A host computer 50 serves only to manage the computing units 41 by data communication with the computing units 41. The multiple PCR system 1 includes the respective computing units 41 in the PCR modules 40, and thus, the PCR modules 40 are independently controlled. Therefore, the multiple PCR system 1 has extendability regardless of the processing capability of the host computer 50, thereby removing a limitation of the number of the detachable PCR modules 40. In this respect, a considerable number of the PCR modules 40 can be mounted in the multiple PCR system 1 within the permissible capacity of the multiple PCR system 1. In particular, in a case where the host computer 50 and the PCR modules 40 are connected through a wire or wireless mode, there is no limitation on extendability, thereby ensuring almost unlimited extendability.

0037As described above, the host computer 50 and the computing units 41 have respective auxiliary memories 54 and 44. The auxiliary memories 54 and 44 store software programs for PCR control and the software programs execute their functions. In particular, the software programs can be connected through wire or wireless network such as a pier-pier network or a server-client network. For example, a LAN transmission technology using a common network interface card or hub may be used through a wire or wireless mode. Through such a connection system, the PCR modules 40 are controlled remotely by the host computer 50 through real-time data communication, thereby independently controlling the PCR modules 40. As described above, the computing units 41 can independently control constitutional elements in the respective PCR modules 40.

0038In particular, in the multiple PCR system 1 shown in FIG. 3, even though data detected by the detection unit 30 can be directly transmitted to the host computer 50, in a case where the detection unit 30 is controlled by each of the computing units 41, it is preferable that detected data are transmitted to the computing units 41 and then to the host computer 50. The detection mechanism of the detection unit 30 is as described above.

0039FIG. 4 is a schematic perspective view of a multiple PCR system 1 according to an embodiment of the present invention. Referring to FIG. 4, the multiple PCR system 1 includes a microchip-type PCR tube (not shown) having a PCR solution-containing PCR chamber (not shown), a heater (not shown) for applying heat to the PCR chamber of the PCR tube, and a detection unit (not shown) for detecting a PCR product signal based on the amount of the PCR product in the PCR solution, a plurality of modules 40, a host computer 50 electrically connected to the modules 40, a display unit 60 for displaying data received from the modules 40, and an input unit 70 that permits a user to input a signal. As used herein, the modules 40 are composed of six numbers and are detachably assembled. The temperature of the PCR chamber of the PCR tube received in each of the modules 40 is independently adjusted by a computing unit (not shown) of each of the modules 40 or the host computer 50.

0040FIG. 5 is a plan view of a microchip-type PCR tube 10 in a PCR module according to an embodiment of the present invention and FIG. 6 is a sectional view taken along line V-V of FIG. 5. Referring to FIGS. 5 and 6, the microchip-type PCR tube 10 is made of silicon and is formed with a PCR chamber 11 containing a PCR solution. The PCR chamber 11 has a sample inlet 12 for injection of the PCR solution and a sample outlet 13 for releasing of the PCR solution. A glass 15 is disposed on the PCR tube 10 made of silicon so that a detection unit (not shown) can detect a fluorescence signal emitted from the PCR product. A heater 20 is separately disposed from the PCR tube 10 and contacts with a lower surface of the PCR tube 10 to apply heat to the PCR tube 10.

0041A real-time PCR monitoring method using the multiple PCR system 1 according to an embodiment of the present invention in which a PCR product signal is a fluorescence signal emitted from the PCR chamber 11 will now be described in detail with reference to FIG. 3. First, a touch screen type monitor that acts as the input/output 60 of the host computer 50 receives PCR conditions, the power of an optical system, and signal measurement conditions, as input values. The input values are transmitted to the computing unit 41 of each of the modules 40, specifically, a microprocessor. The computing unit 41 permits the PCR tube 10 to have a predetermined temperature condition based on the temperature condition of the PCR tube 10 feedbacked from a temperature sensor (not shown) installed in the PCR tube 10. The computing unit 41 also determines the operating and suspending time of the optical system of the detection unit 30 so that an optical signal can be measured in real time according to the measurement conditions. As described above, the computing unit 41 of each of the modules 40 also independently controls constitutional elements of each of the modules 40 and the host computer 50 controls the modules 40 in real time. When the computing unit 41 is not contained in the modules 40, the host computer 50 independently controls the constitutional elements in the modules 40, as described above.

0042A real-time PCR monitoring method using a multiple PCR system in which a PCR product signal according to another embodiment of the present invention is a signal corresponding to impedance measured from a PCR product will now be described with reference to FIG. 3. This embodiment is different from the above-described embodiment in that the detection unit 30 of each of the modules 40 includes the alternating power element 33 and a sensor for sensing a signal corresponding to an electrical signal, i.e., impedance measured in the PCR solution when an alternating current is applied to the PCR solution in the PCR chamber 11. In this embodiment, first, a touch screen type monitor that acts as the input/output unit 60 of the host computer 50 receives PCR conditions, the magnitude and frequency of an alternating voltage for impedance measurement as input values. These input values are transmitted to the computing unit 41 of each of the modules 40. The computing unit 41 permits the PCR tube 10 to have a predetermined temperature based on the temperature condition of the PCR tube 10 feedbacked from a signal processing circuit of the PCR tube 10. The computing unit 41 also determines the magnitude and frequency of an alternating voltage of the detection unit 30 so that impedance can be measured in real time according to the determined conditions. As described above, the computing unit 41 of each of the modules 40 also independently controls the constitutional elements of each of the modules 40 and the host computer independently controls these modules 40. When the computing unit 41 is not contained in the modules 40, the host computer 50 independently controls the constitutional elements in the modules 40.

0043FIG. 7 is a plan view of a microchip-type PCR tube 10 when a detection unit includes an alternating power unit for impedance measurement and FIG. 8 is a rear view of the heater 20 including the temperature sensor 21 of FIG. 6. Referring to FIGS. 7 and 8, interdigitated electrodes 17 are disposed in a PCR chamber 11. Impedance measurement is performed while an alternating current is applied to a PCR mixture, i.e., a PCR solution. A micro-heat wire 22 and a temperature sensor 21 made of a thin metal foil enables temperature control on a chip.

0044Hereinafter, the present invention will be described more specifically by the following Examples. However, the following Examples are provided only for illustrations and thus the present invention is not limited to or by them.

Example 1: Preparation of PCR solution

0045To minimize difference between PCR experiments, other reagents except DNA samples were mixed to prepare a two-fold concentrated master mixture. Then, the master mixture was mixed with the DNA samples (1:1, by volume) to obtain a PCR solution.

0046The composition of the master mixture is as follows: <tables id="tabl0001" num="0001"><table frame="all"><tgroup cols="2" colsep="1" rowsep="0"><colspec colnum="1" colname="col1" colwidth="78.75mm" /><colspec colnum="2" colname="col2" colwidth="78.75mm" /><tbody valign="top"><row><entry namest="col1" nameend="col1" align="left">PCR buffer</entry><entry namest="col2" nameend="col2" align="left">1.0 µℓ</entry></row><row><entry namest="col1" nameend="col1" align="left">Distilled water</entry><entry namest="col2" nameend="col2" align="left">1.04 µℓ</entry></row><row><entry namest="col1" nameend="col1" align="left">10 mM dNTPs</entry><entry namest="col2" nameend="col2" align="left">0.1 µℓ</entry></row><row><entry namest="col1" nameend="col1" align="left">20 µ M of each primer mixture</entry><entry namest="col2" nameend="col2" align="left">0.2 µℓ</entry></row><row rowsep="1"><entry namest="col1" nameend="col1" align="left">Enzyme mixture</entry><entry namest="col2" nameend="col2" align="left">0.16 µℓ</entry></row></tbody></tgroup></table></tables>

Example 2: PCR on microchips

0047To investigate the effect of a thermal transfer rate and a temperature ramping rate on PCR, PCR was carried out on micro PCR chips with the dimension of 7.5 mm x 15.0 mm x 1.0 mm. The micro PCR chips were made of silicon and had advantages such as fast thermal transfer in reactants due to several hundreds times faster thermal conductivity than conventional PCR tubes, a fast temperature ramping rate, and maximal thermal transfer due to use of a trace of DNA samples.

00481 µℓ of the PCR solution of Example 1 was loaded in each of the micro PCR chips, and a PCR cycle of 92°C for 1 second and 63°C for 15 seconds was then repeated for 40 times. The experimental resultants were quantified using Labchip (Agilent) and amplification was identified on a 2% TAE agarose gel.

0049FIG. 9 shows electrophoretic results on a 2% TAE agarose gel after the amplification. Here, 10⁶ and 10⁴ indicate the copy numbers of a HBV template, NTC (no template control) is a negative control for PCR, and SD (standard) is a positive control for PCR.

0050FIGS. 10A and 10B are comparative views that illustrate the concentrations of PCR products with respect to the time required for PCR in a micro PCR chip according to the present invention and in a conventional PCR tube (MJ research, USA). Referring to FIGS. 10A and 10B, a time required for obtaining 40.54 ng/µℓ of a PCR product on a micro PCR chip according to the present invention was only 28 minutes. This is in contrast to 90 minutes required for obtaining 40.88 ng/µℓ of a PCR product using a conventional PCR tube. That is, a time required for obtaining the same concentration of a PCR product using the PCR technology of the present invention was only about one-third of that of using a conventional PCR tube.

0051FIG. 11A is a graph that illustrates a temperature profile for a conventional PCR tube and FIG. 11B is a graph that illustrates a temperature profile for an apparatus according to the present invention.

Example 3: Real-time PCR experiments using multiple PCR system based on signal corresponding to impedance measured in PCR product

0052In this Example, a signal emitted from a PCR solution (Promega) was measured in real time using the following multiple PCR system 1 as shown in FIG. 3.

0053Specifications of a host computer 50 and a computing unit 41 were as follows:

I. Host computer

0054Industrial embedded board(manufactured by Transmeta Co., Ltd., model: AAEON Gene 6330) was used.

0055The GENE-6330 is thinnest board in the AAEON SubCompact Board series. It has a Mini-PCI slot, an onboard SMI 712 LynxEM+ graphic chip provides TFT and DSTN panel support and comes with one 10/100Mbps Ethernet connector, four USB ports and a CompactFlash slot, offering great connectivity. Functional flexibility is enhanced through the choice of either a Type II PCMCIA and Type III Mini PCI slot. <ul id="ul0002" list-style="none" compact="compact"><li>Auxiliary memory: 2.5inch 30GB HDD (manufactured by Hitachi Co., Ltd.)</li><li>Network interface: RTL 8139DL, 10/100Base-T RJ-45</li><li>Input unit: 15.1 inch touch screen (manufactured by 3M Co., Ltd.)</li><li>Output unit: 15.1 inch LCD monitor (manufactured by BOE Hydis Co., Ltd.)</li><li>Operating System: MS Windows 2000 professional</li></ul>

II. Computing unit

0056The computing unit used C8051 F061 (manufactured by Silicon Laboratories Co., Ltd.)

0057The Silicon Laboratories, Inc. C8051 F061 is a 25 MIPS Mixed-Signal 8051 with 24 I/O Lines, 5 Timers, Watchdog Timer, PCA, SPI, SMBus, 12C, 2 UARTS, CAN 2.0B, 2 Channel (16-bit) A/D, 8 Channel (10-bit) A/D, 2 Channel (12-bit) D/A, 3 Analog Comparators, On-Chip Temperature Sensor, 64K Byte In-System Programmable FLASH, 256 Bytes RAM, 4K Bytes XRAM.

0058The host computer 50 and the computing unit 41 were connected through a hub over the Ethernet wire. A power supply unit installed at the host computer 50 supplied an electric power to the PCR modules 40 each including the computing unit 41. Further, the ambient temperature of the PCR modules 40 each including the PCR tube 10 was cooled by the cooler 43.

0059A microplate heater provided with the temperature sensor 21 and the heat wire 22 was used as the heater 20. The detection unit 30 including the alternating power unit 33 was used.

0060To minimize difference between PCR experiments, the PCR solution was prepared as follows: other reagents except DNA samples were mixed to prepare a two-fold concentrated master mixture and then the master mixture was mixed with the DNA samples (1:1, by volume) to obtain the PCR solution.

0061The composition of the master mixture is presented in Table 1 below. <tables id="tabl0002" num="0002"><table frame="all"><title>Table 1</title><tgroup cols="3" colsep="1" rowsep="1"><colspec colnum="1" colname="col1" colwidth="52.50mm" /><colspec colnum="2" colname="col2" colwidth="52.50mm" /><colspec colnum="3" colname="col3" colwidth="52.50mm" /><thead valign="top"><row><entry namest="col1" nameend="col2" align="center">Composition</entry><entry namest="col3" nameend="col3" align="center">Content</entry></row></thead><tbody valign="top"><row><entry namest="col1" nameend="col1" morerows="2" align="center">PCR buffer</entry><entry namest="col2" nameend="col2" align="center">Tris HCl</entry><entry namest="col3" nameend="col3" align="center">10 mM</entry></row><row><entry namest="col2" nameend="col2" align="center">KCl</entry><entry namest="col3" nameend="col3" align="center">50 mM</entry></row><row><entry namest="col2" nameend="col2" align="center">Triton X-100</entry><entry namest="col3" nameend="col3" align="center">0.10%</entry></row><row><entry namest="col1" nameend="col1" morerows="3" align="center">dNTP</entry><entry namest="col2" nameend="col2" align="center">dATP</entry><entry namest="col3" nameend="col3" align="center">200 µ M</entry></row><row><entry namest="col2" nameend="col2" align="center">dCTP</entry><entry namest="col3" nameend="col3" align="center">200 µ M</entry></row><row><entry namest="col2" nameend="col2" align="center">dGTP</entry><entry namest="col3" nameend="col3" align="center">200 µ M</entry></row><row><entry namest="col2" nameend="col2" align="center">dUTP (dTTP)</entry><entry namest="col3" nameend="col3" align="center">200 µ M</entry></row><row><entry namest="col1" nameend="col1" morerows="1" align="center">Primer</entry><entry namest="col2" nameend="col2" align="center">Upstream</entry><entry namest="col3" nameend="col3" align="center">1,000 nM</entry></row><row><entry namest="col2" nameend="col2" align="center">Downstream</entry><entry namest="col3" nameend="col3" align="center">1,000 nM</entry></row><row><entry namest="col1" nameend="col2" align="center">Taq polymerase</entry><entry namest="col3" nameend="col3" align="center">0.025 U/µℓ</entry></row><row rowsep="1"><entry namest="col1" nameend="col2" align="center">MgCl₂</entry><entry namest="col3" nameend="col3" align="center">1.5 mM</entry></row></tbody></tgroup></table></tables>

0062The temperature and duration conditions for PCR were the same as those used in conventional PCR tubes as follows: 1 cycle of 50°C for 120 seconds and 91°C for 180 seconds; 1 cycle of 92°C for 1 second and 63°C for 180 seconds; 44 cycles of 92°C for 1 second and 63°C for 15 seconds; and 1 cycle of 63°C for 180 seconds.

0063To measure impedance values, first, 1 µℓ of the PCR solution as prepared previously was loaded in each of micro PCR chips via a sample inlet as shown in FIGS. 7 and 8. After the micro PCR chips were received in modules, real-time impedance values were measured under an alternating voltage of 100 mV at 100 KHz.

0064FIG. 12A shows the real-time impedance values and FIG. 12B is a graph that illustrates impedance values during extension versus the number of PCR cycles. As seen from FIGS. 12A and 12B, PCR products increased with time, and impedance increased from after about 28 cycles.

Example 4: Real-time measurement and visualization of optical signals

0065Two-stage thermal cycling for the PCR solution of Example 1 was performed according to the PCR conditions presented in Table 2 below. The same apparatus as in Example 1 was used as the multiple PCR system 1 except that the detection unit 30 including the optical source 31 was used for signal detection. <tables id="tabl0003" num="0003"><table frame="all"><title>Table 2</title><tgroup cols="5" colsep="1" rowsep="1"><colspec colnum="1" colname="col1" colwidth="31.50mm" /><colspec colnum="2" colname="col2" colwidth="31.50mm" /><colspec colnum="3" colname="col3" colwidth="31.50mm" /><colspec colnum="4" colname="col4" colwidth="31.50mm" /><colspec colnum="5" colname="col5" colwidth="31.50mm" /><thead valign="top"><row><entry namest="col1" nameend="col1" align="center">Stage</entry><entry namest="col2" nameend="col2" align="center">Section</entry><entry namest="col3" nameend="col3" align="center">Temperature (°C)</entry><entry namest="col4" nameend="col4" align="center">Duration (sec.)</entry><entry namest="col5" nameend="col5" align="center">Cycles</entry></row></thead><tbody valign="top"><row><entry namest="col1" nameend="col1" morerows="1" align="center">Stage 1</entry><entry namest="col2" nameend="col2" align="center">Initial UNG incubation</entry><entry namest="col3" nameend="col3" align="center">50</entry><entry namest="col4" nameend="col4" align="center">120</entry><entry namest="col5" nameend="col5" morerows="1" align="center">1</entry></row><row><entry namest="col2" nameend="col2" align="center">Initial denaturation</entry><entry namest="col3" nameend="col3" align="center">89</entry><entry namest="col4" nameend="col4" align="center">60</entry></row><row><entry namest="col1" nameend="col1" morerows="3" align="center">Stage 2</entry><entry namest="col2" nameend="col2" align="center">Denaturation</entry><entry namest="col3" nameend="col3" align="center">89</entry><entry namest="col4" nameend="col4" align="center">10</entry><entry namest="col5" nameend="col5" morerows="3" align="center">40</entry></row><row><entry namest="col2" nameend="col2" align="center">Annealing</entry><entry namest="col3" nameend="col3" align="center">65</entry><entry namest="col4" nameend="col4" align="center">30</entry></row><row><entry namest="col2" nameend="col2" morerows="1" align="center">Detection time</entry><entry namest="col3" nameend="col3" align="center">Delay</entry><entry namest="col4" nameend="col4" align="center">5</entry></row><row><entry namest="col3" nameend="col3" align="center">Measure</entry><entry namest="col4" nameend="col4" align="center">23</entry></row><row><entry namest="col1" nameend="col1" morerows="2" align="center">Melting</entry><entry namest="col2" nameend="col2" align="center">Start temperature</entry><entry namest="col3" nameend="col5" align="center">60°C</entry></row><row><entry namest="col2" nameend="col2" align="center">Stop temperature</entry><entry namest="col3" nameend="col5" align="center">90°C</entry></row><row><entry namest="col2" nameend="col2" align="center">Ramping rate</entry><entry namest="col3" nameend="col5" align="center">0.1°C/sec</entry></row><row><entry namest="col1" nameend="col1" /><entry namest="col2" nameend="col2" align="center">Heating rate</entry><entry namest="col3" nameend="col5" align="center">10 °C/sec</entry></row><row rowsep="1"><entry namest="col1" nameend="col1" /><entry namest="col2" nameend="col2" align="center">Cooling rate</entry><entry namest="col3" nameend="col5" align="center">5 °C/sec</entry></row></tbody></tgroup></table></tables>

0066First, 1 µℓ of the PCR solution of Example 1 was loaded in each of micro PCR chips via a sample inlet as shown in FIGS. 4 and 5. The micro PCR chips were received in modules and then thermal cycling for the micro PCR chips were performed according to the PCR conditions presented in Table 2 like in FIG. 13A.

0067FIG. 13B is a graph that illustrates real-time signal values measured for 23 seconds during annealing with respect to the number of PCR cycles. As seen from the graph, the amounts of PCR products exponentially increased with time and signal values increased from after about 25 cycles. That is, the graph with a S-shaped curve appears.

0068FIG. 13C shows reduction of fluorescence signals due to separation of double-stranded DNAs into single-stranded DNAs with increasing temperature. Based on analysis of these fluorescence signal patterns, information about the melting temperatures of DNAs can be obtained. Creation of the melting curves of DNAs enables identification of desired DNAs after amplification.

0069As described above, a multiple PCR system according to the present invention includes a plurality of PCR modules, each of which includes a microchip-type PCR tube having a PCR solution-containing PCR chamber, a heater, a detection unit that detects a PCR product signal based on the amount of a PCR product in the PCR solution, and a computing unit that adjusts the temperature of the PCR chamber of the PCR tube; and a host computer electrically connected to the modules. The computing unit of each PCR module independently controls the detection unit and the temperature of the PCR chamber of the PCR tube received in each PCR module. Therefore, PCR for different samples can be carried out at different temperature conditions at the same time and can be monitored in real time.

0070As apparent from the above description, the present invention provides a PCR module in which co-amplification of different samples at different temperature conditions can be carried out and monitored in real time, a multiple PCR system using the same, and a PCR monitoring method.

0071Furthermore, PCR can be performed for smaller amounts of unconcentrated samples at an enhanced temperature transition rate using a microchip-type PCR tube made of silicon with excellent conductivity.