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WO1998009728A1 - Appareil et procede de cyclage thermique d'un echantillon - Google Patents

Appareil et procede de cyclage thermique d'un echantillon Download PDF

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Publication number
WO1998009728A1
WO1998009728A1 PCT/GB1997/002421 GB9702421W WO9809728A1 WO 1998009728 A1 WO1998009728 A1 WO 1998009728A1 GB 9702421 W GB9702421 W GB 9702421W WO 9809728 A1 WO9809728 A1 WO 9809728A1
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WO
WIPO (PCT)
Prior art keywords
sample
unit
cooling
temperature
heating
Prior art date
Application number
PCT/GB1997/002421
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English (en)
Inventor
Anthony Robert Corless
Original Assignee
Central Research Laboratories 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
Application filed by Central Research Laboratories Limited filed Critical Central Research Laboratories Limited
Priority to EP97939067A priority Critical patent/EP0934118A1/fr
Publication of WO1998009728A1 publication Critical patent/WO1998009728A1/fr

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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

Definitions

  • the present invention relates to an apparatus for, and method of, thermally cycling a sample.
  • the invention is suitable for, but not limited to, carrying out biochemical processes, particularly, but not exclusively, polymerase chain reactions (PCRs).
  • PCRs polymerase chain reactions
  • PCR is a well known technique for DNA amplification and is described in, for example United States Patent US-A-4,683,202. Generally PCR involves multiple thermal cycling of DNA steps for increasing the DNA yield.
  • Polymerase Chain Reactions are increased if rapid, accurate thermal transitions are achieved. This is believed to be the case not only when heating from a lower to a higher temperature, but also when cooling from a higher to a lower one. Rapid cooling of a sample permits rapid binding to complementary DNA chains, such as templates or probes, thereby leading to rapid and accurate amplification of DNA.
  • United Kingdom Patent GB-A-2233476 discloses apparatus for controlling the temperature of a reaction so that it follows a required temperature/time profile.
  • a multi-well support having a plurality of reaction sites is heated by a quartz halogen lamp and cooled by a fan.
  • the multi-well support is metallic and heats/cools reaction sites by thermal conduction.
  • a microprocessor and temperature sensors control thermal cycling.
  • the multi-well support (which in turn heats, and cools, the reaction sites) the time taken is relatively longer and the energy imparted to the system (reaction sites, reagent and multi-well support) during the heating phase, which must then be removed during the cooling phase, is significantly greater than the energy required merely to heat the reagents the time taken for each thermal cycle is increased to an undesirable extent.
  • United States Patent US 4,865,986 (Coy Corporation) describes and claims apparatus for selectively heating and cooling upright containers.
  • the apparatus is complex and expensive.
  • heating is performed using electrical resistance heaters. Because the apparatus is bulky there is relatively large thermal inertia. Also unless extremely high electrical currents are used, resistance heaters can take a relatively long time, typically one or two minutes, to heat an object. This means that the apparatus is not suitable for rapid thermal transitions from one temperature to another.
  • firstly temperature transitions must be achieved as quickly and as evenly as possible throughout the bulk of a sample; and secondly when a desired temperature is reached this temperature is maintained without any overshoot or dipping.
  • the first criteria implies that the apparatus should have a small heat capacity and good thermal conductivity.
  • the second criteria imposes design restraints on the thermal impedance of the apparatus as well as any control equipment used to monitor sample temperature and to drive any heater(s) and/or cooler(s).
  • An aim of the present invention is to provide an apparatus for, and method of, thermally cycling a sample sufficiently rapidly and with sufficient accuracy so as to be suitable for biochemical reactions and in particular polymerase chain reactions (PCRs) in order to increase the efficiency of the reaction.
  • Another aim of the invention is to provide an apparatus for, and a method of, thermally cycling a sample which overcomes the aforementioned problems associated with prior art systems.
  • a further aim of the present invention is to provide an apparatus for, and a method of, thermally cycling a sample sufficiently rapidly and with sufficient accuracy so as to be suitable for biochemical reactions and in particular polymerase chain reactions (PCRs) at very high speed, such that the time taken to complete the PCR process is substantially reduced compared to that achieved by the prior art.
  • PCRs polymerase chain reactions
  • a method of thermally cycling a sample comprising: i) providing a sample in a disposable unit and arranging the sample in the unit so that the sample is in thermal contact with a cooling means; ii) providing a source of infra-red radiation so that the radiation is absorbed by the sample and not absorbed to any extent by either the disposable unit or the heat sink means, thereby in use permitting a rapid thermal transition from a lower sample temperature to higher sample temperature to be achieved; iii) providing a coolant for cooling the disposable unit so that the temperature of the sample is reduced rapidly; and iv) repeating the aforementioned heating and cooling until a desired state of the sample is reached
  • the reaction is a PCR.
  • the PCR may be used to amplify DNA.
  • the thermal path includes a path through the sample and through all elements to the ultimate cooling means.
  • a "time constant" for the system is given by the product of the heat capacity and thermal resistance. Minimisation of this time constant implies an overall improvement to the performance.
  • apparatus for thermally cycling a sample in use the sample being contained in a disposable sample unit, the apparatus comprising: a housing for receiving the disposable sample unit so that it is in thermal contact with a heat sink, or otherwise directly accessible to a cooling means; infra-red heating means for heating the sample; cooling means for cooling the sample, and means for synchronising the heating and cooling means so that rapid thermal cycling of the sample is achieved according to a desired thermal cycling profile.
  • the disposable unit is in the form of a planar structure, that is an object which has a thickness small compared to its major axis in the plane, such as a plate or disc, and is such that either both major faces are thermally conducting (to allow double sided heating and cooling) or such that one major face is thermally conducting and the opposite major face is essentially thermally insulating.
  • This allows single sided heating and cooling substantially free of effects due to conduction of heat through the one major face.
  • Manufacturing the disposable unit in this way allows a high surface area to volume ratio allowing heat to be transported into and out of the disposable unit rapidly. For the most part, the temperature inside the disposable unit, that is the temperature of the sample, will equilibrate by thermal conduction. This sets a minimum possible time constant for the apparatus.
  • the thickness of the sample is less than 2.5 x 10 3 m, more preferably it is less than 1 x 10 "3 m, yet more preferably the thickness of the sample is approximately 100 10 '6 m, with a yet thinner layer being preferable until a limiting thinness is reached at which surface effects constrain the biochemical reactions.
  • the present state of knowledge prevents absolute specification of this lowest limit.
  • cooling of the disposable sample unit is achieved by directing a coolant onto the disposable unit or heat sink(s) thermally connected thereto and by thermal conduction and/or forced convection via the heat sinks. Fins, grooves or other means may be applied to the surface(s) of the disposable unit and/or heat sink(s) so as to increase their surface area.
  • the heat sink(s) and any mechanically robust elements of the disposable unit which are in the thermal path are manufactured from a material which has a high transmissivity to infra red radiation employed and a high thermal conductivity. More preferably these elements are manufactured from silicon or from diamond. Silicon is presently the most preferred material since its cost is substantially less than that of diamond.
  • the wavelength of infra-red radiation of interest is between 1.2 x 10 "6 m and 25 x 10 '6 m. More preferably the wavelength of radiation is between 1.4 x 0* m and 15 x W* m.
  • a preferred background source of radiation (which may optionally be used to maintain the sample temperature allowing a continuous balance between heating and cooling) is black body radiation filtered, for example using a silicon sheet to remove short wavelengths which may cause undesirable heating of the assembly.
  • the source temperature is chosen so as to maximise the radiation available at wavelengths above 1.4 x 10 '6 m where water has its most rapid absorption.
  • Most preferably the bulk of radiated energy is in the region of the strong absorption peak in the region of 3 x lO ⁇ wavelength.
  • Such a source is an ideal source of a background radiation, but is less suited to precise, rapid modulation required for rapid temperature change.
  • a presently preferred source of infra red power which is capable of rapid modulation is a carbon dioxide gas laser. Such lasers are readily available in power levels from a few Watts to a few kilo Watts.
  • the beam power may be readily, and rapidly, modulated and the beam may be readily directed.
  • Such a source may be employed in addition to the black body source, as discussed above, or it may be used as the sole infra red source, having its power adjusted as required to raise the temperature, maintain the temperature or allow cooling.
  • heating and cooling are performed as rapidly as possible so as to reduce the overall thermal cycle time.
  • temperature transitions from around 25°C to within a range of 90-98°C are achieved in less than one second. Most preferably the aforesaid temperature transitions are achieved in less than 0.1 second.
  • Precision of temperature measurement is preferable to within ⁇ 0.5°C.
  • the sample is directly heated and once heating is stopped, or reduced in intensity, the sample is rapidly cooled at a controlled rate by being in contact with a heat sink which is maintained at a low temperature, or with a cooling means. It is thus possible to thermally cycle the sample more rapidly than has been previously possible.
  • the heat sink may be formed integrally with the disposable unit.
  • a low-cost disposable unit is removable from a housing.
  • the disposable unit comprises a plastics envelope, and the heat sink means comprises two spaced apart sheets or slabs of silicon, which are moved to grip the faces of the plastics envelope.
  • the arrangement thus formed is hereinafter termed a reaction cell.
  • the advantage with a disposable unit is that it contains all sample materials in a sealed environment and may be removed after an experiment or reaction and easily and readily replaced without having to clean or modify any ancillary heating, cooling or control equipment. This enables higher throughput with less risk of cross-contamination.
  • the plastics material is preferably maintained as thin as is practically possible having regard to its mechanical function; namely it must be sufficiently strong to support its own weight.
  • the disposable unit comprises a silicon base, optionally coated with a thin layer of material which renders it biologically compatible with the PCR process, and a plastics envelope forming the sidewalls and top of a reaction cell.
  • the sidewalls and top are essentially thermally insulating with all salient heat transfer being through the thin biocompatible layer and the silicon base.
  • the thin layer is biocompatible and comprises one of the native oxides, oxynitrides or nitrides of silicon and/or a plastic layer, applied to the silicon, for example, by means of spin casting followed by drying or curing as required.
  • the thin biocompatible layer will have a thickness in the range 0.1- 10 microns, more preferably in the range 0.5 to 3 microns.
  • apparatus for thermally cycling a sample in use the sample being contained in a disposable sample unit, the apparatus comprising: a housing for receiving the disposable sample unit so that it is in thermal contact with a heat sink or directly with a fluid heat transfer means; heating means comprising a fluid heater and a pump for pumping the fluid so that the fluid heats the sample; cooling means for cooling the sample, and means for synchronising the heating and cooling means so that rapid thermal cycling of the sample is achieved according to a desired thermal cycling profile.
  • infra-red radiation is employed to heat the sample, as the sample usually contains a high percentage of water, which strongly absorbs infra-red radiation.
  • Plastic, or polymeric, material may be selected such that it is relatively non- absorbant of infra red radiation, at least at specific wavelengths of interest and is therefore appropriate for forming the disposable unit.
  • the radiation may optionally be filtered, at, or close to, its source, by passing it through a sheet of said plastic or polymeric material thereby removing, or reducing in intensity, such wavelengths as are absorbed while passing the remainder of the radiation.
  • the heat sink(s) are preferably formed from silicon, because silicon is transparent to infra-red radiation and has good thermal conductivity, and is a relatively low-cost and readily available material.
  • the wavelength of the infra-red radiation may be selected so that most of the radiation passes through the sample, with less than 10%, being absorbed by the sample.
  • the wavelength of radiation is selected so that the radiation is almost completely absorbed by the sample in a thin layer, with the remainder of the sample being heated principally by conduction from that layer.
  • the temperature is raised by either an increase in the radiation level absorbed in said thin layer or by radiation of a wavelength which is absorbed more uniformly throughout the sample thickness. Provision may be made to heat and cool the sample from two sides of the disposable unit so as to provide for more uniform irradiation induced heating and cooling.
  • the irradiation may be achieved by using more than one infra-red source, one radiation source and a combination of mirrors and beam splitters or by way of an alternative heater such as a heated fluid.
  • a reflecting layer of, for example gold may be disposed on or adjacent a surface of the sample unit on the side of the sample opposite the incoming direction of radiation.
  • the major face opposing said first major face is substantially thermally insulating.
  • Peltier electrode structures may be coupled to the heat sink(s) in order to induce cooling of the heat sink(s).
  • the Peltier structures may be permanently coupled to the heat sink(s); or, in a further modification, where the heat sink(s) are formed integrally with the disposable sample unit, they may be removably attached to the heat sink(s).
  • Peltier coolers are omitted and in this case the heat sink(s) may also be omitted.
  • the reaction cell in which the sample unit is supported, is preferably dimensioned and arranged so as to be received by a housing.
  • the housing may be in the form of an airtight vessel with an aperture for receiving the disposable unit.
  • An O-ring seal may be arranged to seal the periphery of the aperture between the housing and the sample reaction cell.
  • environmental sensors are provided within the housing which measure pressure and/or temperature and supply signals to a controller.
  • the housing includes forced cooling means such as, for example, a pump connected to a nozzle arranged to supply a coolant so that the coolant is directed onto one surface of the disposable unit or heat sink(s) thereby enhancing the rate of removal of heat.
  • forced cooling means such as, for example, a pump connected to a nozzle arranged to supply a coolant so that the coolant is directed onto one surface of the disposable unit or heat sink(s) thereby enhancing the rate of removal of heat.
  • Coolant is drained from the vessel, cooled and returned to the pump.
  • the pump whose rate may be varied, is arranged to deliver coolant under control of a microprocessor.
  • the micro-processor may have one or more inputs from the environmental sensors and is preferably arranged to control the temperature of the cooler and the heat source(s). In this arrangement, as in the previous, the micro-processor can be "taught" how to control the temperature, by way of neural networks and/or knowledge of a response function of the housing.
  • a liquid coolant is selected whose infra-red absorption is very low, when compared with that of the sample and most preferably negligible, in the spectral range of any irradiation used.
  • the liquid coolant may be selected to have a boiling point at or around a temperature of interest.
  • Liquids such as alcohols, paraffins or perfluorpolyethers are envisaged as being appropriate, especially as some of these can be tailored to have boiling points at or around temperatures of interest.
  • a further means of maintaining the heat transfer surface at a constant temperature is to arrange a jet, or jets, of gas periodically to blow the spent coolant from the said surface. This prevents insulating layers of coolant developing.
  • a yet further means of maintaining a defined level of coverage of the heat transfer surface is to arrange that the reaction cell rotates within the housing such that centrifugal forces cause the any coolant adhering to the surface to be expelled from the surface.
  • a suitable control algorithm and/or neural network may be taught to recognise changes in physical characteristics of a sample. As the sample is amplified its specific heat capacity, conductivity and consequently variations in heating and cooling rates are required and optical (uv, visible and infra-red) absorption or fluorescence characteristics may vary. Information derived from the aforesaid variations may be used to monitor the progress of the reaction and/or to control the rate of reaction.
  • Variations in the control of the rate of reaction can be achieved either analytically, as mentioned below, or by checking data with stored data on a look-up table. Similarly status checks may be made by the micro-processor as to how far reactions have progressed and at what stage reactions should be terminated. Such status checks may also be performed automatically. One way this may be achieved remotely is by shining a laser into the sample and determining how it is reflected or absorbed by using a photocell. A response function for the housing may be convoluted with a response function of the disposable unit so as to obtain a control function for the heating source(s). By judicious choice of coolant, thermal conductivity, specific heat capacity of the disposable unit, coolant mass flow rates, and wavelength and duration of infra-red radiation, it is possible to effect extremely rapid and precise thermal transitions of the sample in the disposable unit.
  • both heating and cooling are achieved using a forced fluid convection system.
  • the system comprises a housing for receiving a disposable unit; at least two fluid delivery circuits capable of supplying fluids at different temperatures, so that one of the circuits supplies fluid hotter than the other; and control means for synchronising delivery of the fluids by way of at least one valve, so that in use, the disposable unit is healed by supplying the hotter fluid and cooled by supply of the relatively cooler fluid.
  • the system may include infra-red heaters and where appropriate features of other embodiments already described above.
  • both heating and cooling are achieved using a forced fluid convection system in which a single working fluid is taken from a cooled reservoir and is heated to a precisely defined temperature as it flows to an outlet nozzle.
  • a forced fluid convection system in which a single working fluid is taken from a cooled reservoir and is heated to a precisely defined temperature as it flows to an outlet nozzle.
  • heating means take the form of a compact heater with low liquid capacity capable of rapid temperature changes, such as a resistively heated sintered, or otherwise fabricated, porous element.
  • Figure 1 is a sectional view of a sample reaction cell comprising a disposable sample unit mounted between two heat sinks;
  • Figures 2 to 4 show sections through alternative embodiments of the invention;
  • Figure 5 is a graph of an example of an idealised thermal cycle applied to a sample in a PCR.
  • Figure 6 shows a section through a further embodiment of the invention
  • Figure 7 shows is a sectional view through an alternative embodiment of a sample reaction cell.
  • a sample reaction cell 1 comprises a disposable planar disc shaped unit 2 and two heat sinks 8 and 10.
  • Unit 2 is formed from synthetic plastics, such as polypropylene or polycarbonate, and in use receives a liquid sample 4.
  • the sample 4 is mainly water in composition and contains DNA and other substances.
  • Unit 2 is tightly sandwiched between two heat sinks 8 and 10 formed from silicon sheets.
  • the sandwiched arrangement thus formed is hereinafter referred to as a reaction cell 1.
  • the reaction cell may contain a plurality of samples in an arrangement of wells.
  • Unit 2 is preferably not more than 2600 microns thick, and its walls are preferably not more than 50 microns. More preferably the walls are as thin as is compatible with mechanical handling.
  • the thickness of the sample 4 is thus reduced to a minimum compatible with the basic biochemical processes. These features are beneficial to the reduction of the thermal time constant of the reaction cell.
  • the area of the cell is not as important to the thermal performance as is its thickness, assuming that the extent of the cell 1 in the plane is significantly greater than its thickness, and that its area is uniformly coupled to heating and cooling means.
  • the wall thickness of the disposable unit is in the range 5-25 microns and the sample thickness is in the range
  • Unit 2 provides a disposable container for receiving the sample 4 and facilitates low cost and rapid fabrication.
  • Heat sinks 8 and 10 are typically, 5 x 10 '3 m thick and are positioned above and below the unit 2 and in good thermal contact therewith, so as to ensure good heat transfer to and from disposable unit 2. Disposed around the edges of each heat sink 8 and 10 are
  • Peltier devices 12 These devices are optional.
  • One or more infra-red radiation sources 14 are positioned above the heat sinks 8 and 10 and provide infra-red radiation to irradiate the reaction cell 1 whilst not impinging on the Peltier devices 12 if present.
  • heat sink 8 is in excellent thermal contact with the unit
  • sample 4 is always maintained at a temperature at or below the lowest temperature in the thermal cycle.
  • Plastics materials generally have a low thermal conductivity, allowing a temperature gradient to be established through the thickness of the wall of unit 2 with little heat transfer. However, as the wall is very thin this effect is negligible.
  • a flux of infra-red radiation is used, and by judicious choice of the range of wavelengths, it can be arranged that very little radiation is absorbed by the unit 2, and that useful absorption takes place in the sample 4.
  • the radiation flux is chosen to exceed, balance, or be less than the heat flow through the walls and into the heat sinks 8 and 10. In this way the sample temperature increases, can be maintained constant, or falls in response to the amount of heating.
  • the material from which the heat sinks 8 and 10 is made should be a good thermal conductor. Also, to permit a flux of infra-red radiation into the unit 2 the material from which it is made should be transparent to such radiation.
  • a material which offers both good thermal conductivity and transparency to infra-red radiation is silicon.
  • Heat is removed from the silicon heat sinks 8 and 10 by, for example, Peltier devices 12 which are arranged to maintain an even and controlled rate of heat removal.
  • Peltier devices 12 By mounting Peltier devices 12 around the periphery of the silicon heat sinks 8 and 10, a region is available for infra-red illumination of sample 4.
  • the good thermal conductivity of the silicon heat sinks 8 and 10 serves to give lateral heat spreading and a substantially uniform temperature profile throughout the disposable unit 2.
  • unit 2 containing sample 4 is introduced between the heat sinks 8 and 10.
  • a clamping or vice structure (not shown) is employed to move the heat sinks 8 and 10 from an open position in which the sample unit 2 is positioned between the heat sinks, to a closed position (as shown in Figure 1), in which the sample unit 2 is firmly gripped between the heat sinks 8 and 10; and is therefore in good thermal contact with them.
  • Infra-red radiation source 14 operates to maintain the sample 4 at a desired initial temperature. When thermal cycling is commenced, the output of radiation source 14 is raised in intensity to heat the sample 4 quickly to a desired temperature for a desired time. The infra-red source 14 may then be reduced in intensity in a desired manner to enable the sample 4 to cool back to its initial or other desired state.
  • Heat sinks 8 and 10 dissipate heat by way of conduction and natural convection, or serve to conduct the heat to the optional Peltier devices. As mentioned above the rate of dissipation may be enhanced by forming fins in the heat sinks. However, unit 2 or the reaction cell 1 may be incorporated into an apparatus adapted to increase the rate of cooling of the sample 4, by forced convection. Embodiments of this aspect of the invention will now be described with reference to Figures 2 to 4.
  • housing 20 which is in the general form of a right circular cylinder.
  • Housing 20 is formed from glass or synthetic plastics material.
  • Housing 20 has an aperture 22 in its upper surface.
  • a shelf 24 is defined within aperture 22. Shelf 24 is dimensioned and arranged to receive the sample reaction cell 1 (i.e. sample unit 2 and at least one heat sink) or the sample unit 2.
  • the sample reaction cell 1 has a DNA sample 4 contained in disposable sample unit 2.
  • An O-ring seal 26 seals a gap between the housing 20 and the edge of reaction cell 1. The O-ring seal therefore ensures the housing 20 is airtight.
  • Nozzle 30 projects into the housing 20.
  • the drain 28 is arranged to drain any coolant fluid from within the housing 20 and deliver the coolant to a cooler 32. Cooler 32 is arranged to cool any fluid collected by drain 28 and to deliver the fluid to nozzle 30 via pump 34.
  • Temperature sensors 36 sense the temperature of the fluid at different positions in the housing 20. Temperature sensor 36a provides an indication of the temperature of the fluid being drained from the housing 20. This temperature is indicated by T
  • Temperature sensor 36b provides an indication of the temperature of the coolant fluid as it enters nozzle 30 and this is indicated by T 2 .
  • Temperature sensor 36c senses the temperature within the housing 20 and this is indicated by T 3 . Signals indicative of temperatures Ti, T 2 and T 3 are input into a controller 38 and the information is stored in and manipulated by computer 46.
  • Computer 46 communicates with the controller 38 by way of a bi-directional data bus 50.
  • Control signals 40, 42 and 44 are output from controller 38.
  • Control signal 40 switches infra-red heating source 14 on and off.
  • Control signal 42 controls cooler 32.
  • Control signal 44 controls pump 34.
  • the apparatus will now briefly be described in its operation and with reference to the graph shown in Figure 5.
  • Sample reaction cell 1 is placed within aperture 22 and O- ring seal 26 is fitted snugly between the cell 1 and wall of housing 20.
  • Information as to the type of polymerase chain reaction (PCR), amount of sample 4, type of sample 4, ambient temperature and thermal cycling profile are input into the computer 46.
  • Software within the computer 46 together with information (which may have been obtained from previous experiments), calculates the desired mass flow rate of coolant.
  • pump 34 pumps coolant slowly. This enables the housing 20, cell 1 and sample 4 to reach an equilibrium temperature and for all sensors 36 to reach steady state. In practise this may only take a few seconds or at most one or two minutes. Once a steady state has been reached rapid thermal cycling may commence.
  • controller 38 switches on infra-red heating source 14.
  • Source 14 rapidly raises the temperature of the sample DNA to temperature Td. This is shown in Figure 5 as point B. Heating is achieved extremely rapidly for the reasons described above.
  • the temperature of the sample is typically in the range of 90 - 98°C. At this temperature
  • coolant may still be pumped onto the heat sink 8 or pumping may be switched off temporarily.
  • the state the experiment has reached is shown by point B on the graph in Figure 5.
  • the temperature is maintained at temperature Td typically for a dwell period.
  • the duration of this dwell period is optimised for the particular PCR reaction, and will generally be minimised.
  • the intensity of heat source 14 is then reduced, possibly to zero, allowing sample
  • This stage is known as the annealing stage.
  • An optimum temperature for the annealing stage is typically within the range of 45-85°C. This temperature is reached rapidly as a result of the jets 48 of coolant impinging against lower surface of heat exchange 8. Undershoot of the cooling is minimised by both careful consideration of the rate of supply of coolant, (and/or the coolant temperature), and by applying a background radiation level which maintains the sample temperature.
  • DNA stretches or primers attach to parts of a target sequence.
  • the next stage of the cycle involves reheating of the sample 4. This period is known as active amplification of DNA and at the onset of this stage the temperature of the apparatus is rapidly increased to Tm. This is shown by point D on Figure 5. During this stage nucleotide extension occurs, thereby forming complementary DNA strands. The optimum temperature range for this stage of the process occurs around 40 - 70°C. Reheating is conveniently arranged by increasing the radiation level to increase and finally maintain the temperature Tm. Conveniently, the coolant may be arranged to have a boiling point at, or close to, the temperature Tm. The complete cycle is then repeated, typically another 20 - 40 times.
  • the temperature of the sample 4 can be varied at any time quickly and precisely.
  • Temperature sensor 36c provides a feedback signal of temperature T 3 which is used to monitor the temperature inside the housing 20.
  • the controller 38 acts to change the temperature of the sample reaction cell 1. Again, this occurs almost instantaneously by virtue of the rapid heat transfer capabilities of the heater 33, cooler 32, pump 34 and infra-red source 14 and also because: the heater 33, cooler 32 and pump 34 are close together; their inter-connecting tubes are short; and they have a low specific heat capacity. Thus a relatively small amount of liquid is held in these components allowing rapid transition of the temperature of the jets 48.
  • the operation of heater 33, cooler 32 and pump 34 is controlled by a microprocessor, rapid temperature transits are possible.
  • FIG. 3 shows a similar arrangement to that shown in Figure 2 in which like parts bear the same reference numerals.
  • Figure 3 shows a housing 20 in which a nozzle housing 30 has three separate nozzles 31 a, b and c. Three separate heating, cooling and pumping circuits are also shown. Each circuit is capable of supplying a fluid at a different temperature. Valves 45 a, b and c are opened and closed in accordance with control signals from controller 38.
  • the operation of me arrangement shown in Figure 3 is similar to that shown in Figure 2, except that in the embodiment shown in Figure 3 there is no infra-red heating source. Heating is performed by way of one or more jets 48 of hot fluid, which is preferably hot water and which emerges through at least one of the nozzles 31.
  • the arrangement may be used in conjunction with an infra-red heating source but this is not necessary because the relatively higher temperature of water required to heat the sample reaction cell 1 is supplied by an electric heater 32a.
  • a one way valve 37 is present in that circuit so as to prevent unwanted back flow into the body of the housing 20. Cooling is achieved in a similar fashion to the embodiment shown in Figure 2, namely by directing a jet of coolant against the heat sink 8. Temperatures of the three fluid channels are separately indicated as Tx, Ty and Tz in Figures 3 and 4.
  • Figure 4 shows a similar arrangement to that shown in Figure 3.
  • the disposable sample unit 2 is in contact with only one heat sink 8.
  • an optional infra-red heater may be included to accelerate heating.
  • both heating and cooling can be achieved using jets of liquid.
  • the reaction cell may be conveniently constructed, as shown in Figure 7, from a metal base 60 with a plastics envelope 62, 64 defined thereupon.
  • a presently preferred embodiment is an aluminium base 60 with a thin plastics coating 62, (rendering the surface biocompatible), upon which coating 62 is bonded a suitably domed, or pressed, plastics component 64 which defines the volume occupied by sample 4.
  • Figure 6 shows a similar arrangement to that shown in Figure 2. Like parts bear the same reference numerals.
  • the disposable sample unit 2 is in contact with only one heat sink 8.
  • the infra red heating 14 is shown to enter the disposable sample unit 2 through the heat sink 8, heating the cooled side of the disposable sample unit.
  • This arrangement of directing infra red radiation preferentially to the cooled side of the unit is presently preferred.
  • Modification may be made to the reaction cell 1 so that it comprises an integral temperature sensor (not shown), such as a moulded thermocouple contact or a thin film thermocouple.
  • an integral temperature sensor such as a moulded thermocouple contact or a thin film thermocouple.
  • Such temperature sensors are accurate to ⁇ 1.0°C are cheap, stable and inert.
  • Electric and/or magnetic fields may be arranged to act on the sample so as to manipulate or vary one or more physical characteristics before, during or after the PCR.
  • the housing 20 may be incorporated into a centrifuge so that centrifugal and/or vibrational forces are caused to act on the sample 4 so as to enhance mixing or separation.
  • the stage to which an experiment has progressed may be ascertained by a number of methods.
  • One of these includes launching a low energy laser (not shown) into the sample unit 2 and monitoring the amount of absorption or reflection of the laser by the DNA, by using a photocell or fluorescence detection (not shown). Any of the embodiments described above may include this feature.
  • the pressure and/or temperature of the interior of the housing 20 may be varied so as to modify the boiling points of liquid jet(s) 48 which impinge on the heat sink 8.
  • the interior pressure of the housing 20 may be reduced relatively simply.
  • suitable non-return and one way valves may be required in fluid channels so as to prevent suck back of any fluid into the housing 20.
  • a gasket may be required between the lower surface of heat sink 8 and the shelf 24 on which it sits in the housing 20. Pressure within the housing may be raised in order to increase the boiling point of coolants.
  • the disposable unit may require clamping of the reaction cell 1 so that it remains in an air tight fit within aperture 22 during an experiment and is not urged out by higher internal pressure within the housing 20.
  • Other variations and features which may be applied to the disposable unit include: the addition of a code by which the unique disposable unit 2 is identified to computer 46 and in particular from which essential control parameters for the reaction may be conveyed; and/or the addition of a semi conductor "chip" which stores information concerning the reaction cycle undergone by the disposable unit; and/or use of capillary action to fill the disposable unit 2; the use of a tight fitting plug permanently to seal the unit 2 following sample loading; and/or the use of a suitably viscous thermally, or otherwise, cured material to seal a capillary opening following sample loading; and/or the use of a tape seal to seal an aperture (in the unit) used for sample loading; and/or the supply of disposable units predosed with reagents, (particular PCR reagents) in a dried form.

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  • Health & Medical Sciences (AREA)
  • Chemical & Material Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Biochemistry (AREA)
  • General Health & Medical Sciences (AREA)
  • Molecular Biology (AREA)
  • Clinical Laboratory Science (AREA)
  • Chemical Kinetics & Catalysis (AREA)
  • Apparatus Associated With Microorganisms And Enzymes (AREA)

Abstract

L'invention porte sur un appareil et un procédé de cyclage thermique particulièrement adaptés à la PCR et comprenant une unité jetable (2) recevant un échantillon (4), un dispositif de chauffage (14), et un refroidisseur (32). Le chauffage et le refroidissement se font très rapidement et peuvent être réglés avec une grande précision, ce qui permet d'accroître la vitesse de la PCR. L'une des variantes préférées comporte un boîtier (20) ou le chauffage est assuré par un dispositif de chauffage IR (14), et le refroidissement, par un jet (48) de liquide de refroidissement. Une autre variante recourt pour le chauffage et le refroidissement à des liquides chauffés ou refroidis distribués par différents circuits. L'invention résout les problèmes associés aux systèmes antérieurs en raison de son prix moindre et son inertie thermique inférieure à celle des systèmes existants; elle permet donc d'effectuer le cyclage thermique d'un échantillon (4) plus vite qu'auparavant. De plus, l'utilisation d'une unité porte-échantillon jetable (2) facile à extraire et à remplacer réduit le risque d'intercontamination, tout en accroissant le rythme de traitement des échantillons.
PCT/GB1997/002421 1996-09-06 1997-09-08 Appareil et procede de cyclage thermique d'un echantillon WO1998009728A1 (fr)

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Application Number Priority Date Filing Date Title
EP97939067A EP0934118A1 (fr) 1996-09-06 1997-09-08 Appareil et procede de cyclage thermique d'un echantillon

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
GBGB9618595.4A GB9618595D0 (en) 1996-09-06 1996-09-06 Reaction cell
GB9618595.4 1996-09-06

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WO1998009728A1 true WO1998009728A1 (fr) 1998-03-12

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Cited By (19)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1999017881A1 (fr) * 1997-10-07 1999-04-15 The Perkin-Elmer Corporation Appareil pour cycleur thermique a impact de fluide
WO1999039005A1 (fr) * 1998-01-29 1999-08-05 University Of Pittsburgh Procede de thermocyclage rapide destine a l'analyse d'echantillons
WO2000029115A1 (fr) * 1998-11-16 2000-05-25 MAX-PLANCK-Gesellschaft zur Förderung der Wissenschaften e.V. Dispositifs et procedes de temperage d'echantillons
DE19908745A1 (de) * 1999-02-22 2000-08-24 Univ Schiller Jena Verfahren und Vorrichtung zur Temperierung von Analysengut in Multiwellanalysenplatten
EP1080230A1 (fr) * 1998-05-19 2001-03-07 Cell Robotics, Inc. Procede et appareil permettant d'activer une reaction enzymatique induite par la chaleur au moyen d'energie electromagnetique
WO2003007677A2 (fr) 2001-07-16 2003-01-30 Idaho Technology, Inc. Systeme de cyclage thermique et son procede d'utilisation
WO2003016558A1 (fr) * 2001-08-16 2003-02-27 Corbett Research Pty Ltd Dispositif thermique a ecoulement continu
DE102004027161B3 (de) * 2004-06-03 2005-08-25 Siemens Ag Ventileinrichtung
DE102004062804B3 (de) * 2004-12-27 2006-05-24 Bernhard Harter Kombitemperierungsgerät
US7264961B2 (en) 2000-03-08 2007-09-04 The Secretary Of State For Defence In Her Britannic Majesty's Government Of The United Kingdom Of Great Britain And Northern Ireland Reaction system for thermal cycling
US7264950B1 (en) * 1999-09-29 2007-09-04 The Secretary Of State For Defence In Her Britannic Majesty's Government Of The United Kingdom Of Great Britain And Northern Ireland Reaction system for performing in the amplification of nucleic acids
EP2108451A1 (fr) * 2008-04-11 2009-10-14 Eppendorf AG Dispositif d'exécution de réactions dans des échantillons
US7851185B2 (en) * 2006-06-30 2010-12-14 Canon U.S. Life Sciences, Inc. Combined thermal devices for thermal cycling
US8778283B2 (en) 2001-04-30 2014-07-15 The Secretary Of State For Defence Reagent delivery system
US8936933B2 (en) 2003-02-05 2015-01-20 IQumm, Inc. Sample processing methods
US9005551B2 (en) 1998-06-24 2015-04-14 Roche Molecular Systems, Inc. Sample vessels
US9662652B2 (en) 2000-12-29 2017-05-30 Chen & Chen, Llc Sample processing device for pretreatment and thermal cycling
WO2022093844A1 (fr) 2020-10-27 2022-05-05 Canon Virginia, Inc. Procédés et systèmes de cyclage thermique
PL446363A1 (pl) * 2023-10-12 2025-04-14 Marek Kanturski Szybki termocykler PCR dla rozłącznych modułów PCR z ciągłym pomiarem temperatury wewnątrz komór reakcyjnych oraz sposób regulowania temperatury w reakcji PCR

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EP0347579A2 (fr) * 1988-06-01 1989-12-27 Daimler-Benz Aerospace Aktiengesellschaft Dispositif comportant un support de structure particulière pour la réception, l'analyse et le traitement d'échantillons
EP0379437A1 (fr) * 1989-01-20 1990-07-25 Bertin & Cie Procédé et dispositif de régulation rapide d'une température de paroi
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EP0542422A1 (fr) * 1991-11-12 1993-05-19 General Atomics Plaque de microtitrage à puits multiples
WO1993022058A1 (fr) * 1992-05-01 1993-11-11 Trustees Of The University Of Pennsylvania Analyse par amplification de polynucleotide a l'aide d'un dispositif micro-fabrique
WO1995018676A1 (fr) * 1994-01-11 1995-07-13 Abbott Laboratories Appareil et procede de cyclage thermique de dosages d'acides nucleiques
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DE3808942A1 (de) * 1988-03-17 1989-09-28 Bio Med Gmbh Ges Fuer Biotechn Inkubator, insbes. fuer die polymerase-ketten-methode
EP0347579A2 (fr) * 1988-06-01 1989-12-27 Daimler-Benz Aerospace Aktiengesellschaft Dispositif comportant un support de structure particulière pour la réception, l'analyse et le traitement d'échantillons
EP0379437A1 (fr) * 1989-01-20 1990-07-25 Bertin & Cie Procédé et dispositif de régulation rapide d'une température de paroi
US5504007A (en) * 1989-05-19 1996-04-02 Becton, Dickinson And Company Rapid thermal cycle apparatus
EP0402995A2 (fr) * 1989-06-12 1990-12-19 Johnson & Johnson Clinical Diagnostics, Inc. Dispositif de régulation de la température et récipient de réaction
US5455175A (en) * 1990-06-04 1995-10-03 University Of Utah Research Foundation Rapid thermal cycling device
EP0542422A1 (fr) * 1991-11-12 1993-05-19 General Atomics Plaque de microtitrage à puits multiples
WO1993022058A1 (fr) * 1992-05-01 1993-11-11 Trustees Of The University Of Pennsylvania Analyse par amplification de polynucleotide a l'aide d'un dispositif micro-fabrique
WO1995018676A1 (fr) * 1994-01-11 1995-07-13 Abbott Laboratories Appareil et procede de cyclage thermique de dosages d'acides nucleiques
US5508197A (en) * 1994-07-25 1996-04-16 The Regents, University Of California High-speed thermal cycling system and method of use
DE19519015C1 (de) * 1995-05-24 1996-09-05 Inst Physikalische Hochtech Ev Miniaturisierter Mehrkammer-Thermocycler
WO1996041864A1 (fr) * 1995-06-13 1996-12-27 The Regents Of The University Of California Chambre de microreaction chauffee par laser a diode dotee d'un moyen de detection d'echantillons
US5589136A (en) * 1995-06-20 1996-12-31 Regents Of The University Of California Silicon-based sleeve devices for chemical reactions

Cited By (34)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO1999017881A1 (fr) * 1997-10-07 1999-04-15 The Perkin-Elmer Corporation Appareil pour cycleur thermique a impact de fluide
AU733101B2 (en) * 1997-10-07 2001-05-10 Applera Corporation Apparatus for a fluid impingement thermal cycler
WO1999039005A1 (fr) * 1998-01-29 1999-08-05 University Of Pittsburgh Procede de thermocyclage rapide destine a l'analyse d'echantillons
US6413766B2 (en) 1998-01-29 2002-07-02 University Of Pittsburgh Of The Commonwealth System Rapid thermocycling for sample analysis
EP1080230A1 (fr) * 1998-05-19 2001-03-07 Cell Robotics, Inc. Procede et appareil permettant d'activer une reaction enzymatique induite par la chaleur au moyen d'energie electromagnetique
EP1080230A4 (fr) * 1998-05-19 2001-12-12 Cell Robotics Inc Procede et appareil permettant d'activer une reaction enzymatique induite par la chaleur au moyen d'energie electromagnetique
US10022722B2 (en) 1998-06-24 2018-07-17 Roche Molecular Systems, Inc. Sample vessels
US9005551B2 (en) 1998-06-24 2015-04-14 Roche Molecular Systems, Inc. Sample vessels
WO2000029115A1 (fr) * 1998-11-16 2000-05-25 MAX-PLANCK-Gesellschaft zur Förderung der Wissenschaften e.V. Dispositifs et procedes de temperage d'echantillons
DE19908745A1 (de) * 1999-02-22 2000-08-24 Univ Schiller Jena Verfahren und Vorrichtung zur Temperierung von Analysengut in Multiwellanalysenplatten
US7659096B2 (en) 1999-09-29 2010-02-09 The Secretary Of State For Defence In Her Britannic Majesty's Government Of The United Kingdom Of Great Britain And Northern Ireland Reaction system for performing in the amplification of nucleic acids
US7264950B1 (en) * 1999-09-29 2007-09-04 The Secretary Of State For Defence In Her Britannic Majesty's Government Of The United Kingdom Of Great Britain And Northern Ireland Reaction system for performing in the amplification of nucleic acids
US8986927B2 (en) 1999-09-29 2015-03-24 The Secretary Of State For Defence Reaction system for performing in the amplification of nucleic acids
US7264961B2 (en) 2000-03-08 2007-09-04 The Secretary Of State For Defence In Her Britannic Majesty's Government Of The United Kingdom Of Great Britain And Northern Ireland Reaction system for thermal cycling
US7537927B2 (en) 2000-03-08 2009-05-26 The Secretary Of State For Defence In Her Britannic Majesty's Government Of The United Kingdom Of Great Britain And Northern Ireland Reaction system for thermal cycling
US9662652B2 (en) 2000-12-29 2017-05-30 Chen & Chen, Llc Sample processing device for pretreatment and thermal cycling
US8778283B2 (en) 2001-04-30 2014-07-15 The Secretary Of State For Defence Reagent delivery system
US9067209B2 (en) 2001-04-30 2015-06-30 The Secretary Of State For Defense Reagent delivery system
US8815181B2 (en) 2001-04-30 2014-08-26 The Secretary Of State For Defence In Her Britannic Majesty's Government Of The United Kingdom Of Great Britain And Northern Ireland Reagent delivery system
WO2003007677A2 (fr) 2001-07-16 2003-01-30 Idaho Technology, Inc. Systeme de cyclage thermique et son procede d'utilisation
US7709250B2 (en) 2001-08-16 2010-05-04 Corbett Research Pty Ltd Continuous flow thermal device
WO2003016558A1 (fr) * 2001-08-16 2003-02-27 Corbett Research Pty Ltd Dispositif thermique a ecoulement continu
US9708599B2 (en) 2003-02-05 2017-07-18 Roche Molecular Systems, Inc. Sample processing methods
US8936933B2 (en) 2003-02-05 2015-01-20 IQumm, Inc. Sample processing methods
US10443050B2 (en) 2003-02-05 2019-10-15 Roche Molecular Systems, Inc. Sample processing methods
DE102004027161B3 (de) * 2004-06-03 2005-08-25 Siemens Ag Ventileinrichtung
DE102004062804B3 (de) * 2004-12-27 2006-05-24 Bernhard Harter Kombitemperierungsgerät
US9272282B2 (en) 2006-06-30 2016-03-01 Canon U.S. Life Sciences, Inc. Combined thermal devices for thermal cycling
US8507257B2 (en) 2006-06-30 2013-08-13 Canon U.S. Life Sciences, Inc. Combined thermal devices for thermal cycling
US7851185B2 (en) * 2006-06-30 2010-12-14 Canon U.S. Life Sciences, Inc. Combined thermal devices for thermal cycling
US10226772B2 (en) 2006-06-30 2019-03-12 Canon U.S. Life Sciences, Inc. Combined thermal devices for thermal cycling
EP2108451A1 (fr) * 2008-04-11 2009-10-14 Eppendorf AG Dispositif d'exécution de réactions dans des échantillons
WO2022093844A1 (fr) 2020-10-27 2022-05-05 Canon Virginia, Inc. Procédés et systèmes de cyclage thermique
PL446363A1 (pl) * 2023-10-12 2025-04-14 Marek Kanturski Szybki termocykler PCR dla rozłącznych modułów PCR z ciągłym pomiarem temperatury wewnątrz komór reakcyjnych oraz sposób regulowania temperatury w reakcji PCR

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Publication number Publication date
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EP0934118A1 (fr) 1999-08-11

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