WO2025230778A2

WO2025230778A2 - Method for processing biological samples

Info

Publication number: WO2025230778A2
Application number: PCT/US2025/025837
Authority: WO
Inventors: Jes Tougaard Gram
Original assignee: Gram Medical Inc
Current assignee: Gram Medical Inc
Priority date: 2024-04-30
Filing date: 2025-04-22
Publication date: 2025-11-06
Anticipated expiration: 2026-10-30
Also published as: WO2025230778A3

Abstract

A method and device for providing at least one reaction zone in an assembled disposable reaction fluid device having a contactless heating of at least one preferably inductive heat-able material inside a disposable reaction fluid device for biologic sampling. At least one inductive heat-able material is positioned in a disposable reaction fluid device where a biologic sample is introduced. The inductive heat-able material is then exposed to inductive heating and heated up to one or more temperatures during the processing of the biologic sample. The inductive heat-able material in the disposable reaction fluid device could be movable and/or placed in stationary positions where the biologic is movable by capillary, gravity, magnetic, centrifugal and/or other force moving the biologic sample through the device.

Description

METHOD FOR PROCESSING BIOLOGICAL SAMPLES FIELD OF INVENTION [0001] The present invention relates to methods, apparatus, and test disposables for the processing of biologic sample materials. BACKGROUND OF THE INVENTION [0002] Many different chemical, biochemical, and other reactions are sensitive to temperature variations. Examples of thermal processes in genetic amplification include, but are not limited to, Polymerase Chain Reaction (PCR), Sanger sequencing, etc. [0003] The reactions may be enhanced or inhibited based on the temperatures of the materials involved. Although it may be possible to process samples individually and obtain accurate sample-to-sample results, individual processing can be time-consuming and expensive. [0004] One approach to reducing the time and cost of thermally processing multiple samples is to use a device including multiple chambers in which different portions of one or more samples may be processed simultaneously. [0005] When multiple reactions are performed in different chambers, however, one significant problem can be accurate control of chamber-to-chamber temperature uniformity. [0006] Temperature variations between chambers may result in misleading or inaccurate results. In some reactions, for example, it may be critical to control chamber-to-chamber temperatures within the range of ±1° C. or less to obtain accurate results. [0007] The need for accurate temperature control may manifest itself as the need to maintain a desired temperature in each of the chambers, or it may involve a change in temperature – raising or lowering the temperature in each of the chambers to a desired set point. [0008] In reactions involving a change in temperature, the speed or rate at which the temperature changes in each of the chambers may also pose a problem. For example, slow temperature transitions may be problematic if unwanted side reactions occur at intermediate temperatures. [0009] Alternatively, temperature transitions that are too rapid may cause other problems. As a result, another problem that may be encountered is comparable chamber-to-chamber temperature transition rate. [0010] In addition to chamber-to-chamber temperature uniformity and comparable chamber-to-chamber temperature transition rate, a variety of transitions (upward and/or downward) between three or more desired temperatures may be required. [0011] In some reactions polymerase chain reaction (PCR), thermal cycling must be repeated up to thirty or more times. Thermal cycling devices and methods that attempt to address the problems of chamber-to-chamber temperature uniformity and comparable chamber-to-chamber temperature transition rates, however, typically suffer from a lack of overall speed-resulting in extended processing times that ultimately raise the cost of the procedures. [0012] One or more of the above problems may be implicated in a variety of chemical, biochemical, and other processes. Examples of some reactions that may require accurate chamber-to-chamber temperature control, comparable temperature transition rates, and/or rapid transitions between temperatures may include the manipulation of nucleic acid samples to assist in the deciphering of the genetic code. [0013] One common example of a reaction in which the problems above may be implicated is PCR amplification. Traditional thermal cycling equipment for conducting PCR uses polymeric microcuvettes that are individually inserted into bores in a metal block. [0014] The sample temperatures are then cycled between low and high temperatures, e.g., 55° C. and 95° C. for PCR processes. When using the traditional equipment according to the traditional methods, the high thermal mass of the thermal cycling equipment (which typically includes the metal block and a heated cover block) and the relatively low thermal conductivity of the polymeric materials used for the microcuvettes result in processes that can require two, three, or more hours to complete for a typical PCR amplification. [0015] One attempt at addressing the relatively long thermal cycling times in PCR amplification involves the use of a device integrating 96 microwells and distribution channels on a single polymeric card. Integrating 96 microwells in a single card does address the issues related to individually loading each sample cuvette into the thermal block. [0016] This approach does not, however, address the thermal cycling issues such as the high thermal mass of the metal block and heated cover or the relatively low thermal conductivity of the polymeric materials used to form the card. [0017] In addition, the thermal mass of the integrating card structure can extend thermal cycling times. Another potential problem of this approach is that if the card containing the sample wells is not seated precisely on the metal block, uneven well-to-well temperatures can be experienced, causing inaccurate test results. [0018] Another problem that may be experienced in many of these approaches is that the volume of sample material may be limited and/or the cost of the reagents to be used in connection with the sample materials may also be limited and/or expensive. [0019] As a result, there is a desire to use small volumes of sample materials and associated reagents. When using small volumes of these materials, however, additional problems related to the loss of sample material and/or reagent volume through vaporization, etc. may be experienced as the sample materials are thermally cycled. [0020] Another problem experienced in the preparation of finished samples (e.g., isolated or purified samples of nucleic acid materials such as DNA, RNA, etc.) of human, animal, plant, or bacterial origin from raw sample materials (e.g., blood, tissue, etc.) is the number of thermal processing steps and other methods that must be performed to obtain the desired end product (e.g., purified nucleic acid materials). [0021] One example is in the preparation of a finished sample (e.g., purified nucleic acid materials) from a starting sample (e.g., a raw sample such as blood, bacterial lysate, etc.). To obtain a purified sample of the desired materials in high concentrations, the starting sample must be prepared for PCR, after which the PCR process is performed to obtain a desired common PCR reaction product. [0022] The common PCR reaction product must then be prepared for, e.g., Sanger sequencing, followed by performance of the Sanger sequencing process. Afterwards, the multiplexed Sanger sequencing product must be demultiplexed. After demultiplexing, the finished Sanger sequencing product is ready for further processing. [0023] This sequence of events may, however, have occurred over days or even weeks. In addition, the technical nature of the processes requires highly skilled personnel to obtain accurate results. [0024] Over past decades molecular biologists have learned to characterize, isolate, and manipulate the molecular components of cells and organisms. These components include deoxyribonucleic acid (DNA), the repository of genetic information, ribonucleic acid (RNA). [0025] RNA is a close relative of DNA whose functions range from serving as a temporary working copy of DNA to actual structural and enzymatic functions as well as a functional and structural part of the translational apparatus and proteins, which are the major structural and enzymatic molecules of cells. [0026] Most of the bench-top experiments conducted by molecular biologists to characterize, isolate and manipulate these components are conducted in test tubes, and typically only one single reaction is conducted within each test tube. [0027] It is required to repeat such reactions, to ensure the accuracy and reliability of the test results as they are subject to experimental errors. The more replicates, the more accurate and reliable the results will be. However, variations in the results between test tubes can be significant. [0028] In the recent years, molecular biologists have explored the possibility of conducting more than one reaction in a single test tube. For example, in the field of polymerase chain reactions (PCR), multiplex reactions using molecular beacons or probes have been developed so that the amplification of more than one target gene can be conducted at the same time within a single test tube. However, it is still necessary to replicate these multiplex experiments. [0029] Other molecular biology experiments such as DNA extraction or purification techniques comprise of several steps. For example, the most standard protocol to perform DNA extraction is to conduct at least the steps of cell lysis, washing and elution of the extracted DNA in water. (Other methods of extracting the DNA could be used, e.g., by cutting the cells to pieces with nano blades in a suitable biochip device.) [0030] In physical disruption methods, the cell membrane is physically broken down by shear or external forces to release cellular components. Although physical methods have traditionally been used to disrupt cells, there are some inherent disadvantages to their use. [0031] Localized heating within a sample can occur with many of the techniques described, leading to protein denaturation and aggregation. With homogenization and grinding methods can be challenging due to inexact terminology used to define sample handling. [0032] Cells disrupt at different times, so the viscosity of the medium constantly changes and released subcellular components are subjected to disruptive forces. In addition to sample handling problems, some physical disruption methods require equipment, such as the French press and sonicator. [0033] Detergent or solution-based cell lysis is a milder and easier alternative to physical disruption of cell membranes, although it is often used in conjunction with homogenization and mechanical grinding when preparing protein samples from tissues to achieve complete cell disruption. [0034] Detergents break the lipid barrier surrounding cells by solubilizing proteins and disrupting lipid-lipid, protein-protein, and protein-lipid interactions. Through empirical testing by trial and error, different detergent-based solutions composed of particular types and concentrations of detergents, buffers, salts, and reducing agents have been developed to provide the best possible results for particular species and types of cells. Detergents have both lysing and solubilizing effects. [0035] The different lysis approaches can e.g., be the following categories: chemical, mechanical, electrical methods, thermal, laser, heat, and other lysis methods e.g., by causing an endothermic reaction near the cell sample. [0036] High temperatures and pressures break the chemical bonds within cell walls, but also denature proteins and is therefore a quick and dirty cell lysis method. But it goes without saying that you should avoid this method if your sample is denatured by heat. [0037] According to prior art US7521246B2 there is provided a cell lysis method including: preparing a cell sample to be lysed; heating the cell sample; and cooling the cell sample by causing an endothermic reaction near the cell sample. In the method, the heating and the cooling may be repeated at least twice. [0038] In the method, the heating may be performed using any method, for example, using heat generated during the exothermic reaction. The heating temperature may be 90° C. or higher and 100° C. or lower, and the cooling temperature may be as low as possible, for example, 30° C. or lower and −30° C. or higher. [0039] US7521246B2 also describes how: Any cell can be lysed according to the US7521246B2 invention without limitation. The kinds of cell samples that can be used include a cell suspension containing microorganism strains, a sample including somatic cells of human, etc. The cell lysis method is proved to be effective in cell lysing gram positive bacteria, such as Bacillus substilus, Bacillus Megatrium, etc., which cannot be easily lysed by a general heating method. [0040] Cell lysis is a process in which the outer cell membrane is broken to release intracellular constituents in a way that important information about the DNA or RNA of an organism can be obtained. [0041] Typically, the cell lysis reaction is conducted in a first test tube. The cell lysate is then poured into another test tube for binding, washing and/or elution. Further purification steps may be conducted in yet another test tube. [0042] The transferring of the sample from one test tube to the other may result in undesirable loss in the DNA as some of the DNA may be left behind in the previous test tube or may be accidentally spilled during the transfer. [0043] Therefore, there is a need to provide a method for conducting more than one reaction, such as replicates of the PCR reactions or all the steps of DNA extraction and purification or the combination thereof, in an integrated test device that overcomes, or at least ameliorates, one or more of the disadvantages described above. [0044] Nucleic acid-based diagnostics is by far the most accurate and scientifically validated method for determining the presence of a potential pathogen in a clinical sample. [0045] Polymerase chain reaction (PCR) is one of the well- known nucleic acid-based techniques for use in amplifying deoxyribonucleic acid (DNA) by using primers that are complementary to the DNA region targeted for amplification under specific thermal cycling conditions i.e., alternately heating and cooling the PCR sample to a defined series of temperature steps. [0046] These thermal cycling steps include at least a denaturing step to physically separate the strands of double stranded DNA at very high temperature, typically about 94 to 96 degree C, to produce single stranded DNA, an annealing step to bind the primers to the target region on the single stranded DNA at lower temperature, typically about 50 to 60 degree C, and a replicating step to synthesize and thereby amplify the target DNA at a higher temperature, typically about 70 to 74 degree C. [0047] The thermal cycling process as described above must be repeated a number of times, typically for at least 20 to 35 cycles, to reach the level of amplification necessary to allow detection of the amplified target. [0048] Therefore, the main disadvantage in using the PCR technique is the high amount of time consumed in the inefficient thermal cycling process. [0049] Rapid portable DNA diagnostics is in demand since the world is facing the threat of potential pandemic events such as covid and new and unknown viruses in particular, rapid diagnostics critical to quickly finding and isolating infected individuals. [0050] Currently, PCR reaction vessels, for example capillaries, are in cassettes which are not in direct thermal contact with the thermal blocks. This results in inefficient heating of the reaction vessel and a decreased rate of heat change. This also results in inefficient energy consumption. [0051] There is a need to provide a device or method for conducting PCR reactions that overcome, or at least ameliorates, one or more of the disadvantages described above. [0052] DNA Separation by Silica Adsorption is an important method of DNA separation that is used in novel technologies that use micro-channels. The principle behind this type of separation relies on DNA molecules binding to silica surfaces in the presence of certain salts and under certain pH conditions. [0053] Conventional methods for DNA extraction, such as centrifugation with ethanol or preparations using commercial purification kits, are hard integrated onto microchips because they require multiple hands-on processing steps. [0054] In addition, they also require large equipment and high volumes of reagents and samples. DNA extraction on microchips provides a fast, cost effective, and effective for high-throughput screening, which also has a very small footprint. This new method has useful applications for biosensors, “lab on a chip” devices, and other new technologies that require rapid, high-quality DNA at minimal cost. [0055] Basic steps of this purification method: ^ The sample is run through a micro-channel. ^ DNA binds to the channel, and all other molecules remain in the buffer solution. ^ The channel is washed of impurities. ^ An elution buffer removes the DNA from channel walls, and the DNA is collected at the end of the channel. [0056] A sample (this may be anything from purified cells to a tissue specimen) is placed into the chip and lysed. The resultant mix of proteins, DNA, phospholipids etc., is then run through the channel where the DNA is adsorbed by silica surface in the presence of solutions with high ionic strength. [0057] The highest DNA adsorption efficiencies are shown to occur in the presence of buffer solution with a pH at or below the pKa of the surface silanol groups. Although the exact mechanism for this interaction is not well understood, one possible explanation involves reduction of the silica’s surface’s negative charge due to the high ionic strength of the buffer. [0058] This decrease in surface charge leads to a decrease in the electrostatic repulsion between the negatively charged DNA and the negatively charged silica. Meanwhile, the buffer also reduces the activity of water by formatting hydrated ions. This leads to the silica surface and DNA becoming dehydrated. These conditions lead to an energetically favorable situation for DNA to adsorb to the silica surface. [0059] This allows positively charged ions to form a salt bridge between the negatively charged silica and the negatively charged DNA backbone in high salt concentration. [0060] The DNA can then be washed with high salt and ethanol, and ultimately eluted with low salt. After the DNA is adsorbed to the silica surface, all other molecules pass through the column. Most likely, these molecules are sent to a waste section on the chip, which can then be closed off using a gated channel or a pressure- or voltage-controlled chamber. [0061] The DNA is then washed to remove any excess waste particles from the sample and then eluted from the channel using an elution buffer for further downstream processing. [0062] Methods using silica beads and silica resins have already been created which successfully isolated DNA molecules which can then be PCR amplified. However, these methods have a few problems associated with them. [0063] First, beads and resins are highly variable depending on how well they are packed and are thus hard to reproduce. Each loading of a micro-channel can result in a different amount of packing and thus change the amount of DNA that adsorbed to the channel. Furthermore, these methods result in a two-step manufacturing process. [0064] Silica structures are a much more effective method of packing material because they e.g. can be etched into the channel during its fabrication and is thus the result of a one-step manufacturing processes via e.g. soft lithography. Silica structures are therefore easier to use in chip designs since beads or resins don’t need to be introduced post manufacturing the chip. [0065] Piezoelectricity is the effect of mechanical strain and electric fields on a material; mechanical strain on piezoelectric materials will produce a polarity in the material, and applying an electric field to a piezoelectric material will create strain within the material. When pressure is applied to a piezoelectric material, a dipole and net polarization are produced in the direction of the applied stress. [0066] An induction heater consists of an electromagnet and an electronic oscillator that passes a high frequency alternating current (AC) through the electromagnet. The rapidly alternating magnetic field penetrates the object, generating electric current inside the conductor called eddy currents. [0067] The eddy currents flow through the resistance of the material and heat it by Joule heating. In ferromagnetic and ferrimagnetic materials, such as iron, heat also is generated by magnetic hysteresis losses. [0068] The frequency of the electric current used for induction heating depends on the object size, material type, coupling (between the work coil and the object to be heated), and the distance/penetration depth. [0069] An important feature of the induction heating process is that the heat is generated inside the object itself, instead of by an external heat source via heat conduction. The objects can be heated very rapidly and in addition, there is no need for external contact e.g., where contamination is an issue. [0070] Having self-controlling low Curie temperature magnetic material for induction heating based on compounding mix. The magnetization decreases with increasing number of additives thereby controlling the saturation magnetization. The compositions of e.g., alloys can be mixed to realize a given Curie temperature. [0071] The principle of the self-controlling-temperature moderator function is as follows: In electromagnetic induction heating, the magnetic flux generated by the high-frequency work coil passes through the heating material in a ferromagnetic phase at a predetermined temperature. Thus, eddy currents flow in the material. The material is heated by the eddy current losses. [0072] Since the Curie point of the developed material is predetermined, the saturation magnetization and the magnetic permeability decrease gradually with increasing temperature and the ferromagnetic property vanished within in the predetermined temperature range. [0073] At the same time, the linkage flux and the eddy currents decrease, and the heating energy is also reduced due to the lower inductance. The exciting current increases inversely; however, it is usually controlled to remain below the limitation current of the inverter. As a result, the temperature of the material decreases slowly. [0074] As the temperature falls below the predetermined temperature range, the ferromagnetic property recovers, and the eddy currents increase. Therefore, it is possible to keep the material temperature constant under a safe value depending on the Curie point without control. This sensor less control gives high reliability operation and safe use of the heating device. [0075] The roots of microfluidics are to be found in three main different fields: microanalysis, biodefence and – obviously – microelectronics. Microfluidics was first applied in microbiology as a tool for analytical analysis as it allows to operate with very small volumes of samples and reagents, which is quite a compelling feature for microanalysis. [0076] The possibility to implement several functions in a small and yet cheap device, dramatically increased the popularity of microfluidics-based applications in this branch. Moreover, as with many other scientific fields, research for military purposes stimulated a lot of effort on the development of microfluidics technology as a tool of defense against potential bacteriological threats were government institutions, such as the DARPA (Defense Advanced Research Projects Agency), commissioned microfluidics systems for fast in-situ detection. [0077] Fluids inside microchannels of microfluidic devices gain new features at this scale. One of the most important examples is laminar flow, i.e., a regime in which viscosity-related effects are more important than inertial ones. [0078] Laminar flow has several implications on how fluids are handled in microfluidic devices. In this regime fluids mix only via diffusion a rather slow mechanism and makes reactions within microfluidic devices harder to achieve. [0079] Clear weld allows the near infrared (NIR) and infrared (IR) laser welding of clear IR and NIR transparent plastics. Clear weld can be coated onto parts or used as an additive compounded into resins. [0080] While there are many established methods to weld plastics, each with its own advantages and disadvantages, Clear weld offers a dynamic, plastic welding technology to provide you with greater design, engineering, and manufacturing flexibility. [0081] The Clear weld is coated, leaving a green layer on the surface of the part. A second top part that is IR transparent is placed above the coated part and pressure is applied. The laser welds the two parts together, and when performed correctly, the Clear weld coating is both transparent and colorless. [0082] Magnetic attraction and repulsion are one of three fundamental non- contact forces in nature. The other two forces are electrostatic and gravitational. [0083] An inferred contactless temperature sensor that is activated triggers, that light bounces off the surface of the object and detects radiation emitted from the object. The thermometer then infers the temperature based on that electrical emission with impressive accuracy. Quality non-contact thermometer has an accuracy of ± 0.3 °C / ± 0.5 °F. [0084] A Centrifuge for centrifugation is one of the most common pieces of equipment used to separate materials into subfractions in a biochemistry lab. A centrifuge is a device that spins liquid samples at high speeds and thus creates a strong centripetal force causing the denser materials to travel towards the bottom of the centrifuge tube more rapidly than they would under the force of normal gravity. Often used to separate plasma and white blood cells from cloth and red blood cells in a centrifuge tube. SUMMARY OF THE INVENTION [0085] This invention concerns a method of contactless heating of a preferably inductive heat-able material preferably in a disposable reaction fluid device for biologic sampling. [0086] Induction heating is an accurate, fast, repeatable, efficient, non- contact technique for heating metals or any other electrically conductive materials. [0087] At least one inductive heat-able material is positioned/introduced in a disposable reaction fluid device where also a biologic sample is introduced. The inductive heat-able material is then exposed to inductive heating and heated up to one or more temperatures during the processing of the biologic sample. [0088] This inductive heat-able material in a disposable reaction fluid device could be movable and/or placed stationary positions where the biologic is movable by capillary, gravity, magnetic, centrifugal and/or other force moving the biologic sample through the device. [0089] The following STEP 1, 2 and 3 will be used to identify areas of improvement according to the inventions described herein. [0090] Step 1: Device designed to perform DNA extraction at least to the steps of cell lysis, washing and elution of the extracted DNA in water. The sample materials may be placed in at least one process chamber for e.g. a DNA extraction by breaking the cells open, commonly referred to as cell disruption or cell lysis, to expose the DNA within. Removing membrane lipids and proteins by adding a detergent and/or protease and precipitating the DNA with an alcohol e.g. ethanol or isopropanol since DNA is insoluble in these alcohols and thereby isolating the DNA. Other lysis methods could also be used in this first step e.g., chemical, mechanical, electrical methods, thermal, laser, ultrasonic, heat, and other lysis methods e.g., by causing an endothermic reaction near the cell sample. [0091] Step 2: After the isolation of the DNA, the DNA is exposed to PCR process in at least one but preferably followed by and/or in a plurality of process chambers in the device, where also the necessary ingredients like fluorescent color and primer are added to the fluid that holds the DNA either in liquid and/or dry formula along with the required heating and/or cooling of the sample materials. Creating selectivity of PCR results from the use of primers that are complementary to the DNA region targeted for amplification under specific thermal cycling conditions. [0092] Step 3: An improved system features a broad spectrum of light source that offers maximum flexibility in selecting fluorescent chemistries and the new filter based optical design allows selection of the optimal wavelengths of light for excitation and emission, resulting in excellent sensitivity and discrimination between multiple fluorophores and/or detection in sequential, parallel, and combined form. [0093] The preferred use of LEDs generating a blue light at a wavelength preferably of ~470 nm in real-time and/or end point PCR ensures an early detection e.g., through an optical lens and/or fiber combined with a unique new reflector/parabolic system/surface implemented in one or more of the reaction wells of the device. The fiber optical switch aligned with the detector and/or the patriated filter allows for simultaneous and/or constant imaging/detection creating a much earlier and faster detection. [0094] These selected process step and the advantages mentioned above and/or below in any combination or as stand alone may provide a variety of advantages over known sample processing methods, systems, apparatuses, and devices. [0095] Other objectives and aspects of the invention will become apparent from the following detailed description, taken in conjunction with the accompanying drawings, which illustrate, by way for example, the features in accordance with embodiments of the invention. [0096] To the accomplishment of the above and related objects, this invention may be embodied in the form illustrated in the accompanying drawings, attention being called to the fact, however, that the drawings are illustrative only, and that changes may be made in the specific construction illustrated and described within the scope of the appended claims. [0097] Although, the invention is described above in terms of various exemplary embodiments and implementations, it should be understood that the various features, aspects, and functionality described in one or more of the individual embodiments are not limited in their applicability to the particular embodiment with which they are described, but instead can be applied, alone or in various combinations, to one or more of the other embodiments of the invention, whether or not such embodiments are described and whether or not such features are presented as being a part of a described embodiment. Thus, the breadth and scope of the present invention should not be limited by any of the above-described exemplary embodiments. [0098] The presence of broadening words and phrases such as “one or more,” “at least,” “but not limited to” or other like phrases in some instances shall not be read to mean that the narrower case is intended or required in instances where such broadening phrases may be absent. BRIEF AND DETAILED DESCRIPTION OF DRAWINGS [0099] The accompanying drawings illustrate various embodiments of systems, methods, and embodiments of various other aspects of the disclosure. Any person with ordinary skills in the art will appreciate that the illustrated element boundaries (e.g., boxes, groups of boxes, or other shapes) in the figures represent one example of the boundaries. [00100] It may be that in some examples one element may be designed as multiple elements or that multiple elements may be designed as one element. In some examples, an element shown as an internal component of one element may be implemented as an external component in another and vice versa. [00101] Furthermore, elements may not be drawn to scale. Non-limiting and non-exhaustive descriptions are described with reference to the following drawings. The components in the figures are not necessarily to scale, emphasis instead being placed upon illustrating principles. [00102] Furthermore, the drawings may contain text or captions that may explain certain embodiments of the present invention. This text is included for illustrative, non-limiting, explanatory purposes of certain embodiments detailed in the present invention. [00103] In the drawings: Embodiments of the invention are described with reference to the following figures. The same numbers are used throughout the figures to reference like features and components. The features depicted in the figures are not necessarily shown to scale. Certain features of the embodiments may be shown exaggerated in scale or in somewhat schematic form, and some details of elements may not be shown in the interest of clarity and conciseness. [00104] For the accomplishment of the above and related objects, this invention may be embodied in the form illustrated in the accompanying drawings, attention being called to the fact, however, that the drawings are illustrative only, and that changes may be made in the specific construction illustrated and described within the scope of the appended claims. [00105] The accompanying drawings illustrate a disclosed embodiment and serves to explain the principles of the disclosed embodiment. It is to be understood, however, that the drawings are designed for purposes of illustration only in a simple form, and not as a definition of the limits of the invention. [00106] Fig. 1 Describing a top view of a turn-able/spinnable disposable reaction fluid device that could compare to a version of a disposable reaction fluid device showing a potential location of the chambers/wells, having options for different sample supply route, but also alternatives of lysis through nano blades and/or filter areas. The disk/maze labyrinth having a center well ready to receive and/or containing an inductive heat-able disk for the thermal cycling process. [00107] Fig. 2 Describing a different view of the turn-able/spinnable disposable reaction fluid device. [00108] Fig. 3 Describing the closure/lid preferrable in a clear material in whole or in part for the turn-able/spinnable disposable reaction fluid device with the retaining/distance pins/points for the inductive heat-able disk for the thermal cycling process. [00109] Fig. 4 Describing a version of the inductive heat-able disk for the thermal cycling process. [00110] Fig.5 Describing another version of the inductive heat-able disk for the thermos cycling process potentially having a silica coated and/or laminated surface for attracting/holding e.g., isolated, or purified samples of nucleic acid materials such as DNA, RNA, etc. [00111] Fig.6 Describing a round ball version of an inductive heat-able e.g., silica coated and movable carrier for the thermal cycling process. [00112] Fig.1 shows a top view of a turn-able/spinnable disposable reaction fluid device A. having multiple chambers/wells B. positioned around a distribution well/trench having access canals D. and E. connecting to both the center well F. and the that also is the main thermal reaction area options for different sample supply route, but also alternatives of lysis through nano blades and/or filter areas. The disk/maze labyrinth having a center well ready to receive and/or containing an inductive heat-able disk for the thermal cycling process that amplifies/copies e.g., DNA and RNA through a thermal cycling process. [00113] Fig.2 shows a different view of the turn-able/spinnable disposable reaction fluid device A. here a biologic sample be introduced along with process fluids e.g., already purified DNA or blood or plasma derived from blood in need of a lysis process could be introduced into the center well F. where an inductive heat- able disk for the thermal cycling process E. (shown in Fig 4.) also would be present and capable of thermal cycling and/or a lysis process exposing the DNA by causing at least endothermic reaction near the cell sample by exposing the biologic sample to inductive heating and cooling e.g., by releasing pressurized CO2 and/or Nitrogen gas or other cooling agents to the reaction fluid device. [00114] If lysis is part of the process the disposable reaction fluid device A. would then be spun around its center axis being pushed through filter and/or nano blade canal D. that would then retain ruptured cell wall and other debris from the lysis process letting the smaller DNA samples through to the distribution canal C. the distribution canal C. could be at a higher elevation in the device resulting in the sample fluid with DNA then returning to the center well F. when the spinning of the device slowed down and/or stopped. [00115] Here in the center well F. thermal cycling could be performed and/or started for the amplification/copying of the DNA having cooling cycles preformed e.g., by spinning the DNA containing fluid out into the distribution well C. and back. In the spinning process the access canals E. could be opened and/or closed e.g., by turning the lid H. (not shown in this drawing) having valve/open/close capabilities having the DNA containing fluid distributed to the outer wells B. for further processing. [00116] Each outer well e.g., being prepacked with process material and/or containing an inductive heat-able material/surface for an additional thermal cycling processing followed by an optical detection of the processed result. The turn- able/spinnable disposable reaction fluid device A. could also move/turn in steps exposing each outer well to multiple process areas like e.g., an inductive heating station, a cooling station, an optical detection station a temperature station that all could be in different or combined in stations when appropriate. [00117] Fig.3 shows the closure/lid preferrable in a clear material in whole or in part for the turn-able/spinnable disposable reaction fluid device with the retaining/distance pins/points for the inductive heat-able disk for the thermal cycling process. The lid H. could also have the ability to enable the access canals to be opened and/or closed e.g., by turning the lid H. (not shown in this drawing) thereby enabling valve/open/close capabilities for access to the outer wells B. [00118] Fig.4 shows a version of the inductive heat-able disk for the thermal cycling process can be seen E. having a centering hole I. through its thermal heating capabilities the disk can be used for lysis and/or amplification/copying e.g., DNA and RNA. It can also be used as a carrier from a separate lysis process whereby having a silica coated and/or laminated surface for attracting/holding e.g., isolated, or purified samples of nucleic acid materials such as DNA, RNA, etc. and can be placed disposable reaction fluid device A. for further PCR processing. [00119] Fig.5 shows another version of the inductive heat-able disk for the thermos cycling process can be seen potentially having a silica coated and/or laminated surface that also could be silica printed/decorated for attracting/holding e.g., isolated, or purified samples of nucleic acid materials such as DNA, RNA, etc. [00120] Fig. 6 shows a ball yet another version of an inductive heat-able carrier that could be silica coated and movable e.g., by magnetism through a disposable reaction fluid device not shown on the drawing being like a labyrinth/maze with multiple wells having distancing points for an even fluid distribution of the sample fluids by the ball during the lysis and/or amplification/copying e.g., DNA and RNA through a thermal cycling process. Detailed Description of the Preferred Embodiments [00121] In a preferred embodiment the disposable reaction fluid device would have a circular positioned wells around a center where at least one well position was inductive heat-able part that e.g., being a stationary and/or movable insert/carrier for the sample thermal processing. [00122] When ready the devise would spin using centrifugal force to help move the sample fluids into the distribution well and/or outer reaction wells and/or move in steps introducing each well to the inductive heating source e.g., with different energy and/or time exposure. The device could e.g., also have a grading where the spinning of the device would force the fluid sample away from the heating source enabling a faster cooling e.g., in the distribution well and at a lower spinning and/or stop of the spinning the fluid sample would run back into the heating well area. [00123] In another embodiment the disposable reaction fluid device would have circular positioned wells around a center well that e.g., was capable of blood separation using centrifugal force and at a following step to help move the processed sample fluids into one or more reaction wells also using centrifugal force spinning the device. [00124] In another embodiment the disposable reaction fluid device would have circular positioned wells around a center well that e.g., was capable of a lysis process exposing the DNA e.g., by chemical, mechanical, electrical methods, thermal, laser, ultrasonic, heat, or other lysis methods. [00125] In another embodiment the disposable reaction fluid device would have circular positioned wells around a center well that was capable of thermal cycling and/or a lysis process exposing the DNA by causing an endothermic reaction near the cell sample by exposing the biologic sample to inductive heating and cooling by releasing pressurized CO2 and/or Nitrogen gas into and/or onto the reaction fluid device e.g., combined by spinning sequences where the biologic sample was driven through nano blades and/or a filter trap by the centrifugal force the sample fluid returning to the center well whenever the device slowed and/or stopped spinning. [00126] Connecting a heat/temperature sensor preferably contactless like an inferred temperature sensor and an inductive heating unit from the PCR apparatus thereby creating a contactless heating zone controllable by the following variables: Heat applied to inductive heating and by having heat censors and e.g., a defined conductive compound material mix it is now possible to be in total temperature control of the PCR process having the DNA containing fluid peaking in heat delivered conductive carrier ball/disk and later cooling down e.g., by releasing pressurized CO2 and/or Nitrogen gas to the disposable reaction fluid device. [00127] This ensures that the entire DNA containing fluid reaches its high and low temperatures while undergoing a constant and repeatable procedure enabling some of the fastest and reliable PCR cycle and detection rates in the industry. [00128] DNA extraction process according to the invention can be controlled by means of a silica coated conductive heat-able part e.g., a disk, ring, sphere, ball, carrier ball, or other device capable of receiving and/or holding and delivering and/or returning the sample material during cell lysis having a defined area of silica or similar surface that binds DNA enabling the DNA from the biologic sample to be collected. [00129] The amount of DNA collected e.g., being determined by the size and/or surface priming of the area that attracts the DNA thereby only collecting the necessary amount of DNA from a sample and thereby enabling multiple extractions of DNA from the same sample material. [00130] Consequently, it will be possible to collect the right amount of DNA that is needed from a sample material eliminating the inconsistently that up till now have been created by of the difference in amount of DNA that is contained in the actual sample material. [00131] In another preferred embodiment of the invention the silica or similar surface that binds DNA has predetermined surface, pattern, shape and/or primer that enables it to control the amount of DNA and/or even identify and attract specific targeted DNA that it wants to attract and bind to its surface and/or the release time of the DNA at a later point in time. [00132] A version of the process according to the invention could work as follows: [00133] First having a container/process chamber that receives and/or contains both sample material and a suitable fluid where a DNA extraction can take place by breaking the cells open, commonly referred to as cell disruption or cell lysis, to expose the DNA within. [00134] Applying the fluid containing the exposed DNA to the silica coated conductive part, carrier ball/disk or other transportation silica coated vehicle enabling the DNA to attach itself to its silica surface and then introduce it to the disposable reaction fluid device and the fluid composition in the disposable reaction fluid device. [00135] A version of the process according to the invention could work as follows: Placing the disposable reaction device in a PCR apparatus having a receiving location and an electromagnetic activator designed to move the conductive carrier ball forth and back in the disposable reaction device at a controllable/programmable pace thereby moving the conductive carrier ball from one chamber/well to another exposing the biologic sample to inductive heating and cooling e.g., by releasing pressurized CO2 and/or Nitrogen gas to the reaction fluid device. [00136] Having a dome shaped chamber/well getting loaded with a heat-able ball shaped e.g., glass/silica coated conductive core will by gravity force spread a fluid sample evenly over a large contact surface especially if the dome shaped chamber/well have distancing ribs/and/or points holding the ball shaped glass/silica coated conductive core in place preventing full contact to the dome surface thereby enabling a large surface contact area on a small sample. [00137] In an embodiment of the invention the inductive heat-able material is designed to be a movable carrier moved by contactless magnetic force that is getting contactless inductive heated to a certain temperature at given positions e.g., in a reaction and/or cleaning well in the device. [00138] This disposable reaction fluid device having at least one chamber/well and/or zone being prepacked/preloaded with reactions solutions dry and/or wet e.g., having cleaning fluid and/or activation fluid prepacked/preloaded. [00139] In an embodiment the disposable reaction fluid device would have a have multi-layer/sandwich layer of chambers/wells and/or zones on top of each other separated with a breakable/penetrable membrane/valve and/or a mechanical open/closed position e.g., by mowing lid and base in different/opposite directions. [00140] The membrane/valve separating the different layers of the reaction fluid device could be as simple as tinfoil breakable by a magnetic movable carrier vessel e.g., a ball that is breaking the foil by the pull and/or push of the magnetic force and/or a membrane melting open enabled by the inductive heat of the carrier vessel and/or a clear weld laser solution. [00141] In another embodiment the disposable reaction fluid device would have circular positioned wells around a center well that was inductive heat-able for the sample processing. When ready the devise would spin using centrifugal force to help move the sample fluids into the outer reaction wells. [00142] Also using hydrophobic and/or hydroscopic surfaces e.g., in combination with centrifugal force spinning a microfluid device to help move and direct the sample material through the microfluid device. [00143] A version of the process according to the invention could work as follows: Light source and detection of the DNA during and/or after the PCR process makes step two and three, closely connected through the operation of the apparatus and could work as follows: Besides the magnet moving the conductive carrier ball and inductive heating source the reaction fluid device disposable the apparatus also have both a light source and detection unit ensuring detection e.g., of DNA with fluorescent die attached. [00144] This is achieved by pointing a LED generating a blue light at a wavelength preferably of ~470 nm in real-time and/or end point PCR ensures an early detection through the optical lens, filter and detector combined with a unique new reflector system. The optical lens aligned with the filter and the detector allows for simultaneous and/or constant imaging/detection creating a much earlier and faster detection. [00145] At least one LED generating a blue light is directed towards the transparent detection area e.g., a dedicated chamber/well position where the turn- able/spinnable disposable reaction fluid device could turn to/under in steps detecting at least one well at the time ensuring an early detection of the DNA through the stationary optical lens, filter and detector directed at the same point in the glass capillary as the LED. [00146] This combined with the fact that the PCR treated DNA fluid is passing by in a swiveling current reflecting light in all directions and a unique new reflector system on the back of the glass capillary that catches the DNA reflection light and direct it all towards the stationary optical lens, filter, and detector. The efficiency of the early detection e.g., done in parallel with the thermal cycling potentially enabling an adjustment of the number of thermal cycling performed during the detection and/or thermal cycling process. [00147] In an advanced version of the apparatus, the detection would occur through multiple optical fibers combined with a unique new reflector system that would cover each detection area and reflect back to the detector and e.g. also having a lens and a reflector/parabolic arrangement to concentrate the LED light into e.g. resembling a laser light, and a fiber optical switch aligned with the detector allow for simultaneous and/or constant imaging/detection at multiple points or channels creating a much earlier and faster detection. [00148] The optical detection module/detection system consists of the optical module housing and the primary detection components include emission filter/filters, an image intensifier, and a detector. The intensifier increases the light intensity of the fluorescence without adding any electrical noise and allows very discrete quantization of the fluorescence in the chambers and/or channels. [00149] Fluorescent light from the chambers and/or channels passes through the emission filter and intensifier and is then detected by the detector. The detector can simultaneously and/or individually collects light from multiple fluorophores in multiple chambers and/or channels and separate the signals into those of the individual fluorophores. This allows monitoring of multiple amplifications simultaneously in the same PCR process. [00150] Each chamber/well can hold dedicated primer/primers in dry and/or liquid form as well as fluorescent dye/dyes in dry and/or liquid form. [00151] Each chamber/well of the reaction fluid device can hold at least one dedicated sample port that can be activated from the outside enabling the mix of DNA fluid, primer, and fluorescent dye e.g., through piercing the membrane that might be manufactured in connection with the separation membrane and/or another connection port suitable for loading of e.g., DNA fluid, primer, and fluorescent dye. [00152] In another embodiment of the invention a magazine/holding device for several reaction fluid devices. The chambers/wells of the reaction fluid device being preloaded and/or possible to load with dedicated substances for the PCR process e.g., primer/primers in dry and/or liquid form and maybe also fluorescent dye/dyes in dry and/or liquid form. [00153] Releasing the DNA containing fluid at a controlled pace while moving through chambers/wells of the reaction fluid device. The chambers/wells being preloaded and/or possible to load with dedicated substances for the PCR process e.g., primer/primers in dry and/or liquid form and maybe also fluorescent dye/dyes in dry and/or liquid form. [00154] All and/or part of complete solution for the PCR process can also be delivered with the DNA containing fluid, but preferably there have to be at least on unique primer in preferably each chamber before the fluid is applied. [00155] One advantage of having small distance ribs and/or points in the process chambers the device during heating and/or cooling of the sample material in the process chambers is that it creates a faster and more uniform temperature given the even fluid sample layer around the heating source of the sample materials. [00156] Therefore, this feature could help to ensure a more uniform reaction of the sample materials in the process chamber during heating and/or cooling, an advantage that may be particularly significant where small volumes of sample materials and/or reagents are used. [00157] Another advantage may include enhanced heating and/or cooling through inductive heating and additional cooling by releasing pressurized CO2 and/or Nitrogen gas to the reaction fluid device during processing. As a result, the cooling of sample materials may be expedited e.g., by a controlled release of pressurized CO2 and/or Nitrogen gas to the reaction fluid device not relying solely on the surrounding temperature to provide for the removal of thermal energy from the sample materials. [00158] Another potential advantage of using inductive heating in the reaction fluid device as heating source of the sample material is that control over heating of sample materials in the process chambers may be enhanced. [00159] For example, increasing and/or decreasing the eddy current in the device may improve heating control by essentially damping the temperature increase of the sample material (by releasing pressurized CO2 and/or Nitrogen gas to the reaction fluid device cooling during and/or after the inductive heating process). [00160] Another potential advantage is that uniformity of sample material temperature in the different process chambers may also be improved by rotating the device during heating. For example, where heating and/or cooling is accomplished inside the process chamber on the axis of which the device is rotating, rotation can be helpful in preventing uneven heating. [00161] Other advantages of the devices and methods of the present invention include the ability to perform complex thermal processing on sample materials in a manner that reduces variability of the results due to human error. [00162] Further, with respect to the processing of biological materials for genetic amplification, this advantage may be achieved by operators that have a relatively low skill level as compared to the higher skill level of operators required to perform currently used methods. [00163] As discussed above, the thermal control advantages of the devices, methods and systems of the present invention may include chamber-to-chamber temperature uniformity, comparable chamber-to-chamber temperature transition rates, and the increased speed at which thermal energy can be added and/or removed from the process chambers. [00164] Among the device features that can contribute to these thermal control advantages are the inclusion of a reflective layer (e.g., metallic/conductive) in the device, baffle structures to assist in removing thermal energy from the device, and low thermal mass of the device. By including thermal indicators and/or absorbers in the devices, enhanced control over chamber temperature may be achieved even as the device is rotated and/or not during processing. [00165] In those embodiments that include connected process chambers in which different processes may be sequentially performed on a starting sample, the present invention may provide an integrated solution to the need for obtaining a desired finished product from a starting sample even though multiple thermal processes are required to obtain the finished product. [00166] In other embodiments in which the process chambers are multiplexed from a loading chamber (in which the starting sample is loaded), it may be possible to obtain multiple finished samples from a single starting sample. Those multiple finished samples may be the same materials where the multiplexed process chambers are designed to provide the same finished samples. Alternatively, the multiple finished samples may be different samples that are obtained from a single starting sample. [00167] For those embodiments of the devices that include distribution channels partly formed in a metallic/conductive layer, the ability of improved heating and/or cooling of the metallic/conductive layer may provide a further advantage in that it may be possible to design selected distribution channels to tailor the devices for specific test protocols, adjust for smaller sample material volumes, etc. [00168] It may also be advantageous to isolate the process chambers by closing and/or opening the distribution channels after distributing sample materials to the process chambers. [00169] For those embodiments that include a reflective layer forming a portion of each of the desired process chambers, the present invention may also provide the advantage of improved signal strength when the samples contained in the process chambers are monitored for fluorescent or other electromagnetic energy signals. [00170] The signal strength may be improved if the reflective (e.g., metallic) layer reflects the electromagnetic energy being monitored as opposed to absorbing the energy or allowing it to be transmitted away from a detector. [00171] The signal strength may be even further improved if the metallic layer is formed into a shape that acts as a focusing reflector (e.g., parabolic reflector). If electromagnetic energy used to interrogate and/or heat materials in the process chambers is reflected by the reflective layer, then that layer may also improve the efficiency of the interrogation and/heating processes by effectively doubling the path length of the electromagnetic energy through the sample materials in the process chambers. [00172] An advantage of those embodiments including filter chambers with capture plugs is that filtering material appropriate for the particular process being performed may be added at the point-of-use. For example, if the device is being used for genetic amplification, a filtering material designed to allow passage of nucleic acid materials of particular sizes may be delivered to the filter chamber before processing of the genetic materials. [00173] Advantages of those embodiments of the invention that include control patterns include the ability to control the delivery of electromagnetic energy to the device or detect changes in the process chambers, without requiring changes to the hardware and/or software used in the system employing the device. [00174] For example, the amount and/or wavelength of electromagnetic energy delivered to the process chambers and/or valves can be controlled using a control pattern on the device. Such control may further reduce the operator error associated with using the devices. [00175] As used in connection with the present invention, "thermal processing" (and variations thereof) means controlling (e.g., maintaining, rising, or lowering) the temperature of sample materials to obtain desired reactions. [00176] As one form of thermal processing, "thermal cycling" (and variations thereof) means sequentially changing the temperature of sample materials between two or more temperature set points to obtain desired reactions. Thermal cycling may involve cycling between lower and upper temperatures, cycling between lower, upper, and at least one intermediate temperature, etc. [00177] As used in connection with the present invention, the term inductive heating capable of being delivered from a source to a desired conductive material in the absence of physical contact. [00178] The present invention provides a method of conducting a thermal cycling process by providing a device including a plurality of process chambers/wells, each process chamber of the plurality of process chambers defining a volume for containing sample material, providing separate process chambers including a holding device for these. [00179] Furthermore a thermal structure; locating a first temperature transmitting surface of the silica coated carrier ball/disk of the device in contact with a controllable temperature transmitting surface, wherein at least some process chambers of the plurality of process chambers are in thermal communication when the a chamber/well of the reaction fluid device is in contact with the silica coated conductive carrier ball/disk enabling changing process temperatures based on level of eddy current that is delivered. [00180] The present invention provides a method of conducting a thermal cycling process by providing a device including a plurality of process chambers, each process chamber of the plurality of process chambers defining a volume for containing sample material; providing sample material in the plurality of process chambers; directing contactless inductive energy into the plurality of process chambers to raise the temperature of the sample material in the plurality of process chambers/wells; having stationary conductive heating inserts e.g. of different size and/or material composition thereby enabling different temperatures in the plurality of process chambers, wherein the temperature of the sample material in the plurality of process chambers/wells thereby be set at different temperature levels simply controlled by the different size and/or material composition when exposed to the same level of eddy current. [00181] In another aspect, the present invention provides a method of processing sample material by providing a device including at least one process chamber array that includes a loading chamber and a first process chamber; providing sample material in the at least one process chamber array, the sample material being provided in the loading chamber of the at least one process chamber for cell lysis; moving the collected DNA sample material from this chamber into a washing/cleaning cycle in at least one following process chamber before moving the ready DNA sample into at least one PCR process chamber. [00182] In another aspect, the present invention provides a method of processing sample material by providing a device including a plurality of process chamber arrays, each process chamber array of the plurality of process chamber arrays including a loading chamber and a first process chamber; providing sample material in at least one process chamber array of the plurality of process chamber arrays, the sample material being provided in the loading chamber of the at least one process chamber array; moving the sample material from the loading chamber to the first process chamber of the at least one process chamber array by moving the silica coated conductive carrier ball/disk that collects and deliver the DNA into the at least one process chamber array before raising the temperature for the first cycle of the PCR process. [00183] In another aspect, the present invention provides a device for processing sample material, the disposable reaction fluid device having at least one hydrophobic and/or hydroscopic surface in the device including a substrate that includes first and second suitable surfaces; a plurality of process chambers/wells. [00184] In another aspect, the present invention provides a device for processing sample material, the device including a substrate that includes first and second suitable surfaces; a plurality of process chambers/wells in the device, each of the process chambers defining a volume for containing a sample; and a control pattern on the device, the control pattern including at least one indicator associated with each of the plurality of process chambers/wells. [00185] In another aspect, the present invention provides a complete sample processing system including at least one but preferably multiple fluorescent protein colors in the same and/or separate process chambers/wells in the PCR process. [00186] In another aspect, the present invention provides a sample processing system having at least one container/process chamber that receives and/or contains both sample material and a suitable fluid where a DNA extraction can take place by breaking the cells open, commonly referred to as cell disruption or cell lysis, to expose the DNA within. [00187] Having filled/ filling the disposable reaction fluid device with the fluid containing the exposed and/or exposing the DNA enabling the DNA to attach itself to the silica surface of the conductive carrier ball/disk exposed in the fluid during the aqueous phases comprise at least one of: (i) a cell lysis solution; (ii) a washing buffer; (iii) an elution buffer and (iv) a polymerase chain reaction solution. Having a DNA wash machine preparing at least one DNA sample for a PCR process. [00188] Some of these aspects and other features and advantages of the devices, systems and methods of the invention are described below with respect to illustrative embodiments of the invention. [00189] Advantageously, the disclosed method can be used to conduct several different types of molecular biology techniques. [00190] The following words and terms used herein shall have the meaning indicated: The term "coupled" in reference to a glass/silica coated conducting carrier ball/disk being "coupled" to a chemical species includes both direct and indirect physical and chemical bonding between a glass/silica coated conducting carrier ball/disk and a chemical species. [00191] Chemical bonding covers both covalent and noncovalent bonding of the molecules of a chemical species and includes specifically, but not exclusively, covalent bonding, electrostatic bonding, hydrogen bonding and van der Waals' bonding. [00192] Chemical bonding may cover direct chemical bonding in which the molecules of a chemical species form bonds with the glass/silica coated conducting carrier ball/disk and indirect chemical bonding in which the molecules of a chemical species form bonds with another chemical species that in turn bonds to the glass/silica coated conducting carrier ball. [00193] Physical bonding refers to any attractive, nonchemical interaction which can hold a chemical species on the surface of the glass/silica coated conducting carrier ball/disk. The physical bonding may also be direct and indirect in that for direct physical bonding, the chemical species is physically bonded directly to the glass/silica coated conducting carrier ball/disk while in indirect physical bonding; the chemical species is bonded directly to another chemical species which is physically bonded to the glass/silica coated conducting carrier ball/disk. [00194] The term "glass/silica coated conducting carrier ball/disk " is to be interpreted broadly to include any glass/silica coated solid or compounded conductive materials of any shape that is capable of being inductive heated and/or coupled to a chemical species. And may be made of metal and/or plastic and/or glass or any combination hereof and being designed in any shape. [00195] Unless specified otherwise, the terms "comprising" and "comprise", and grammatical variants thereof, are intended to represent "open" or "inclusive" language such that they include recited elements but also permit inclusion of additional, unrecited elements. [00196] Throughout this disclosure, certain embodiments may be disclosed in a range format. The description in range format is merely for convenience and brevity and should not be construed as an inflexible limitation on the scope of the disclosed ranges. [00197] Accordingly, the description of a range should be considered to have specifically disclosed all the possible sub-ranges as well as individual numerical values within that range. This applies regardless of the breadth of the range. [00198] Exemplary, non-limiting embodiments of a method for conducting more than one reaction in an assembled reaction fluid device will now be disclosed. [00199] In one embodiment, the reactions comprise of nucleic acid extraction reactions. In one embodiment, the reactions comprise of polymerase chain reactions. The aqueous phases may comprise of a cell lysis solution, a washing buffer, an elution buffer, or a polymerase chain reaction solution. [00200] The means the glass/silica coated conducting carrier ball/disk may be moving at varying or constant speed, or a combination thereof. The amount of DNA needed in the chambers/wells and/or fluid used is taken into consideration to determine the speed of the movement of the glass/silica coated conducting carrier ball means such as to control the movement through the chambers/wells within the assembled reaction fluid device also going into as well as up from a chamber/well using the magnetic/electromagnetic force to contactless move the glass/silica coated conducting carrier ball/disk in and out of liquid baths in the disposable reaction fluid device. [00201] The polymerase chain reactions may include fluorescence protein dyes that may aid in the detection of the presence and/or amount of the nucleic acid present before, during and/or after completion of the reactions. The polymerase chain reactions may also be multiplex reactions. The fluorescence dyes employed may be SYBR Green, or molecular probes or beacons. [00202] In one embodiment, the disclosed system further comprises an optical detection means for detecting the presence and/or amount of nucleic acid in each of said immiscible phases. [00203] In one embodiment, the disclosed system further comprises separation between chambers/wells by high viscosity fluids that do not mix with the fluid in the chambers/wells in the disposable reaction fluid device. [00204] In one embodiment, the contact less temperature control of the inductive heating of the reaction fluid device having different compound composition and/or size of the conductive material in each chamber for selectively and independently controlling the temperature of the individual chambers during the PCR mode. [00205] The canals in the reaction fluid device could be spiral formed and may be generally circular in shape and may be configured to rotate about a central axis potentially with stops at the reaction chambers located in spiral of the reaction fluid device with respect to number of reaction chambers needed. [00206] In one embodiment, the first and second body parts are moveable relative to the other in one planar direction, such as by rotation. Accordingly, the size of device is relatively smaller when compared to any device wherein movement in more than one planar direction is required. [00207] It will be appreciated that the disclosed method allows for conducting of more than one physical or chemical reaction in an assembled disposable reaction fluid device. [00208] The disclosed method allows for the conducting of the same experiment in replicates, and yet avoids test tube to test tube variations which may significantly affects the accuracy and reliability of experimental results. Advantageously, positive and/or negative control experiments can also be included in the same assembled disposable reaction fluid device to further enhance the integrity of the experiments conducted therein. [00209] It will be appreciated that the disclosed methods can be used to conduct several different types of molecular biology experiments, such as polymerase chain reactions, DNA extraction and/or DNA purification. [00210] Advantageously, the disclosed method of a having a 2- or 3- dimensional kind of labyrinth maze where the glass/silica coated conducting carrier ball/disk travels from one chamber/well to another by contactless magnetic/electromagnetic force also eliminates the need to transfer experimental samples or reactions from one test tube to another. [00211] Parts/device according to the invention could also be magnetic and/or de-magnetized and/or re-magnetized during the operation of the equipment according to the invention. [00212] It will be apparent that various other modifications and adaptations of the invention will be apparent to the person skilled in the art after reading the foregoing disclosure without departing from the spirit and scope of the invention and it is intended that all such modifications and adaptations come within the scope of the inventions. [00213] It will be appreciated that the disclosed method allows for conducting of more than one physical or chemical reaction in a disposable reaction fluid device. [00214] In one embodiment, the temperature control means is thermally coupled to the second body part for selectively and independently controlling the temperature of the individual chambers during the PCR mode. [00215] The first body part may be generally circular in shape and may be configured to rotate about a central axis with respect to the second body part. [00216] In one embodiment, the first and second body parts are moveable relative to the other in one planar direction, such as by rotation. Accordingly, the size of device is relatively smaller when compared to any device wherein movement in more than one planar direction is required. [00217] In one embodiment, only the first body part is moveable. In another embodiment, only the second body part is moveable. In yet another embodiment, both the first and second body parts are moveable. [00218] In one embodiment, the means for moving the first body part comprises a motor coupled to the central axis of the first body part. In one embodiment, at least one of the first and second body parts rotates and/or moves at an adjustable speed. [00219] In one embodiment, the reaction is nucleic acid amplification reaction or polymerase chain reaction. The nucleic acid amplification reaction may be preceded by a reverse transcription step that converts RNA into DNA. Therefore, it is to be appreciated that the disclosed device may be used to amplify nucleic acid from various types of RNA such as viral RNA, messenger RNA and transporter RNA. [00220] In one embodiment, while the reactive sample is exposed to one of the reaction chambers/wells, the temperature in any of the other chambers can be adjusted to a different temperature based on controlling the different level of inductive heating energy levels contactless applied to the glass/silica coated conducting carrier ball/disk at a given position. [00221] In case of multi-layer fluid devices more than two layers fluid device the option of having induction heating from two sides and/or multiple positions e.g., in combination with different size and/or compound of the conductive material this configuration could enable multiple different heat zones at the same time. [00222] In one embodiment, while the reactive sample is exposed to one of the reaction chambers/wells, the temperature in any of the other chambers can be adjusted to a different temperature based on controlling the different level of laser energy levels contactless applied to the glass/silica coated conducting carrier ball/disk at a given position, and/or another conductive/heat absorbing material in the fluid device. [00223] In case of multi-layer fluid devices more than two layers fluid device a laser would need a clear window and/or contact point from the side of the fluid device to transfer heat. [00224] The reaction fluid devices could also have one or more surfaces that where hydrophobic and/or hydrophilic e.g., made by e.g., a fento laser in the production mold of such reaction fluid device or in the actual reaction fluid device before assembly. Additives in the plastic of the reaction fluid device could also help improve such a feature. [00225] In one embodiment, the device further comprises an optical detection unit that can detect the presence and/or amount of nucleic acid in the reactive sample before, during and/or after the reaction. [00226] In yet another aspect, the present invention a concentrated beam provides the assembly of the disposable reaction fluid device by the principles of clear welding where a laser beam will pass through a clear surface and hit a heat absorbing surface where it then will generate/release the heat. [00227] It can be compared to sunrays passing through a window without heating the glass but when it hits a heat absorbing material like a dark shirt it will release its heat. Heat absorbers can even be put in clear materials without deluding the visibility when looking through it. [00228] Given the current invention/inventions a number of possibilities arise in the design of the process chambers and on what surfaces therein the heat is released in the process chamber/well now benefitting from another contactless heating source than inductive heating benefiting from such a feature as explained earlier in the text above. [00229] In yet another aspect, the present invention the use of primers and/or fluorescent protein/dye in dry formulated form enables longer shelf time, easier handling and a possible delayed release that helps prevent cross contamination in sample fluids passing through multiple process chambers/wells e.g., when coated on a surface in the process chamber and/or in a coated pill form. Other additives in the PCR process can be delivered in a dry and/or liquid formulation as a mix and/or in separated form. [00230] In yet another aspect, the present invention the use of primers and/or fluorescent protein/dye in a liquid pill form enables longer shelf time, easier handling and a possible delayed release that helps prevent cross contamination in sample fluids passing through multiple process chambers/wells e.g. when preloaded in the process chamber ready for use and/or in a liquid pill form and/or similar liquid pill material used as cover on a chamber/well and/or opened by the inductive heating of the glass/silica coated conducting carrier ball/disk. [00231] In yet another aspect, the present invention having a silica surface that could attract and hold the exposed DNA during a wash procedure the center well having both a controllable inlet and/or outlet feature preferably keeping the access from the center well closed from the surrounding reaction wells until at least an initial thermal cycling have been performed on the now exposed DNA. [00232] In yet another aspect, the present invention having the DNA containing fluid peaking in heat delivered by a conductive carrier ball/disk and later cooling down e.g., by releasing pressurized CO2 and/or Nitrogen gas or other cooling agent to the disposable reaction fluid device thereby ensuring that the entire DNA containing fluid reaches its high and low temperatures while undergoing a constant and repeatable procedure enabling some of the fastest and reliable PCR cycle and detection rates in the industry. [00233] In yet another aspect, the present invention having a method for conducting at least one reaction within a assembled reaction fluid device, said system comprising: Having at least one of said assembled disposable reaction fluid device having at least one reaction phases for allowing a reaction to occur therein, and at least one glass/silica coated conductive area stationary and/or on a movable transport unit capable of being coupled to and/or holding a chemical species being moved contactless by a combination in part or in whole or as a stand-alone by e.g., capillary, gravity, centrifugal, heat explosion, mechanical or magnetic/electromagnetic force, wherein said transport unit is movable into said reaction phases to introduce said chemical species thereto; and at least one activator means for enabling the movement of and entering of said process chamber/well under a controlled and programmable speed having at least one transparent process chamber/well for inspection and/or other features. [00234] In yet another aspect, the present invention having a method wherein the at least one reaction zone in a assembled disposable reaction fluid chip, fluid chamber, fluid disposable or other suitable fluid device, said method comprising the steps of: providing in said fluid device at least one zone formed by respective reaction phases; providing in said fluid device at least one separation area moving up and out of a chamber/well using gravity of the fluids to clear the transport unit before going down to the next chamber/well containing fluids and/or membrane e.g. a high viscosity fluid that is immiscible with said reaction phases and which is disposed there between to thereby separate said reaction zones; and providing at least one glass/silica coated part, particle, nanoparticle comprises a conductive core, such as a metal, copper, aluminum, steel, or brass. [00235] It can also be a semiconductor such as graphite, carbon, silicon carbide, metal oxide or a compounded material that is introduced into a biological sample, in proximity and/or next to said biological sample this at least one glass/silica coated conductive transport unit capable of being coupled to and/or holding a chemical species. [00236] In yet another aspect, the present invention having a method comprising an optical detection device for improved detecting of the presence and/or amount of said chemical species in said reaction phases due to a parabolic reflector positioned in relation to the at least one process chamber and concentrating the reflection towards the optical detection device. [00237] In yet another aspect, the present invention having a method, first having a container/process chamber that receives and/or contains both sample material and a suitable fluid where a DNA extraction can take place by breaking the cells open, commonly referred to as cell disruption or cell lysis, to expose the DNA within by filling the container/process chamber with the fluid containing the exposed DNA enabling the DNA to attach itself to a silica or glass surface exposed to the fluid in the container. [00238] In yet another aspect, the present invention having a method where DNA is collected by exposing a defined size and/or composition of silica surface to exposed DNA after a cell lysis enabling the DNA to attach itself to the silica surface exposed to the fluid thereby enabling the collection of a repeatable number/volume of DNA from each sampling by introducing a new silica surface to the fluid. [00239] In yet another aspect, the present invention having a method wherein a controlled DNA collection is taken from a cell lysis solution by exposing a defined silica or similar DNA attraction surface area with a suitable surface design and/or coated with a selective primer enabling a repeatable and/or targeted DNA collection in a sample cell lysis solution. [00240] In yet another aspect, the present invention having a method wherein said aqueous phases comprise at least one of: at least one glass or silica coated transport unit; a cell lysis solution; a washing buffer; an elution buffer all combined in a wash machine device having elevation between the different chambers/wells the transport unit traveling like on a rollercoaster entering the chambers/wells on the low and exiting on the high positions through the different process steps of obtaining and processing a DNA sample. [00241] In yet another aspect, the present invention having a method wherein at least one cooling zone made of a compounded conductive plastic material having cooling distributed to the thermal cycling fluid through the outside cooling exposure of the plastic material and/or conductive surface going through the process chamber the surface being combined with a contactless heat-able conductive material. [00242] In yet another aspect, the present invention having a method wherein the contactless heating of a defined heating zone in the process chamber is done by the principles of clear welding where a laser beam or other concentrated energy source will pass through a clear surface without any significant heat absorption and hit a heat absorbing surface where it then will generate/release the heat. [00243] In yet another aspect, the present invention having a method wherein the assembled reaction fluid chip, fluid chamber, fluid disposable or other suitable fluid device have more than one layer of chambers/wells e.g., separated by a conductive layer/area e.g., a foil capable of being heated by inductive heating and/or a laser utilizing the principles of clear welding to open and/or close areas in the assembled disposable reaction fluid device. [00244] It will be apparent that various other modifications and adaptations of the invention will be apparent to the person skilled in the art after reading the foregoing disclosure without departing from the spirit and scope of the invention and it is intended that all such modifications and adaptations come within the scope of the appended claims. [00245] The abovementioned suggestions are meant to be used in both as standalone and in combinations and in part combinations not limited to any of the described technologies in creation of new patent claims for current and/or dependent patent applications.

Claims

CLAIMS 1. A method for selectively maintaining a biologic/reactive sample at different temperatures during the course of a reaction, in a disposable reaction fluid device comprising: At least one process chamber having a biologic/reactive sample introduced and then being thermal cycled in a PCR process by the heat from at least one contactless heat-able insert/area inside the disposable reaction fluid device, the insert/area containing an inductive heat-able material that when activated by an inductive heater can distribute the heat to the fluid through the contact surface of the at least one stationary and/or movable heat-able insert/area inside the disposable reaction fluid device.

2. The method as in claim 1, further comprising that the fluid of the biologic/reactive sample/containing the sample can be heated by a laser using the clear weld principals of a concentrated energy source that will pass through a clear surface without any significant heat absorption and hit a heat absorbing surface where it then will generate/release the heat inside the disposable reaction fluid device as a heat source for the thermal cycling or to open and/or close areas by heat in the assembled disposable reaction fluid device.

3. The method as in claim 1, further comprising that the fluid containing the biologic/reactive sample preferably is in direct contact with the heating element and preferably distributed evenly to the contact surface of the heat-able insert/area in the disposable reaction fluid device for improved control of the thermal cycling heating and cooling.

4. The method as in claim 1, further comprising the disposable reaction fluid device having wells/chambers evenly positioned around a center well/chamber preferably in a circular even spaced pattern and where at least one well/chamber is inductive heat-able during a heating step in the sample processing and when ready the devise would spin using centrifugal force to help move the sample fluids from the center well into a distribution well and/or into a following connected reaction well followed by having the disposable reaction fluid device moving around its center axis in steps introducing each well to a inductive heating source, temperature measurement, different energy and/or time exposure, and sample detection zones .

5. The method as in claim 1, further comprising the disposable reaction fluid device having circular positioned wells around a center well the center well connected by a distribution and/or cooling trench/well that would help an even distribution spinning the device using the centrifugal force as main distribution to the outer wells where primers and/or fluorescent protein/dye for the PCR process are located in dry, frozen and/or liquid formulated form in at least one process chamber/well.

6. The method as in claim 1, further comprising the disposable reaction fluid device would have circular positioned wells around a center well that is capable of a lysis process exposing the DNA by chemical, mechanical, electrical methods, thermal, laser, ultrasonic, heat, or other lysis methods like nano blades.

7. The method as in claim 1, further comprising the disposable reaction fluid device would have circular positioned wells around a center well that was capable of thermal cycling and/or a lysis process exposing the DNA by causing at least endothermic reaction near the cell sample by exposing the biologic sample to inductive heating and cooling by releasing pressurized CO2 and/or Nitrogen gas or other cooling agents to the reaction fluid device.

8. The method as in claim 1, further comprising the disposable reaction fluid device being capable of preforming cell lysis using centrifugal force in whole or in part by forcing the sample fluid through areas with nano blades and/or filters.

9. The method as in claim 1, further comprising connecting a heat/temperature sensor preferably contactless like an inferred temperature sensor and an inductive heating unit from the PCR apparatus thereby creating a contactless heating zone controllable by the following variables: Heat applied to inductive heating and by having heat censors and having the heat-able area/part made by a defined conductive compound material mix so it is now possible to be in total temperature control of the PCR process.

10. The method as in claim 1, further comprising a cooling option where the assembled disposable reaction fluid chip, fluid chamber, fluid disposable or other suitable fluid device is processed in a cooling enclosure during processing and/or having access to periodic cooling exposure liquid CO2 and/or Nitrogen or other cooling agent released to cool the assembled disposable reaction fluid chip, fluid chamber, fluid disposable or other suitable fluid device.

11. The method as in claim 1, further comprising an insertable silica coated carrier disk being introduced to the disposable reaction fluid device after it have been through a separate lysis process whereby having a silica coated and/or laminated surface for attracting/holding isolated, or purified samples of nucleic acid materials such as DNA, RNA, etc. and can be placed disposable reaction fluid device and transfer the samples for further PCR processing.