DOT CELLULAR AUTOMATA (QCA)

Field of the invention:

The present invention relates to a Portable Molecular Quantum Dot Cellular Automata (QCA) X-Ray System (1) and a novel method to generate X-ray waves by the application of Quantum Dot Cellular Automata based nanotechnology using said QCA X-Ray System(l) and its working thereof. The present invention reveals a novel method to radiate X-ray wherein the said QCA X-ray System (1) required very negligible amount of voltage and consumes very less amount of energy and power compared to conventional methods and systems to generate X-ray waves with same intensity.

Background of the invention:

One of the biggest discoveries in the 19th century was the discovery of X-ray by Wilhelm Rontgen. That time it was an unknown type of radiation and termed as X-radiation or X-ray. The existing convention for production of X-ray requires X-ray tube which is a vacuum tube that employs a high voltage [1] to accelerate the electrons released by a hot cathode plate. These high velocity electrons colliding with metal anode and radiate X-rays. While colliding with anode, electrons knock an orbital electron out of inner electron shell of anode atom. The electrons from higher energy level then fill up the vacancy and radiate X-ray. The existing conventional process of generating X-rays is inefficient with production efficiency of only one percent [2, 3]. The process encompasses good amount of power to produce the required flux of X-rays. Digital X-ray generator employs 440 VAC, 50/60 Hz supply with three to single phase transformer. Here around 80 KVA amount of power is generated during the process of X-rays generation. Most of this amount is lost and consumed by the tube as waste heat. The existing X-ray tubes are designed in such a way that they can dissipate the excess heat. Energy and power loss are big concerns while generating X-ray. Around 2500° C is generated in the existing conventional process of generating X-rays hence associated cooling system is imperative.

Existing conventional X-ray systems suffer from many drawbacks. The focal spot at anode may attain a temperature level of approximately 2500° C and anode assembly may reach a temperature of around 1000° C. They use a high voltage power source of approximately 150 kilo volt (kV) [17, 18]. Another major drawback observed in the existing generation methodology is that approximately about 1% of the energy is radiated as X-ray and the rest is released as heat [19, 20]. Our proposed system should overcome all the above major drawbacks.

Following prior arts depict a comparative study on existing and our proposed portable QCA X-ray system (1) and disclosed the superiority of the proposed portable QCA X-ray system (1) against the existing counterpart:

US20110280371 disclosed a device related generally to medical X-ray imaging and more particularly to a device for the generation of X-ray emission using titanium dioxide (Ti0 ₂ ) nanotubes. The main parameters in this prior art is as the supply voltage provided is in range of 60kV caused high operating temperature, power consumption of order 270kW, X-ray generation efficiency of 1 to 2%, while cooling system and vacuum chamber are present.

US20120207269 related to an X-ray generating device, an X-ray system and the use of an X- ray generating device in at least one of an X-ray system and a CT system. In particular, the present invention relates to an X-ray generating device having an electron scattering element. The main parameters in this prior art is as the supply voltage provided is in range of lkV anode voltage and 120kV cathode voltage caused high operating temperature, very high power consumption, X-ray generation efficiency of 1 to 2%, while cooling system and vacuum chamber are present.

US20120219118 related to an emission electron source using nano-structures as emitters and self-aligned and nano-sized gate aperture for low voltage control, the fabrication method thereof and its use in X-ray generator. The main parameters in this prior art is as the supply voltage is very high caused high operating temperature, power consumption in kW, X-ray generation efficiency of 1 to 2%, while cooling system and vacuum chamber are present.

US20120027173 disclosed an invention related to an electron emitter for an X-ray tube. Furthermore, the invention related to an X-ray tube comprising such electron emitter and to an X-ray image acquisition device comprising such X-ray tube. Furthermore, the invention related to a method of acquiring an image of an object e.g. by transmission radiography with X-rays, to a computer program element adapted for controlling such method when executed on a processor and to a computer-readable medium having such computer program element stored thereon. The main parameters in this prior art is as the supply voltage is lOkV/mm caused high operating temperature more than 1000 ^° C, power consumption in kW, X-ray generation efficiency of 1 to 2%, while cooling system and vacuum chamber are present.

US20110051895 refers to X-ray systems for use in high-resolution imaging applications with an improved power rating and, more particularly, to a variety of system configurations for an X-ray based image acquisition system using an X-ray source of the rotary anode type or, alternatively, an array of spatially distributed X-ray sources fabricated in carbon nanotubes (CNT) technology, thus allowing higher sampling rates for an improved temporal resolution of acquired CT images as needed for an exact reconstruction of fast moving objects (such as e.g. the myocard) from a set of acquired 2D projection data. The main parameters in this prior art is as the supply voltage is very high in range of 40kV to 160 kV caused high operating temperature, power consumption in kW, X-ray generation efficiency of 1 to 2%, while cooling system and vacuum chamber are present.

US7289602 disclosed a portable, self-contained, electronic radioscopic imaging system uses a pulsed X-ray source, a remote X-ray sensor, and a self-contained, display and controller unit to produce, store, and/or display digital radioscopic images of an object under investigation. The pulsed X-ray source transmits a burst of narrow pulses of X-rays at the object being investigated at a low repetition rate. The main parameters in this prior art is as the operating voltage is very high in range of 40kV to 125 kV caused high operating temperature, power consumption in 750W, X-ray generation efficiency of 1 to 2%, while cooling system and vacuum chamber are present.

The present invention relates to a Portable Molecular Quantum Dot Cellular Automata methodology for generating X-ray wave from QCA unit. Our proposed system should overcome all the above major drawbacks of high operating voltage, high power consumption, heat dissipated during radiation process, low X-ray generation efficiency, importability due to large size of the conventional X-ray systems and high operating voltage present in the aforesaid prior arts. Comparatively, in proposed invention Quantum dot Cellular Automata [4] paradigm can be employed to generate X-ray wave with very less amount of supply voltage in the range of 2 to 2.81 V _rms and very small amount of power consumption in the range of watt only, the almost 100% radiated energy turns into X-ray wave ensuring least waste with a feature of portability due to its small constructional size.

The proposed Portable Molecular Quantum Dot Cellular Automata X-Ray System (1) generally discloses a portable X-ray system consisting of X-ray generator tube (6) and X-ray detector (8). The present invention is to propose relates to an X-ray generator only. Portable X-ray detectors (8) are already available. The existing conventional X-ray generators are huge in size and permanently housed in a room. The patients are to be brought physically to the X- ray room for imaging. Sometimes this movement becomes very painful for patients having fractures. The present invention is directed towards these kinds of patients to give them some relief from additional pain of movement. Said X-ray generator system along with X-ray detector will be brought to the patient site. The image taken will be stored temporarily with the detector and later it will be analyzed at the laboratory.

Objective of the invention:

The prime objective of the present invention is to propose a Portable Molecular Quantum Dot Cellular Automata (QCA) X-Ray System (1) comprising of a QCA X-ray generator, a X-ray detector and a Q-ray image analyzer, more particularly, to propose a QCA X-ray generator comprising an array of molecular QCA Cells (2) arranged in a X-ray plate (12), a ground plate (3), an arrangement of electrodes (4) and an oxide layer (5) wherein said electrodes (4) are arranged at the lowest level and are buried under said oxide layer (5), said molecular QCA cell (2) are arranged over said oxide layer (5) and furthermore, above layer of said molecular QCA cell (2), said ground plate (3) is placed.

The another objective of the present invention is to propose a portable QCA X-ray system which operates on very low supply voltage of 2 to 2.81 rms voltage which is comparatively negligible to the supply voltage ranging from 1 KV to 125 kV in conventional X-ray systems existing and using in various applications nowadays.

The another objective of the present invention is to propose a Portable Molecular Quantum Dot Cellular Automata (QCA) X-Ray System (1) which operates on very low operating power in some watts only which is comparatively negligible to the supply power of 80 kW in conventional X-ray systems.

The another objective of the present invention is to propose a Portable Molecular Quantum Dot Cellular Automata (QCA) X-Ray System (1) which turns almost 100% radiated energy into X-ray waves while in existing X-ray technology, almost 99% energy is radiated as heat and only 1% radiated into X-ray wave., furthermore, the proposed invention has property of no heat loss during X-ray radiation process. The another objective of the present invention is to propose a Portable Molecular Quantum Dot Cellular Automata (QCA) X-Ray System (1) which is portable in size so that easily brought to patient sites and can give them some relief from additional pain of movement as the existing conventional X-ray generators are huge in size and permanently housed in a room causes the patients to move physically to the X-ray room for imaging and this movement becomes very painful for patients having fractures.

Summary of Invention:

The proposed Portable Molecular Quantum Dot Cellular Automata X-Ray System (1) generally discloses a portable X-ray system consisting of X-ray generator tube (6) and X-ray detector (8). The present invention is to propose relates to an X-ray generator only. Portable X-ray detectors (8) are already available. The existing conventional X-ray generators are huge in size and permanently housed in a room. The patients are to be brought physically to the X- ray room for imaging. Sometimes this movement becomes very painful for patients having fractures. The present invention is directed towards these kinds of patients to give them some relief from additional pain of movement. Said X-ray generator system along with X-ray detector will be brought to the patient site. The image taken will be stored temporarily with the detector and later it will be analyzed at the laboratory.

In the present invention, we disclose one preferred embodiment of the Portable Molecular Quantum Dot Cellular Automata (QCA) X-Ray System wherein said (QCA) X-Ray System consists of an X-ray generator tube, Hollow Parabolic Waveguide, X-ray detector, and the computer controlled (QCA) X-ray Image Analyzer; wherein the said X-ray generator tube is provisioned to generate X-ray from the QCA Cell, due to a unique selection of said QCA Cell and Molecular Cell clocking arrangement therein; wherein said embodiment of the Portable Molecular Quantum Dot Cellular Automata (QCA) X-Ray System is characterized in: (a) generation of X-ray wave with very less amount of supply voltage in the range of 2 to 2.81 V _rms and consuming very small amount of power in the range of watt only; (b) ensuring least waste heat generation by utilizing almost all the power in (QCA) X-Ray generation; (c) each QCA cell is composed of two V shaped molecules, having six redox sites, and the molecular Cell dimension is defined by selecting cell size (d) as 1 nm and also the height (h) as 1 nm; (d) Application of dielectric like Si0 ₂ between electrodes and molecules whose dielectric constant is 4.2; and (e) compact and portable integrated system for effective movement from one patient site to another. In the present invention, we disclose a QCA X-Ray generator tube, comprises of an assembly of a X-ray plate containing an array of molecular QCA cells (2), a ground plate (3), electrodes (4), an oxide layer (5), dielectrics and an X-ray tube (6) attached with a power supply section (13) requires application of very low amount of power in the range of watt, energy and supply voltage in the range of 2 to 2.81 V _rms while the conventional methods for generating X-ray wave involves use of very high supply voltage mostly in kV, power in kW and dissipates a large amount of heat loss. Another embodiment of the proposed invention is to provide a method to generate X-ray by the application of Quantum dot Cellular Automata (QCA) in such a provision that the almost 100% radiated energy turns into X-ray wave ensuring least waste. Another embodiment of the present invention is to propose a portable QCA X-ray generator so that said X-ray generator system along with X-ray detector will be brought to the patient site to give them some relief from additional pain of movement.

Brief description of the accompanying drawings:

Figure 1 shows a perspective view of said QCA cell (2) in V shaped molecular form wherein each said QCA cell (2) is composed of two V shaped molecules and has six redox sites. The figure 1 depicts three stable configurations of the two mobile electrons within the said molecular QCA cell (2).

Figure 2 depicts Molecular Cell dimension of said QCA cell (2) wherein size and height of the said QCA cell is denoted by d and h respectively.

Figure 3 depicts a plot showing interdependency between size (in nm) of said QCA Cell (2) and RMS voltage i.e. V _rms (in Volts) for three different spacing of said electrodes (4).

Figure 4 depicts the four phases of the sinusoidal signals 0; _{, 2,} 0 ₃ and 0 ₄ applied to each of said electrodes (4) such that data may flow as shown and also shows submerged said electrodes(4) [7] to generate an electric field E at the level of said molecular QCA cells (2).

Figure 5(a) shows perspective view of said QCA X-Ray system (1) comprising two buried said electrodes (3), said ground plate (2) and said oxide layer (4) wherein said electrodes (3) are buried within said oxide layer(4) whereas Figure 5(b) depicts a cross sectional view of said QCA X-Ray system (1).

Figure 6 depicts a plot between maximum operating temperature in K, cell size in nm and RMS voltage in volt [7]. Figure 7 shows said QCA cell (2) in 2D representation.

Figure 8 shows Characteristic Curve of an electron wave while moving through channels.

Figure 9 depicts the cross- sectional view of X-ray generator comprising within the proposed QCA X-ray System (1) wherein said electrodes (4) are arranged at the lowest level and are buried under said oxide layer (5), said molecular QCA cell (2) are arranged over said oxide layer (5) and furthermore, above layer of said molecular QCA cell (2), said ground plate (3) is placed.

Figure 10 depicts the perspective view of proposed QCA X-ray system (1) comprising said X- ray tube (6) accompanying with a hollow parabolic waveguide section (7) within said portable QCA X-ray generator, a QCA X-ray detector (8), a computer controlled QCA X-ray image analyzer (9) and electrical connectors (10) wherein the directions of radiation (11) of said QCA ray radiated from said X-ray tube (6) following by hollow parabolic waveguide section are also showing herein.

Figure 11(a) depicts a cross-sectional view of said X-ray plate (12) containing an array of said QCA cells (2) whereas Figure 11(b) views the dimensions of said QCA cells (2) that will replace the square cells in said X-ray plate (12).

Figure 12 depicts the perspective view of the said X-ray tube (6) containing a power supply section (13), said X-ray plate (12) containing an array of said QCA cells (2), said QCA X-ray generator comprising said electrodes (4), said oxide layer (5) and said ground plate (3), alongwith direction of radiation (11) coming out from said X-ray plate (12) directed towards the radiation head (14).

Detailed description of the invention:

In the present invention, a Portable Molecular Quantum Dot Cellular Automata X-Ray System(l) is designed and developed to disclose a novel method to generate X-ray wave by the application of Quantum dot Cellular Automata technique.

The proposed invention consists of said X-ray plate (12) containing an array of QCA cells (2) as shown in Figure 11a. Each QCA cell (2) in said X-ray plate (12) will be replaced by the molecular counterpart as shown in Figure l ib. The cross section of said QCA X-ray system (1) is depicted in Figure 9. At the lowest level said electrodes (4) are arranged. These are buried under said oxide layer (5). The molecular QCA cells (2) are arranged over said oxide layer (5) as in Figure 11a. Above the layer of said molecular QCA cells (2), said ground plate (3) is placed. The cell size of 1 nm may work at temperature between 1000°K to 1300° K at 2 to 2.81 RMS voltages. So there is need for temperature control and said electrodes (4) might be supplied with the required RMS voltage employing step down transformer. Figure 12 depicts said X-ray tube (6) containing power supply section (13). Power supply (13) is housed at the back of said X-ray tube (6). It contains said electrodes (4) and said oxide layer (5). Said ground plate (3) will be located at the top of said electrodes (4). Just outside the power supply section (13) said X-ray plate (12) containing an array of QCA cells (2) is placed. Radiation (11) coming out from said X-ray plate (12) is directed towards radiation head (14).

The detailed design of the furnace can be broadly divided into several functional units given as follows:-

QCA Cell and Molecular cell clocking arrangement:

The said QCA cells (2) and electromagnetic clock signal are the most vital ingredients in the present invention of X-rays radiated from said QCA cells (2) which consume very less amount of electric energy and power.

Each QCA cell (2) is composed of two V shaped molecules and has six redox sites as shown in Figure 1. The redox sites are considered as quantum dots. The figure 1 depicts three stable configurations of the two mobile electrons within the molecular cell. Mobile electrons establishing themselves at the upper diagonal sites (i.e., either at cites 2 and 0 or 1 and 3) represent ACTIVE states of said QCA cell (2). These active states carry two polarities of said cells (2) i.e., P = 1. P = 1 is said to represent binary Γ and P = 1 represents binary 0'. When the two mobile electrons are positioned at the two below sites, the cell is said to represent NULL' state. Figure 2 depicts molecular QCA cell (2) dimension. Here, cell size (d) to be 1 nm and height (h) to be 1 nm is employed[5, 6]. Clock signal is applied through submerged said electrodes (4) buried in said oxide layer (5).

Electrodes

Said electrodes (4) carry electromagnetic clock signals and they are placed at the bottom of said oxide layer (5). The phase shifted sinusoidal signal is applied to each of the electrodes (4) to energize the electrons. Figure 4 depicts the four phases of the applied sinusoidal signal i.e. ,0i, ₂ , 0 ₃ and 0 ₄ and 0i < 0 ₂ < 0 ₃ < 0 ₄ such that the data may flow in the direction as shown in Figure 4. This electric field if in the Y and -Y directions switch said molecular

QCA cell (2) from ACTIVE state to NULL state and vice- versa. Said electrodes (4) have finite radius and potential voltage is applied with respect to said ground plate (3) as shown in Figure 5.

Average electrode potential [7] is determined as, where V _el and V _e2 are the potentials on two adjacent said electrodes (4). The electrode potential difference between two adjacent said electrodes (4) can be given as,

V _e = V _e2 - V _el (2)

The RMS voltage V _rms can be defined as ^ϊ ' - where Vi is maximum allowable V _avg and V ₂ is minimum allowable V _avg [7]. The interdependency between cell size and RMS voltage is studied and analyzed in Figure 3. A spacing of 20 nm [7] is applied while selecting V _rms and cell size. While selecting the above two parameters, analysis of the temperature issues is also required. Now maximum applicable phase difference 0 _max between two adjacent said electrodes (4) having maximum potential difference V _em ax can be expressed as,

0max = ±2sin ^{" 1} ( ¾ ) radians (3)

Here, Vo is peak potential value of clock signal applied to adjacent said electrodes (4) and minimum RMS voltage should be applied [7]. The spacing(s) between said electrodes (4) is kept at 20 nm. Said ground plate (3) is placed = 25 nm above said electrodes (4) and said QCA cells (2) are placed = 23 nm above said electrodes as depicted in Figure 5. The length and radius of said electrode are chosen to be 100 nm and 5 nm respectively as justified in article [9, 10].

Dielectrics

Dielectric like Si0 ₂ is used between said electrodes and molecules whose dielectric constant is 4.2. Said electrodes shall be buried inside said dielectric (Si0 ₂ ) [11].

Temperature Management If said QCA cell size is allowed to decrease, reduced RMS voltage and maximum operating temperature can be regulated as analyzed in Figure 6. At 1000° K to 1300° K, an array of said cells having dimension of 1 nm can be employed with an RMS value of 2 to 2.81 Vrms voltage approximately [7] .

Proposed methodology for the generation of X-ray by the application of QCA technology

Application of clock signal energizes the electrons and brings them to the NULL state. Application of input signal decides polarity when applying simultaneously with the clock signal. Tunneling electrons possess dual wave particle property. Each electron particle, while moving through the tunnel, behaves as a group of waves as suggested by de-Broglie's hypothesis on matter waves [12, 13]. According to this hypothesis this group of waves is nothing but superposition of several monochromatic waves with same amplitude and phase but marginally different wavelength [14, 15] . Let (x) be the superposition state of an electron tunneling between the dots in the x direction. Fourier transform expresses the superposition state (x) of an electron as,

Φ&1 =— t^ ^^ (4) where (k) is the amplitude of the superposition wave, k = ^ is the wave propagation velocity, is the wavelength and z=^™X Fig. 8 shows the characteristic curve of an electron wave while moving through channels [16] . Whenever electron is localized, it is positioning at x = 0 and at this position e ^l(bc> = 1. It means electron waves of different frequencies interfere constructively and no oscillations are reported. Hence (x) attains peak at x = 0. At other values of x, the components of e ^l(kx> are added up in Equation 4. Thus resulting in oscillations and the value of (x) is obtained. At e ^l(kx> attains minimum value and characteristic curve achieves the negative peak. When x grows from this point, the value of e ^l(kx> also grows resulting in growth of (x).

As stated earlier, clock signal is the energy supplier for the electrons to change their state. We assume that inter-dot channels are experiencing finite potential energy V(jc) in the positive x direction. Then time independent Schrodinger wave equation is, where m is the mass of electron, is reduced plank constant, E _n is the in finite sequence of discrete energy levels corresponding to all possible non-negative integral values of n. Here, n is representing the quantum number. Equation 5 can be reduced to

E„ = Ψζ Ι (6) where d is the molecular cell dimension [16]. If applied voltage to the molecule is V volt and junction capacitance is C then, an expression can be generated as [16], ^ + V( ) = ¾CV ² (7)

This expression will be useful in calculating operating RMS voltage of the system.

We assume that two discrete energy states E _nl and E _n2 correspond to two quantum numbers tij and ti ₂ . Electron may transit from one energy state to another if sum or difference of quantum numbers is an odd number [16]. We need to find out the n* quantum number such that while transiting from this state to ground state, a cell radiates energy between 5 X 10 ³ eV to 10 ⁴ eV.

This transition is expressed as,

X-ray generating system requires to radiate X-ray energy in the range between 5 K10 eV to 10 ⁴ eV. Considering lowest energy value i.e., 5 ¾¾10 ³ eV to be equal to Ε in Equation 8, we deduce a relation between electron quantum number (n) and cell dimension (d) as, m ^z - i = m x io¾ ³ (9)

Again considering the highest energy radiation i.e., 10 ⁴ eV and equating it to E _n in Equation 8, the relation between electron quantum number n and molecular cell dimension d can be expressed as, k ^¾ - 1 = X (10)

A careful study of Figure 6 results that at temperature of 1000° K and at 2V _rms operating voltage the cells attain a dimension of 1 nm considering potential energy of an electron to be

5.82 XlO - ^" 20 Joules and junction capacitance to be 200 atto-farad. If molecular cell dimension is considered to be 1 nm, for lowest level of X-ray radiation, Equation 6 produces the value of n to be 116. If the same methodology is applied in Equation 8 for highest limit of X-ray radiation, the value of electron quantum number n can be deduced to 162, the temperature is modified to 1300°C at 2.81 V _rms applied voltage. For a single molecular cell the Equation 8 can be reformed as,

*¾ = d^; (# (I D where ·¾ is radiation frequency.

Equation 11 produces results of 3¾ = $ X W Hz with n = 162 and d = 1 nm and s¾ = $M X l ^s Hz with n = 116 and d = 1 nm which falls between 1 X I S*® Hz to X Hz, the frequency range of existing X-ray for X ray system. The above calculations are for single molecular cell. The radiation energy strength for N number of molecular cells arranged in cascade is computed between 5 X T ^{* 3} X N to 10 ⁴ times N.

Proposed Portable Molecular Quantum Dot Cellular Automata X-Ray system (1)

The said Portable Molecular Quantum Dot Cellular Automata X-Ray System (1) discloses a portable X-ray system consisting of X-ray generator and X-ray detector (8). Portable X-ray detectors (8) are already available. The present invention is to propose Portable Molecular Quantum Dot Cellular Automata X-Ray System (1), more particularly to an QCA X-ray generator which comprises an array of molecular QCA Cells (2) arranged in a X-ray plate (12), a ground plate (3), an arrangement of electrodes (4) and an oxide layer (5) wherein said electrodes (4) are arranged at the lowest level and are buried under said oxide layer (5), said molecular QCA cell (2) are arranged over said oxide layer (5) and furthermore, above layer of said molecular QCA cell (2, said ground plate (3) is placed.

The invention consists of said X-ray plate (12) containing an array of said QCA cells (2) as shown in Figure 11a. Each said QCA cell (2) in the X-ray plate (12) will be replaced by the molecular counterpart as shown in Figure 1 lb.. The cell size of 1 nm may work at temperature between 1000° K to 1300° K at 2 to 2.81 RMS voltage. So there is need for temperature control and electrodes might be supplied with the required RMS voltage employing step down transformer. Figure 12 depicts said X-ray tube (6) containing power supply section (13). Said power supply section (13) is housed at the back of said X-ray tube (6). Just outside said power supply container (13) said X ray plate (12) containing an array of QCA cells (2) is placed. Radiation (11) coming out from said X-ray plate (12) is directed towards radiation head (14). Portable X-ray Detector (8)

Portable X-ray detector (8) [27, 28] is already available in the market. The proposed X-ray system (1) as shown in Figure 10 consisting of the X-ray generator (1) and X-ray detector (8) may be brought to the patient site.

The image created will be detected by the proposed X-ray detector (8). The detector will convert it into electrical signal and will store information temporarily.

Hollow Waveguide or Capillaries (7)

X-ray wave is difficult to direct. Different techniques are employed to direct X-ray beams such as optics based on total reflection principle such as capillary, natural crystals and multilayer optics i.e., manmade layered structures etc. X-ray after generation are scattered everywhere unless we place a hollow parabolic waveguide (7) just after said X-ray tube (6) as suggested in Figure 10. The hollow parabolic waveguide (7) may be made from Carbon Nano Tube (CNT) or glass as reported in patents [29, 30].

Although a preferred embodiment of the invention has been illustrated and described, it will at once be apparent to those skilled in the art that the invention includes advantages and features over and beyond the specific illustrated construction. Accordingly it is intended that the scope of the invention be limited solely by the scope of the hereinafter appended claims, and not by the foregoing specification, when interpreted in light of the relevant prior art.

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