CN101987018B - Nuclear medical X-ray machine - Google Patents
Nuclear medical X-ray machine Download PDFInfo
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- CN101987018B CN101987018B CN2010105283723A CN201010528372A CN101987018B CN 101987018 B CN101987018 B CN 101987018B CN 2010105283723 A CN2010105283723 A CN 2010105283723A CN 201010528372 A CN201010528372 A CN 201010528372A CN 101987018 B CN101987018 B CN 101987018B
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Abstract
The invention belongs to the technical field of medical apparatus and instruments, in particular to a nuclear medical X-ray machine. The nuclear medical X-ray machine comprises a support, a 238Pu low-energy photon source, a 241Am low-energy photon source, an anti-scattering screen, a shielding protection plate, a photographic film holder, an examination bed, a programmable control type operating table, a storage battery pack, a DC low-voltage power supply and the like, wherein the two low-energy photon sources are complementary. The nuclear medical X-ray machine provides marking X-ray or single-color X-ray radiation rather than the continuous X-ray spectrum of bremsstrahlung of the traditional X-ray machine to diagnose human organs, and the nuclear medical X-ray machine can form a high-contrast sharp image on a photographic film. The invention overcomes the defect that the dose commitment of examinees and X-ray workers is aggravated because the traditional X-ray machine and the CT (Computed Tomography) machine have diagnosis radiation and scattering radiation on non-examined human organs and can save about 90% of electric energy. The invention has the advantages of clear imaging, low energy consumption, safety, small size, light weight and the like.
Description
Technical field
The invention belongs to technical field of medical instruments, be specifically related to a kind of nuclear energy medical x-ray machine.
Background technology
Now; The WHO of countries in the world government and the United Nations pays much attention to the dose commitment of the diagnostic illumination of X-ray production apparatus to person under inspection, public individual and X ray worker; International Atomic Energy Agency has issued " international ionization radiation protection and radiation source safety basic security standard " for this reason; The Chinese government has also issued " ionization radiation protection and radiation source safety basic standard " GB18871-2002, implements in the whole nation April 1 2003 Christian era.These standard-required X ray workers are when utilizing the radiodiagnosis irradiation to carry out medical services for the person under inspection; To reduce person under inspection, public individual and X ray worker's dose commitment itself as far as possible; Prevent that deleterious definitiveness biological effect from generating; The generation rate of stochastic effect is compared the acceptable level that is restricted to the medical interests that the x-ray bombardment diagnosis brings, thereby the potential hazard that radiodiagnosis brings is reduced to bottom line, realize bringing good to and remove all evil.
But; Domestic and international widely used diagnostic illumination all is the bremsstrahlung continuous x-ray spectrum of the X-ray tube emission in the X-ray production apparatus at present; This bremsstrahlung all is continuous distribution from the low grenz ray of penetrativeness to the high hard X ray ray of penetrativeness; The probability that the X ray that penetrativeness is low passes human organ is very little, is almost all absorbed by thicker human organ, is difficult on film, forming the high picture rich in detail of contrast.In order to improve contrast, people are at X-ray tube window mounting filtering sheet, and the grenz ray elimination with X-ray tube produces sees through the hard X ray share of human organ and the ratio of grenz ray share in order to raising., the actual share of hard X ray has also reduced when filtering grenz ray, thereby has reduced the total amount of the X ray on the shooting egative film.In order to satisfy film to the constant requirement of the total amount of X ray, people improve tube voltage again.Experimental data proves that along with the raising of tube voltage, the share of the grenz ray that penetrativeness is low also increases considerably, and must increase at the thickness of the filter of X-ray tube window thereupon.The thickness increase of filter also strengthens the total amount that projects on the film, and the contrast on the egative film that causes making a video recording reduces, and not only makes the shooting film fogging, and has increased scattered rays to non-harmful irradiation of being examined organ.For under the condition that does not improve tube voltage, on the shooting egative film, obtain contrast preferably, people are installed intensifier additional in magazine, the sensitivity of system is improved, thereby reduce person under inspection's diagnostic illumination; But highly sensitive intensifier-film combination has reduced definition again, makes the X ray worker be difficult to operation.In addition, X-ray production apparatus will consume a large amount of electric energy and produce useless grenz ray and scattered rays, brings many difficulties for the radiation protection of X-ray production apparatus.The X-ray production apparatus reason that contrast is not high on film proves as follows: people are with a large amount of accurate experiments and Theoretical Calculation summary and derive absorptance τ and the wavelength X of diagnostic illumination and the effective atomic number Z of human organ of X ray to each organ of human body
EfChanging Pattern be τ=CZ
Ef 4λ
3, the C when wavelength variations is little in this relational expression is a constant, the Z corresponding with skeleton
EfBe 8.74, the Z corresponding with the human muscle
EfBe 6.25, the Z corresponding with body fat
EfBe 5.92.According to this relational expression, τ skeleton: τ human muscle: τ body fat=4.75:1.24:1.Though the Z of skeleton, kindred, fatty three-type-person's body organ
EfConstant, but the wavelength X of the bremsstrahlung diagnostic illumination of the X-ray tube of X-ray production apparatus emission is always changing, and makes that the ratio of these three absorptances is not a constant, causes the contrast of photographic film not high.
The sign X-ray is the wavelength combination of differentiated several kinds of spectral line mutually by the few in number of the nuclear radiation of radionuclide, makes τ=CZ
Ef 4λ
3Basic is constant, causes that photographic film has higher contrast ratio in the magazine.
238Pu with
241Am is two kinds of long-life low-energy photon sources that nuclear reactor is produced.
238The composition of the radiating sign X-ray of Pu is 43.5keV, 99.9 keV, 11.6 ~ 21.7 keV; But the intensity of two signs of 43.5 keV and 99.9 keV spectral line only accounts for about 1% of total share; The only sign X-ray of remaining 11.6 ~ 21.7 keV as diagnostic illumination; Its average energy is 16.5 keV, and the sign X-ray of this average energy 16.5 keV can be used for the diagnostic illumination of the human organ of large, medium and small area and less thickness just.
241The radiating sign X-ray of Am is 59.5 keV, 26.4 keV, 11.9 ~ 22.2 keV.Remove the sign X-ray of 11.9 ~ 22.2 keV with filter; The sign X-ray of forming with 59.5 keV, 26.4 keV is made the diagnostic illumination of human organ, or makes the picture rich in detail that diagnostic illumination can both obtain high-contrast with the monochromatic X-ray of 59.5 keV, wherein uses the definition of image of 59.5 keV monochrome X-ray the highest.
And the sign X-ray that protects 59.5 keV ~ 16.5 keV only just can make splendid attire with the H96 pyrite about 20mm, the steel plate about 24mm
238Pu with
241It all identifies X-ray the canister sealing of the low-energy photon source of two row of Am, thereby satisfies country's " ionization radiation protection and radiation source safety basic standard " requirement (GB18871-2002).
Therefore, a kind of energy consumption of not having a bremsstrahlung of exploitation extremely low, by little lightweight, the shooting egative film contrast hi-vision of nuclear energy transmit identification X-ray, that be prone to protection, volume clearly, the non-nuclear energy medical x-ray machine of being examined device and do not have diagnostic illumination is very important.
Summary of the invention
The purpose of this invention is to provide a kind of based on above-mentioned
238Pu with
241The high-contrast imaging requirements that both meets diagnosing radiation of the mental retardation sign X source of two series of Am; Can provide a kind of again for radiology department's machine room of medical system and not have bremsstrahlung, do not have to leak ray, the non-dose commitment nuclear energy medical x-ray machine seldom, that be prone to protection of being examined organ, and be a kind of in the overall process that produces diagnosing radiation the low-carbon economy electromechanical equipment of consumed power not.
The objective of the invention is to realize: this nuclear energy medical x-ray machine through following technical scheme; It comprises support; Be connected with low-energy photon source fixed cross beam group and column group under the top on the support, be hinged with big activity respectively at the front end of each crossbeam of low-energy photon source fixed cross beam group and column group
238Pu low-energy photon source rocking arm, middle activity
238Pu low-energy photon source rocking arm, little activity
238Pu low-energy photon source rocking arm, big activity
241Am low-energy photon source rocking arm, middle activity
241Am low-energy photon source rocking arm, little activity
241Am low-energy photon source rocking arm; Said each low-energy photon source rocking arm can be at 360 of its perpendicular
oRocking-turn and move forward and backward and lock in the angle along the front end of each crossbeam, each crossbeam also can move up and down and lock along each column of low-energy photon source fixed cross beam group and column group around its rear end; The long arm end of each low-energy photon source rocking arm is fixed with big activity respectively
238Pu low-energy photon source, middle activity
238Pu low-energy photon source, little activity
238Pu low-energy photon source, big activity
241Am low-energy photon source, middle activity
241Am low-energy photon source, little activity
241The Am low-energy photon source; On the support below low-energy photon source fixed cross beam group and the column group, be fixed with a low-energy photon source group and deposit the shielding platform; The upper surface that the low-energy photon source group is deposited the shielding platform is provided with six circular recessed basins of depositing low-energy photon source; When each low-energy photon source rocking arm straight down the time, six recessed basins of circle are corresponding with the position of each low-energy photon source; Diagnostic bed each low-energy photon source of being installed in
238Pu or
241Under the radiating sign X-ray of Am, and on the support of diagnostic bed bottom, cartridge for photographic film is set, cartridge for photographic film is installed in low-energy photon source
238Pu or
241200mm---400mm position behind the human organ of the sign X-ray irradiation of Am; Around diagnostic bed with below the cartridge for photographic film of bottom, be provided with anti-scatter and shield; Also be provided with the shielding protection plate after the anti-scatter screen around diagnostic bed; The dry timber of said diagnostic bed employing is processed; Said anti-scatter screen is aluminum---ferrum---aluminum composite three-layer plate structure; Said shielding protection plate is aluminum---lead---ferrum composite three-layer plate structure; Said support adopts metal material to process and lead ground connection is used in its bottom; It is the composite plate structure that wood-ferrum-lead-ferrum four layer materials are processed that said low-energy photon source group is deposited the shielding platform; This X-ray machine also comprises accumulator battery, Dc low voltage power supply and control type operating board able to programme, and control type operating board able to programme and Dc low voltage power supply are connected and control the switch and the button of each low-energy photon source with accumulator battery.
Said big activity
238The Pu low-energy photon source comprises that a bottom has the Stainless steel basin shape of a hollow circular hole to support, and the sunk screw group of a trapezoid rustless steel hollow round platform shielding overcoat bottom it is installed in the support of Stainless steel basin shape; The bottom of the hollow hole of the hollow round platform shielding of rustless steel overcoat is trapezoidal, and the internal diameter of going to the bottom of this trapezoidal hollow hole is consistent with the internal diameter that Stainless steel basin shape is supported hollow hole; In the upper flat top hollow hole of the hollow round platform shielding of rustless steel overcoat, shield overcoat through the H96 pyrite screwed pipe that has been threaded; Top in the H96 pyrite screwed pipe shielding overcoat is through the rustless steel shielding bolt that has been threaded, and its underpart is equipped with
238The Pu low-energy photon source; Said
238The Pu low-energy photon source comprise the monel metal pressure vessel,
238Pu radioactivity potsherd and exit window,
238The Pu low-energy photon source is connected with H96 pyrite screwed pipe shielding sleeve thread through the monel metal pressure vessel, and exit window is positioned at its bottom; Hollow hole at the hollow round platform shielding of the rustless steel overcoat that is positioned at H96 pyrite screwed pipe shielding jacket bottom is equipped with a H96 pyrite gate, and a lucite dust excluding plate also is installed in the hollow hole under H96 pyrite gate; H96 pyrite gate and a slip iron core are connected; Slide last plane unshakable in one's determination and lower plane is respectively equipped with the hollow round platform of rustless steel and shields top back-moving spring and the middle part back-moving spring that the outer surface of overcoat is connected; Be installed on the edge horizontal plane of Stainless steel basin shape support with the corresponding sucking coil unshakable in one's determination that slides, the magnetic field gravitation that sucking coil produces when photoexposure is slightly larger than the distance of sliding to sucking coil unshakable in one's determination of sliding
238The external thread diameter of the monel metal pressure vessel of Pu low-energy photon source; The lower hollow trapezoidal walls intracavity of filling with the hollow round platform shielding of rustless steel overcoat through the molten lead that temperature is higher than 330 ℃ forms a trapezoidal annulus of lead screen; On the inwall of the trapezoidal hollow hole in bottom of the hollow round platform of said rustless steel shielding overcoat, also be connected with an anti-scatter aluminium sheet funnel through sunk screw.
Activity in said
238Pu low-energy photon source, little activity
238The overall structure of Pu low-energy photon source and said big activity
238The overall structure of Pu low-energy photon source is identical; Said big activity
241Am low-energy photon source, middle activity
241Am low-energy photon source, little activity
241The overall structure of Am low-energy photon source also all with said big activity
238The overall structure of Pu low-energy photon source is identical.
Said control type operating board able to programme comprises 6 single-phase DC solid-state relays, 6 sucking coils, 12 dropping resistors, 6 photoelectrical couplers, 8 toggle switch, 12 making buttons, 6 fuses, 1 single-pole switch, 1 Programmable Logic Controller PLC and 1 band switch; That Programmable Logic Controller PLC adopts is FX2N-32MR-ES/UL; The A phase line is connected with N with the terminal L of PLC through moving plate of band switch and the 220V alternating current of zero line N; 24V terminal among the PLC is connected with the end of toggle switch KNX6, KNX7 and making button SB1, SB2, SB3, SB4, SB5, SB6 respectively; The other end of KNX6 and KNX7 is connected with X17 with the input terminal X0 of PLC again, and the other end of making button SB1, SB2, SB3, SB4, SB5, SB6 is connected with input terminal X1, X2, X3, X4, X5, the X6 of PLC respectively again; The 0V terminal that is connected with ground among the PLC is at first with the negative pole of another moving plate of band switch and LED 0, LED1, LED2, LED3, LED4, LED5 and after connecing; Again with the signal input part negative pole of single-phase DC solid-state relay SSR0, SSR1, SSR2, SSR3, SSR4, SSR5 and connect; The positive pole of LED0 with after the positive pole of solid-state relay SSR0 input is connected again with after the end of dropping resistor R1 is connected, the other end of R1 is connected with the lead-out terminal Y0 of PLC; The colelctor electrode of the phototransistor T0 of photoelectrical coupler is connected with the 24V positive source, and the end of dropping resistor R0 is connected with ground, the non-earth terminal of R0 be connected with the input X7 of PLC again after the E utmost point E0 of T0 is connected; The 24V dc source is through the end of single-pole switch Q and fuse F U0, FU1, FU2, FU3, FU4, FU5 and connect; The other end of FU0 be connected with the end of making button SB7 again after the output head anode of SSR0 is connected; One end of the other end of SB7 and the negative pole of SSR0 and first sucking coil also connects; The other end of this sucking coil is connected with the end of KNX0, and the other end of KNX0 is connected with ground.The positive pole of LED1 be connected with the end of R3 again after the SSR1 input anode is connected, the other end of R3 is connected with the outfan Y1 of PLC; The colelctor electrode of the phototransistor T1 of photoelectrical coupler connects the 24V positive source, its E utmost point E1 be connected with the input X10 of PLC again after the end of R2 is connected, the other end of R2 joins with ground; The end of making button SB8 is connected the back and is connected with FU1 with the SSR1 output head anode; The other end of SB8 be connected with an end of second sucking coil again after the SSR1 negative pole of output end is connected; The other end of this sucking coil is connected with the end of KNX1, and the other end of KNX1 is connected with ground; The positive pole of LED2 is connected the back and is connected with the end of dropping resistor R5 with the positive pole of SSR2 input, the other end of R5 is connected with the outfan Y2 of PLC; The colelctor electrode of phototransistor T2 in the photoelectrical coupler connects the 24V positive source, its E utmost point E2 be connected with the input X11 of PLC again after the end of dropping resistor R4 is connected, the other end of R4 is connected with ground; The end of making button SB9 be connected with the positive pole of the outfan of SSR2 again after the end of FU2 is connected; The other end of SB9 be connected with an end of the 3rd sucking coil again after the negative pole of SSR2 outfan is connected; The other end of this sucking coil is connected with the end of KNX2, and the other end of KNX2 is connected with ground; The positive pole of LED3 be connected with the end of dropping resistor R7 again after the positive pole of SSR3 input is connected, the other end of R7 is connected with the outfan Y3 of PLC; The colelctor electrode of phototransistor T3 in the photoelectrical coupler is connected with the 24V positive source, its E utmost point E3 be connected with the end of dropping resistor R6 again after the input X12 of PLC is connected, the other end of R6 is connected with ground; The end of making button SB10 be connected with the end of FU3 again after the SSR3 output head anode is connected; The other end of SB10 be connected with an end of the 4th sucking coil again after the SSR3 negative pole of output end is connected; This sucking coil other end is connected with the end of KNX3, and the other end of KNX3 is connected with ground; The positive pole of LED4 be connected with the end of dropping resistor R9 again after the SSR4 input anode is connected, the other end of R9 is connected with the outfan Y4 of PLC; The colelctor electrode of the phototransistor T4 of photoelectrical coupler is connected with the 24V positive source, its E utmost point E4 be connected with the end of dropping resistor R8 again after PLC input X13 is connected, the other end of R8 is connected with ground; The end of making button SB11 be connected with FU4 again after the SSR4 output head anode is connected; The other end of SB11 is connected the back and is connected with an end of the 5th sucking coil with the SSR4 negative pole of output end; The other end of this sucking coil is connected with the end of KNX4, and the other end of KNX4 is connected with ground.The positive pole of LED5 be connected with the end of dropping resistor R11 again after the positive pole of SSR5 is connected, the other end of R11 is connected with the outfan Y5 of PLC; The colelctor electrode of the phototransistor T5 of photoelectrical coupler is connected with the 24V positive source, its E utmost point E5 be connected with the end of dropping resistor R10 again after PLC input X14 is connected, the other end of R10 is connected with ground; The end of making button SB12 be connected with the end of FU5 again after the SSR5 output head anode is connected; The other end of SB12 be connected with an end of the 6th sucking coil again after the SSR5 negative pole of output end is connected; The other end of this sucking coil is connected with the end of KNX5, and the other end of KNX5 is connected with ground.
Nuclear energy medical x-ray machine of the present invention is when carrying out diagnostic illumination; The Stainless steel basin shape of anti-scatter screen, shielding protection plate, low-energy photon source support absorbed the person under inspection up and down, the overwhelming majority of the sign X-ray of left, right, front and rear all directions scattering, the radiation level of space of planes all is a background thereafter.And X-ray machine of the present invention chamber can adopt the thick brick of 200mm to do surroundings wall, does upper and lower floor with the thick armored concrete of 200mm, just has no the X-ray of sign and leaks into outdoor.Therefore, the X ray worker time does not have the exposure dose burden for the person under inspection carries out the diagnostic illumination service in that nuclear energy medical x-ray machine of the present invention is indoor.
According to the invention
238The Pu low-energy photon source with
241The radiation level of Am low-energy photon source working space in force all meets the regulation requirement of country " ionization radiation protection and radiation source safety basic standard " (GB18971-2002).
The present invention not only overcome bremsstrahlung contrast on the shooting film of traditional X-ray radiography unit, CT machine not high, not fogging clear, examined that human organ exists diagnosing radiation and scattered radiation and the shortcoming that increases the weight of person under inspection and X ray worker dose commitment to non-; And having overcome the traditional X-ray radiography unit and CT machine power consumption can not be grown greatly apart from shortcomings such as fast moving, nuclear energy medical X-ray function of the present invention is saved electric energy about 90%.Therefore, the present invention has that imaging is clear, energy consumption is low, the little advantage such as in light weight of safety, volume, both has been fit to big and medium-sized cities use, and is adapted at again using in samll cities and towns outlying district, the battlefield medical aid.
Description of drawings
Fig. 1 is the population structure sketch map of the embodiment of the invention.
Fig. 2 is the big activity among Fig. 1
238The cross-sectional view of Pu low-energy photon source.
Fig. 3 is the big activity among Fig. 1
241The cross-sectional view of Am low-energy photon source.
Fig. 4 is that the circuit of the control type operating board able to programme among Fig. 1 connects sketch map.
The specific embodiment
Below in conjunction with accompanying drawing and embodiment the present invention is described in further detail.
Referring to Fig. 1, present embodiment comprises support 2, is being connected with low-energy photon source fixed cross beam group and column group 5 on top on the support 2 under 3, is hinged with big activity respectively at the front end of each crossbeam of low-energy photon source fixed cross beam group and column group 5
238Pu low-energy photon source rocking arm 6, middle activity
238Pu low-energy photon source rocking arm 8, little activity
238Pu low-energy photon source rocking arm 10, big activity
241Am low-energy photon source rocking arm 12, middle activity
241Am low-energy photon source rocking arm 14, little activity
241Am low-energy photon source rocking arm 16; For adapting to the requirement of various diagnostic illumination position, each low-energy photon source rocking arm can be at 360 of its perpendicular
oRocking-turn and move forward and backward and lock in the angle along the front end of each crossbeam, each crossbeam also can move up and down and lock along each column of low-energy photon source fixed cross beam group and column group 5 around its rear end; The long arm end of each low-energy photon source rocking arm is fixed with big activity respectively
238Pu low-energy photon source 7, middle activity
238Pu low-energy photon source 9, little activity
238Pu low-energy photon source 11, big activity
241Am low-energy photon source 13, middle activity
241Am low-energy photon source 15, little activity
241Am low-energy photon source 17; On the support 2 below low-energy photon source fixed cross beam group and the column group 5, be fixed with the low-energy photon source group and deposit shielding platform 4; The upper surface that the low-energy photon source group is deposited shielding platform 4 is provided with six circular recessed basins of depositing low-energy photon source; When each low-energy photon source rocking arm straight down the time, six recessed basins of circle are corresponding with the position of each low-energy photon source; This shielding platform 4 supplies X ray worker shielding when maloperation and back-moving spring inefficacy and replacing back-moving spring all to leak ray, and making the radiation level perseverance of X-ray machine chamber is background.Diagnostic bed 21 are installed in each low-energy photon source
238Pu or
241Under the radiating sign X-ray of Am, and cartridge for photographic film 19 is set on the support of diagnostic bed 21 bottoms, cartridge for photographic film 19 is installed in low-energy photon source
238Pu or
241200mm---400mm position behind the human organ of the sign X-ray irradiation of Am; Be provided with anti-scatter and shielding 18 around diagnostic bed 21 with below the bottom cartridge for photographic film 19; Also be provided with shielding protection plate 20 after the anti-scatter screen 18 around diagnostic bed 21; Said diagnostic bed 21 adopt dry timber to process; Said anti-scatter screen 18 is aluminum---ferrum---aluminum composite three-layer plate structure; Said shielding protection plate 20 is aluminum---lead---ferrum composite three-layer plate structure; Said support 2 adopts metal material to process and lead ground connection is used in its bottom 22; It is the composite plate structure that wood-ferrum-lead-ferrum four layer materials are processed that said low-energy photon source group is deposited shielding platform 4; This X-ray machine also comprises accumulator battery 1, Dc low voltage power supply 24 and control type operating board 23 able to programme, and control type operating board 23 able to programme and Dc low voltage power supply 24 are connected and control the switch and the button of each low-energy photon source with accumulator battery 1.Subsequent use Dc low voltage power supply when accumulator battery 1 is stopped power supply for the 220V civil power, at ordinary times by 1 charging of 24 pairs of accumulator batteries of Dc low voltage power supply, also can be by solaode and the charging of movable small generating set; Accumulator in the accumulator battery 1 can be one, also can be for two or more, and the anode of the negative electrode back parallel with one another ground connection of each accumulator, each accumulator is also parallel with one another when two or more, and the output voltage of accumulator battery 1 is 12V/24V/36V.
Referring to Fig. 2, big activity
238Pu low-energy photon source 7 comprises that the bottom has the Stainless steel basin shape of a hollow circular hole to support 25, and the hollow round platform shielding of trapezoid rustless steel overcoat 37 is installed in the Stainless steel basin shape support 25 through the sunk screw group 38 of its bottom; The bottom of the hollow hole of the hollow round platform shielding of rustless steel overcoat 37 is trapezoidal, and the internal diameter of going to the bottom of this trapezoidal hollow hole is consistent with the internal diameter that Stainless steel basin shape is supported 25 hollow holes; In the upper flat top hollow hole of the hollow round platform shielding of rustless steel overcoat 37, shield overcoat 35 through the H96 pyrite screwed pipe that has been threaded; Top in the H96 pyrite screwed pipe shielding overcoat 35 is through the rustless steel shielding bolt 34 that has been threaded, and its underpart is equipped with
238Pu low-energy photon source 33; Said
238Pu low-energy photon source 33 comprise the monel metal pressure vessel,
238Pu radioactivity potsherd and exit window,
238Pu low-energy photon source 33 is threaded with H96 pyrite screwed pipe shielding overcoat 35 through the monel metal pressure vessel, and exit window is positioned at its bottom; Hollow hole at the hollow round platform shielding of the rustless steel overcoat 37 that is positioned at H96 pyrite screwed pipe shielding overcoat 35 bottoms is equipped with H96 pyrite gate 32; In the hollow hole under H96 pyrite gate 32 lucite dust excluding plate 36 is installed also, horizontally slipping of 32 pairs of lucite dust excluding plates 36 of H96 pyrite gate is contactless friction-free slip; H96 pyrite gate 32 unshakable in one's determination 28 is connected with sliding, and slide unshakable in one's determination 28 last plane and lower plane are respectively equipped with the hollow round platform of rustless steel and shield top back-moving spring 29 and the middle part back-moving spring 27 that the outer surface of overcoat 37 is connected; Be installed on the edge horizontal plane of Stainless steel basin shape support 25 with the 28 corresponding sucking coils 26 unshakable in one's determination that slide, the magnetic field gravitation that sucking coil 26 produces when photoexposure makes slip unshakable in one's determination 28 be slightly larger than to the distance that sucking coil 26 slides
238The external thread diameter of the monel metal pressure vessel of Pu low-energy photon source 33 like this, just can make H96 pyrite gate 32 open fully.Fill with the lower hollow trapezoidal walls intracavity of the hollow round platform shielding of rustless steel overcoat 37 through the molten lead that temperature is higher than 330 ℃, when temperature drops to plumbous freezing point, just formed the trapezoidal annulus 30 of lead screen; When corrosion resistant plate or other sheet material were enough thick, also available steel plate or thick corrosion resistant plate and thick copper coin and all kinds of sheet material replaced the trapezoidal annulus 30 of hollow lead screen, and then did to go up the top with stainless steel material and process the hollow round platform shielding of rustless steel overcoat 37.On the inwall of the trapezoidal hollow hole in bottom of the hollow round platform of said rustless steel shielding overcoat 37, also be connected with anti-scatter aluminium sheet funnel 31, be used for reducing of the harmful irradiation of scattering sign X-ray human organ through sunk screw.Fig. 2 explanation,
238Pu low-energy photon source 33 is all shielded by H96 pyrite screwed pipe shielding overcoat 35, rustless steel shielding bolt 34, H96 pyrite gate 32, the hollow round platform shielding of rustless steel overcoat 37, makes
238Pu low-energy photon source 33 has no the sign X-ray to let out, and need not to resemble the anti-leak parts to be set the traditional X-ray radiography unit.Simultaneously, Stainless steel basin shape is supported 25 and has been absorbed the make progress overwhelming majority sign X-ray of scattering of person under inspection's skin.
Activity in said
238Pu low-energy photon source 9, little activity
238The overall structure of Pu low-energy photon source 11 and said big activity
238The overall structure of Pu low-energy photon source 7 is identical.Middle activity
238The nominal activity of Pu low-energy photon source 9 is less than big activity
238The nominal activity of Pu low-energy photon source 7, little activity
238The nominal activity of Pu low-energy photon source 11 is less than middle activity
238The nominal activity of Pu low-energy photon source 9.
Said big activity
241Am low-energy photon source 13, middle activity
241Am low-energy photon source 15, little activity
241The overall structure of Am low-energy photon source 17 also all with said big activity
238The overall structure of Pu low-energy photon source 7 is identical.Middle activity
241The nominal activity of Am low-energy photon source 15 is less than big activity
241The nominal activity of Am low-energy photon source 13, little activity
241The nominal activity of Am low-energy photon source 17 is less than middle activity
241The nominal activity of Am low-energy photon source 15.Fig. 3 is big activity
241The cross-sectional view of Am low-energy photon source, visible by figure, big activity
241Am low-energy photon source 13 comprises that Stainless steel basin shape supports 39, the trapezoidal annulus of sucking coil 40, middle part back-moving spring 41, unshakable in one's determination 42, the top back-moving spring 43 of sliding, hollow lead screen 44, anti-scatter aluminium sheet funnel 45, H96 pyrite gate 46, rustless steel shielding bolt 47,
241Am low-energy photon source 48, H96 pyrite screwed pipe shielding overcoat 49, lucite dust excluding plate 50, the hollow round platform shielding of rustless steel overcoat 51, sunk screw group 52.Wherein,
241Am low-energy photon source 48 by the monel metal pressure vessel,
241Am radioactivity enamel, exit window assembled package form.
In Fig. 1, big activity
238Pu low-energy photon source 7 provides the irradiation of sign x-ray, middle activity for thickness human organ in the large tracts of land
238Pu low-energy photon source 9 provides the irradiation of sign x-ray, little activity for the less thickness human organ of middle area
238Pu low-energy photon source 11 provides the irradiation of sign x-ray for the little thickness human organ of small size; Big activity
241Am low-energy photon source 13 picture rich in detail of high-contrast occurs for the big thickness human organ of large tracts of land provides sign X-ray or the irradiation of monochromatic x-ray on the shooting film.Middle activity
241Am low-energy photon source 15 picture rich in detail of high-contrast occurs for thickness human organ in the middle area provides sign X-ray or the irradiation of monochromatic x-ray on the shooting film.Little activity
241Am low-energy photon source 17 picture rich in detail of high-contrast also occurs for thickness in the small size or the big thickness human organ of small size provide sign X-ray or the irradiation of monochromatic x-ray on the shooting film.Also can make according to the size and the shape of human organ
238Pu with
241Two series of Am also satisfy the medical low-energy photon source of specific (special) requirements, make the non-organ of being examined avoid harmful irradiation.Therefore,
238Pu with
241The low-energy photon source of two complementary serieses of Am can satisfy whole requirements that the nuclear energy medical x-ray machine carries out diagnostic illumination fully.
Fig. 2 and Fig. 3 explanation, when sucking coil 26 and 40 all during the access failure power supply,
23833 draws of Pu low-energy photon source
241The mental retardation sign X-ray that Am low-energy photon source 48 radiates is all shielded by H96 pyrite gate 32 and 46, rustless steel shielding bolt 34 and 47, H96 pyrite screwed pipe shielding overcoat 35 and 49, the hollow round platform shielding of rustless steel overcoat 37 and 51, makes
23833 draws of Pu low-energy photon source
241Am low-energy photon source 48 all is in storing state, makes big activity
238The outer surface of Pu low-energy photon source 7 and big activity
241The radiation level of the outer surface of Am low-energy photon source 13 all is a background, the harmful irradiation that makes person under inspection and X ray worker before and after exposure, avoid leaking ray.
238Pu low-energy photon source 7,
238Pu low-energy photon source 9,
238Pu low-energy photon source 11,
241Am low-energy photon source 13,
241Am low-energy photon source 15,
241The monel metal pressure vessel of Am low-energy photon source 17, radioactivity potsherd or radioactivity enamel and exit window can be made by human organ size and shape; Each low-energy photon source is all sent approximate parallel sign X-ray, makes the non-organ of being examined do not identified the diagnostic illumination of X-ray and the irradiation of the least possible scattered rays.
238Pu low-energy photon source 7,
238Pu low-energy photon source 9,
238Pu low-energy photon source 11,
241Am low-energy photon source 13,
241Am low-energy photon source 15,
241Am low-energy photon source 17 is installed in the loop configuration vertical, rotatable various angles successively, can process CT machine numerous in variety and sheet metal defectoscope and rays safety detection apparatus.
Said low-energy photon source also can adopt intrinsic specific activity (millicurie/gram) height, activity is big, area is little
244Cm makes the diagnostic illumination of specific use.
Referring to Fig. 4, control type operating board 23 able to programme comprises 6 single-phase DC solid-state relays, 6 sucking coils, 12 dropping resistors, 6 photoelectrical couplers, 8 toggle switch, 12 making buttons, 6 fuses, 1 single-pole switch, 1 Programmable Logic Controller PLC and 1 band switch; That Programmable Logic Controller PLC adopts is FX2N-32MR-ES/UL; The A phase line is connected with N with the terminal L of PLC through the moving plate 53 of band switch and the 220V alternating current of zero line N; 24V terminal among the PLC is connected with the end of toggle switch KNX6, KNX7 and making button SB1, SB2, SB3, SB4, SB5, SB6 respectively; The other end of KNX6 and KNX7 is connected with X17 with the input terminal X0 of PLC again, and the other end of making button SB1, SB2, SB3, SB4, SB5, SB6 is connected with input terminal X1, X2, X3, X4, X5, the X6 of PLC respectively again; The 0V terminal that is connected with ground among the PLC is at first with the negative pole of band switch moving plate 54 and LED 0, LED1, LED2, LED3, LED4, LED5 and after connecing; Again with the signal input part negative pole of single-phase DC solid-state relay SSR0, SSR1, SSR2, SSR3, SSR4, SSR5 and connect; The positive pole of LED0 with after the positive pole of solid-state relay SSR0 input is connected again with after the end of dropping resistor R1 is connected, the other end of R1 is connected with the lead-out terminal Y0 of PLC; The colelctor electrode of the phototransistor T0 of photoelectrical coupler is connected with the 24V positive source, and the end of dropping resistor R0 is connected with ground, the non-earth terminal of R0 be connected with the input X7 of PLC again after the E utmost point E0 of T0 is connected; The 24V dc source is through the end of single-pole switch Q and fuse F U0, FU1, FU2, FU3, FU4, FU5 and connect; The other end of FU0 be connected with the end of making button SB7 again after the output head anode of SSR0 is connected; One end of the other end of SB7 and the negative pole of SSR0 and sucking coil 26 also connects; The other end of sucking coil 26 is connected with the end of KNX0, and the other end of KNX0 is connected with ground.The positive pole of LED1 be connected with the end of R3 again after the SSR1 input anode is connected, the other end of R3 is connected with the outfan Y1 of PLC; The colelctor electrode of the phototransistor T1 of photoelectrical coupler connects the 24V positive source, its E utmost point E1 be connected with the input X10 of PLC again after the end of R2 is connected, the other end of R2 joins with ground; The end of making button SB8 is connected the back and is connected with FU1 with the SSR1 output head anode; The other end of SB8 be connected with an end of sucking coil 55 again after the SSR1 negative pole of output end is connected; The other end of sucking coil 55 is connected with the end of KNX1, and the other end of KNX1 is connected with ground; The positive pole of LED2 is connected the back and is connected with the end of dropping resistor R5 with the positive pole of SSR2 input, the other end of R5 is connected with the outfan Y2 of PLC; The colelctor electrode of phototransistor T2 in the photoelectrical coupler connects the 24V positive source, its E utmost point E2 be connected with the input X11 of PLC again after the end of dropping resistor R4 is connected, the other end of R4 is connected with ground; The end of making button SB9 be connected with the positive pole of the outfan of SSR2 again after the end of FU2 is connected; The other end of SB9 be connected with an end of sucking coil 56 again after the negative pole of SSR2 outfan is connected; The other end of sucking coil 56 is connected with the end of KNX2, and the other end of KNX2 is connected with ground; The positive pole of LED3 be connected with the end of dropping resistor R7 again after the positive pole of SSR3 input is connected, the other end of R7 is connected with the outfan Y3 of PLC; The colelctor electrode of phototransistor T3 in the photoelectrical coupler is connected with the 24V positive source, its E utmost point E3 be connected with the end of dropping resistor R6 again after the input X12 of PLC is connected, the other end of R6 is connected with ground; The end of making button SB10 be connected with the end of FU3 again after the SSR3 output head anode is connected; The other end of SB10 be connected with an end of sucking coil 40 again after the SSR3 negative pole of output end is connected; Sucking coil 40 other ends are connected with the end of KNX3, and the other end of KNX3 is connected with ground; The positive pole of LED4 be connected with the end of dropping resistor R9 again after the SSR4 input anode is connected, the other end of R9 is connected with the outfan Y4 of PLC; The colelctor electrode of the phototransistor T4 of photoelectrical coupler is connected with the 24V positive source, its E utmost point E4 be connected with the end of dropping resistor R8 again after PLC input X13 is connected, the other end of R8 is connected with ground; The end of making button SB11 be connected with FU4 again after the SSR4 output head anode is connected; The other end of SB11 is connected the back and is connected with an end of sucking coil 57 with the SSR4 negative pole of output end; The other end of sucking coil 57 is connected with the end of KNX4, and the other end of KNX4 is connected with ground.The positive pole of LED5 be connected with the end of dropping resistor R11 again after the positive pole of SSR5 is connected, the other end of R11 is connected with the outfan Y5 of PLC; The colelctor electrode of the phototransistor T5 of photoelectrical coupler is connected with the 24V positive source, its E utmost point E5 be connected with the end of dropping resistor R10 again after PLC input X14 is connected, the other end of R10 is connected with ground; The end of making button SB12 be connected with the end of FU5 again after the SSR5 output head anode is connected; The other end of SB12 be connected with an end of sucking coil 58 again after the SSR5 negative pole of output end is connected; The other end of sucking coil 58 is connected with the end of KNX5, and the other end of KNX5 is connected with ground.
Referring to Fig. 1 and Fig. 4, big activity
238Pu low-energy photon source 7 is corresponding with sucking coil 26, middle activity
238Pu low-energy photon source 9 is corresponding with sucking coil 55, little activity
238Pu low-energy photon source 11 is corresponding with sucking coil 56, big activity
241Am low-energy photon source 13 is corresponding with sucking coil 40, middle activity
241Am low-energy photon source 15 is corresponding with sucking coil 57, little activity
241Am low-energy photon source 17 is corresponding with sucking coil 58.
Fig. 4 explanation; When single-pole switch Q breaks off and when civil power 220V connected, can check among the PLC corresponding relation of T0, T1, T2, T3, T4, T5 and LED0, LED1, LED2, LED3, LED4, LED5 in each making button SB1, SB2, SB3, SB4, SB5, SB6 and the photoelectrical coupler.
Fig. 1 and Fig. 4 explanation; Need only X ray worker closed toggle switch KNX0 and making button SB7, KNX1 and SB8, KNX2 and SB9, KNX3 and SB10, KNX4 and SB11, KNX5 and SB12 on the guidance panel of control type operating board 23 able to programme, just can remove to adjust the technical parameter of R0 and R1 and sucking coil 26, R2 and R3 and sucking coil 55, R4 and R5 and sucking coil 56, R6 and R7 and sucking coil 40, R8 and R9 and sucking coil 57, R10 and R11 and sucking coil 58 through the film image of 19 li of the diagnostic bed 21 following cartridge for photographic film of installing.The rotation band switch makes moving plate 53 and 54 and 220V alternating current cut-out, and each lead-out terminal Y0, Y1, Y2, Y3, Y4, Y5 and the earth of PLC are all broken off, and is used for protecting the output circuit of PLC.Closed KNX0 makes the moving together contact X0 of input terminal closed, break contact X0 is broken off; Closed KNX13 cuts off the power supply Y0, Y1, Y2, Y3, Y4, Y5.
Present embodiment is that human organ provides the operating process of diagnostic illumination following:
Referring to Fig. 1, Fig. 2, Fig. 3, Fig. 4, before start, connect the 220V alternating current on the PLC, about five minutes of the electronic device among the preheating PLC.Press human organ size and shape and confirm to use the numbering of low-energy photon source.If the irradiation of sign x-ray will be provided for the human organ of thickness in the large tracts of land, just can confirm to use big activity
238P
UThe human organ that the anti-scatter aluminium sheet funnel 31 of low-energy photon source 7 is aimed on diagnostic bed 21; The about 250mm of air line distance of human organ and anti-scatter aluminium sheet funnel 31; Anti-scatter screen 18 is laid in diagnostic bed 21 both sides, and anti-scatter is shielded 18 and diagnostic bed 21 the about 250mm of distance, with the scattered rays of shielding protection plate 20 shieldings to the X ray worker; Closed toggle switch KNX0 and single-pole switch Q; Press exposure button SB1, output winding Y0 energising 1-2ms of PLC, the magnetic field suction slip unshakable in one's determination 28 that sucking coil 26 produces drives H96 pyrite gates 32; Making low-energy photon source 33 1---2ms sends the irradiation of sign x-ray to human organ in the time, and the photographic film in the cartridge for photographic film of below diagnostic bed 21, installing 19 can obtain the picture rich in detail of high-contrast.If desired with artificial exposure, can be by artificial exposure button SB7; Exposing operation is broken off single-pole switch Q and toggle switch KNX0, with big activity after accomplishing successively
238Pu low-energy photon source 7 is moved back into the low-energy photon source group and deposits in the circular recessed basin corresponding on the shielding platform 4, and anti-scatter screen 18 is resetted with shielding protection plate 20.
When the human organ that runs into the big thickness of large tracts of land will carry out diagnostic illumination, can confirm to use big activity
241Am low-energy photon source 13, this moment is with big activity
241The human organ that the anti-scatter aluminium sheet funnel 45 of Am low-energy photon source 13 is aimed on diagnostic bed 21; The about 350mm of air line distance of human organ and anti-scatter aluminium sheet funnel 45; Anti-scatter protective shield 18 is laid in diagnostic bed 21 both sides; Anti-scatter is shielded 18 and diagnostic bed 21 the about 250mm of distance, with the scattered rays of shielding protection plate 20 shieldings to the X ray worker, closed toggle switch KNX3 and single-pole switch Q; Press exposure button SB4; The output winding Y3 of PLC energising 1-2ms, the magnetic field suction that sucking coil 40 produces slide and unshakable in one's determination 42 drive H96 pyrite gates 46, make low-energy photon source 48 1---and 2ms sends the irradiation of sign x-ray or monochromatic X-ray shines to human organ the time in; Photographic film in the cartridge for photographic film of below diagnostic bed 21, installing 19 can obtain the picture rich in detail of high-contrast, the wherein corresponding monochromatic x-ray irradiation of HD image.If carry out the manual work exposure, can be by artificial exposure button SB10; Exposing operation is broken off single-pole switch Q and toggle switch KNX3, with big activity after accomplishing successively
241Am low-energy photon source 13 is moved back into the low-energy photon source group and deposits in the circular recessed basin corresponding on the shielding platform 4, and anti-scatter screen 18 is resetted with shielding protection plate 20.
Activity in confirming to use
238Pu low-energy photon source 9, little activity
238Pu low-energy photon source 11, middle activity
241Am low-energy photon source 15, little activity
241Am low-energy photon source 17 provides method of diagnosing and operating procedure with noted earlier identical for human organ.
Claims (3)
1. nuclear energy medical x-ray machine; It is characterized in that: it comprises support (2); Be connected with low-energy photon source fixed cross beam group and column group (5) going up under the top (3) of support (2), be hinged with big activity respectively at the front end of each crossbeam of low-energy photon source fixed cross beam group and column group (5)
238Pu low-energy photon source rocking arm (6), middle activity
238Pu low-energy photon source rocking arm (8), little activity
238Pu low-energy photon source rocking arm (10), big activity
241Am low-energy photon source rocking arm (12), middle activity
241Am low-energy photon source rocking arm (14), little activity
241Am low-energy photon source rocking arm (16); Said each low-energy photon source rocking arm can be in 360 ° of angles of its perpendicular rocking-turn and move forward and backward and lock along the front end of each crossbeam, each crossbeam also can move up and down and lock along each column of low-energy photon source fixed cross beam group and column group (5) around its rear end; The long arm end of each low-energy photon source rocking arm is fixed with big activity respectively
238Pu low-energy photon source (7), middle activity
238Pu low-energy photon source (9), little activity
238Pu low-energy photon source (11), big activity
241Am low-energy photon source (13), middle activity
241Am low-energy photon source (15), little activity
241Am low-energy photon source (17); On the support (2) of low-energy photon source fixed cross beam group and column group (5) below, be fixed with a low-energy photon source group and deposit shielding platform (4); The upper surface that the low-energy photon source group is deposited shielding platform (4) is provided with six circular recessed basins of depositing low-energy photon source; When each low-energy photon source rocking arm straight down the time, six recessed basins of circle are corresponding with the position of each low-energy photon source; Diagnostic bed (21) are installed in each low-energy photon source
238Pu or
241Under the radiating sign X-ray of Am, and on the support of diagnostic bed (21) bottom, cartridge for photographic film (19) is set, cartridge for photographic film (19) is installed in low-energy photon source
238Pu or
241200mm---400mm position behind the human organ of the sign X-ray irradiation of Am; Around diagnostic bed (21), be provided with anti-scatter and shield (18) with the below of bottom cartridge for photographic film (19); Anti-scatter screen (18) all around also is provided with shielding protection plate (20) afterwards in diagnostic bed (21); Said diagnostic bed (21) adopt dry timber to process; Said anti-scatter screen (18) is aluminum---ferrum---aluminum composite three-layer plate structure; Said shielding protection plate (20) is aluminum---lead---ferrum composite three-layer plate structure; Said support (2) adopts metal material to process and lead ground connection is used in its bottom (22); It is the composite plate structure that wood-ferrum-lead-ferrum four layer materials are processed that said low-energy photon source group is deposited shielding platform (4); This X-ray machine also comprises accumulator battery (1), Dc low voltage power supply (24) and control type operating board able to programme (23), and control type operating board able to programme (23) and Dc low voltage power supply (24) and accumulator battery (1) are connected and control the switch and the button of each low-energy photon source.
2. nuclear energy medical x-ray machine according to claim 1 is characterized in that: said big activity
238Pu low-energy photon source (7) comprises that a bottom has the Stainless steel basin shape of a hollow circular hole to support (25), and a hollow round platform shielding overcoat of trapezoid rustless steel (37) is installed in the Stainless steel basin shape support (25) through the sunk screw group (38) of its bottom; The bottom of the hollow hole of the hollow round platform shielding overcoat of rustless steel (37) is trapezoidal, and the internal diameter of going to the bottom of this trapezoidal hollow hole is consistent with the internal diameter that Stainless steel basin shape is supported (25) hollow hole; In the upper flat top hollow hole of the hollow round platform shielding overcoat of rustless steel (37), shield overcoat (35) through the H96 pyrite screwed pipe that has been threaded; Top in the H96 pyrite screwed pipe shielding overcoat (35) is through the rustless steel shielding bolt (34) that has been threaded, and its underpart is equipped with
238Pu low-energy photon source (33); Said
238Pu low-energy photon source (33) comprise the monel metal pressure vessel,
238Pu radioactivity potsherd and exit window,
238Pu low-energy photon source (33) is threaded with H96 pyrite screwed pipe shielding overcoat (35) through the monel metal pressure vessel, and exit window is positioned at its bottom; Hollow hole at the hollow round platform shielding overcoat of rustless steel (37) that is positioned at H96 pyrite screwed pipe shielding overcoat (35) bottom is equipped with a H96 pyrite gate (32), and a lucite dust excluding plate (36) also is installed in the hollow hole under H96 pyrite gate (32); H96 pyrite gate (32) is connected with one slide (28) unshakable in one's determination; Last plane and the lower plane of (28) unshakable in one's determination of sliding is respectively equipped with the hollow round platform of rustless steel and shields top back-moving spring (29) and the middle part back-moving spring (27) that the outer surface of overcoat (37) is connected; Be installed on Stainless steel basin shape with (28) the corresponding sucking coil (26) unshakable in one's determination that slides and support on the edge horizontal plane of (25), the magnetic field gravitation that sucking coil when photoexposure (26) produces makes slide (28) unshakable in one's determination be slightly larger than to the distance that sucking coil (26) slides
238The external thread diameter of the monel metal pressure vessel of Pu low-energy photon source (33); The lower hollow trapezoidal walls intracavity of filling with the hollow round platform shielding overcoat of rustless steel (37) through the molten lead that temperature is higher than 330 ℃ forms a trapezoidal annulus of lead screen (30); On the inwall of the trapezoidal hollow hole in bottom of the hollow round platform of said rustless steel shielding overcoat (37), also be connected with an anti-scatter aluminium sheet funnel (31) through sunk screw;
Activity in said
238Pu low-energy photon source (9), little activity
238The overall structure of Pu low-energy photon source (11) and said big activity
238The overall structure of Pu low-energy photon source (7) is identical; Said big activity
241Am low-energy photon source (13), middle activity
241Am low-energy photon source (15), little activity
241The overall structure of Am low-energy photon source (17) also all with said big activity
238The overall structure of Pu low-energy photon source (7) is identical.
3. nuclear energy medical x-ray machine according to claim 1 and 2 is characterized in that: said control type operating board able to programme (23) comprises 6 single-phase DC solid-state relays, 6 sucking coils, 12 dropping resistors, 6 photoelectrical couplers, 8 toggle switch, 12 making buttons, 6 fuses, 1 single-pole switch, 1 Programmable Logic Controller PLC and 1 band switch; That Programmable Logic Controller PLC adopts is FX2N-32MR ES/UL; The A phase line is connected with N with the terminal L of PLC through the 220V alternating current of the first band switch moving plate (53) and zero line N; 24V terminal among the PLC is connected with the end of toggle switch KNX6, KNX7 and making button SB1, SB2, SB3, SB4, SB5, SB6 respectively; The other end of KNX6 and KNX7 is connected with X17 with the input terminal X0 of PLC again, and the other end of making button SB1, SB2, SB3, SB4, SB5, SB6 is connected with input terminal X1, X2, X3, X4, X5, the X6 of PLC respectively again; The 0V terminal that is connected with ground among the PLC is at first with the negative pole of the second band switch moving plate (54) and LED 0, LED1, LED2, LED3, LED4, LED5 and after connecing; Again with the signal input part negative pole of single-phase DC solid-state relay SSR0, SSR1, SSR2, SSR3, SSR4, SSR5 and connect; The positive pole of LED0 with after the positive pole of solid-state relay SSR0 input is connected again with after the end of dropping resistor R1 is connected, the other end of R1 is connected with the lead-out terminal Y0 of PLC; The colelctor electrode of the phototransistor T0 of photoelectrical coupler is connected with the 24V positive source, and the end of dropping resistor R0 is connected with ground, the non-earth terminal of R0 be connected with the input X7 of PLC again after the E utmost point E0 of T0 is connected; The 24V dc source is through the end of single-pole switch Q and fuse F U0, FU1, FU2, FU3, FU4, FU5 and connect; The other end of FU0 be connected with the end of making button SB7 again after the output head anode of SSR0 is connected; One end of the other end of SB7 and the negative pole of SSR0 and sucking coil (26) also connects; The other end of sucking coil (26) is connected with the end of KNX0, and the other end of KNX0 is connected with ground; The positive pole of LED1 be connected with the end of R3 again after the SSR1 input anode is connected, the other end of R3 is connected with the outfan Y1 of PLC; The colelctor electrode of the phototransistor T1 of photoelectrical coupler connects the 24V positive source, its E utmost point E1 be connected with the input X10 of PLC again after the end of R2 is connected, the other end of R2 joins with ground; The end of making button SB8 is connected the back and is connected with FU1 with the SSR1 output head anode; The other end of SB8 be connected with an end of sucking coil (55) again after the SSR1 negative pole of output end is connected; The other end of sucking coil (55) is connected with the end of KNX1, and the other end of KNX1 is connected with ground; The positive pole of LED2 is connected the back and is connected with the end of dropping resistor R5 with the positive pole of SSR2 input, the other end of R5 is connected with the outfan Y2 of PLC; The colelctor electrode of phototransistor T2 in the photoelectrical coupler connects the 24V positive source, its E utmost point E2 be connected with the input X11 of PLC again after the end of dropping resistor R4 is connected, the other end of R4 is connected with ground; The end of making button SB9 be connected with the positive pole of the outfan of SSR2 again after the end of FU2 is connected; The other end of SB9 be connected with an end of sucking coil (56) again after the negative pole of SSR2 outfan is connected; The other end of sucking coil (56) is connected with the end of KNX2, and the other end of KNX2 is connected with ground; The positive pole of LED3 be connected with the end of dropping resistor R7 again after the positive pole of SSR3 input is connected, the other end of R7 is connected with the outfan Y3 of PLC; The colelctor electrode of phototransistor T3 in the photoelectrical coupler is connected with the 24V positive source, its E utmost point E3 be connected with the end of dropping resistor R6 again after the input X12 of PLC is connected, the other end of R6 is connected with ground; The end of making button SB10 be connected with the end of FU3 again after the SSR3 output head anode is connected; The other end of SB10 be connected with an end of sucking coil (40) again after the SSR3 negative pole of output end is connected; Sucking coil (40) other end is connected with the end of KNX3, and the other end of KNX3 is connected with ground; The positive pole of LED4 be connected with the end of dropping resistor R9 again after the SSR4 input anode is connected, the other end of R9 is connected with the outfan Y4 of PLC; The colelctor electrode of the phototransistor T4 of photoelectrical coupler is connected with the 24V positive source, its E utmost point E4 be connected with the end of dropping resistor R8 again after PLC input X13 is connected, the other end of R8 is connected with ground; The end of making button SB11 be connected with FU4 again after the SSR4 output head anode is connected; The other end of SB11 is connected the back and is connected with an end of sucking coil (57) with the SSR4 negative pole of output end; The other end of sucking coil (57) is connected with the end of KNX4, and the other end of KNX4 is connected with ground; The positive pole of LED5 be connected with the end of dropping resistor R11 again after the positive pole of SSR5 is connected, the other end of R11 is connected with the outfan Y5 of PLC; The colelctor electrode of the phototransistor T5 of photoelectrical coupler is connected with the 24V positive source, its E utmost point E5 be connected with the end of dropping resistor R10 again after PLC input X14 is connected, the other end of R10 is connected with ground; The end of making button SB12 be connected with the end of FU5 again after the SSR5 output head anode is connected; The other end of SB12 be connected with an end of sucking coil (58) again after the SSR5 negative pole of output end is connected; The other end of sucking coil (58) is connected with the end of KNX5, and the other end of KNX5 is connected with ground.
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| US4066898A (en) * | 1976-04-12 | 1978-01-03 | The Dow Chemical Company | Method and apparatus for monitoring amount of a substance applied to a fabric |
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| US6928142B2 (en) * | 2002-10-18 | 2005-08-09 | Koninklijke Philips Electronics N.V. | Non-invasive plaque detection using combined nuclear medicine and x-ray system |
| CN101069090A (en) * | 2004-09-03 | 2007-11-07 | 杰克·E·朱尼 | Nuclear medical imaging device |
| CN201822861U (en) * | 2010-11-01 | 2011-05-11 | 周春生 | Nuclear energy medical X-ray machine |
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