CN102512188A - X-ray arrangement for the image representation of an examination object and use of the X-ray arrangement - Google Patents
X-ray arrangement for the image representation of an examination object and use of the X-ray arrangement Download PDFInfo
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- CN102512188A CN102512188A CN2011103515078A CN201110351507A CN102512188A CN 102512188 A CN102512188 A CN 102512188A CN 2011103515078 A CN2011103515078 A CN 2011103515078A CN 201110351507 A CN201110351507 A CN 201110351507A CN 102512188 A CN102512188 A CN 102512188A
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Abstract
For the high-contrast representation of small lesions or other target areas in tissue in the human body containing at least one contrasting chemical element, an X-ray arrangement is described, comprising at least one X-ray radiation source which emits essentially polychromatic X-ray radiation, a first detector or a plurality of first detectors, which can be used to determine values of a first intensity of X-ray radiation transmitted through the examination object, a second detector or a plurality of second detectors, which can be used to determine values of a second intensity of X-ray radiation emitted by the examination object, at least one correlation unit, which can be used to correlate the first intensity values of the transmitted X-ray radiation with the second intensity values of the emitted X-ray radiation pixel by pixel, and at least one output unit for the representation of the examination object from pixel signals obtainable by correlation of the first intensity values with the second intensity values. The transmission and emission images are preferably recorded simultaneously. The method can also be combined with other radiological images, e.g. positron emission tomography (PET) or single photon emission computer tomography (SPECT).
Description
The application is that the application number submitted on April 20th, 2006 is 200680019880.0, name is called dividing an application of " being used for the use that pictorial display is checked the X-ray apparatus and the X-ray apparatus of object ".
The present invention relates to be used for by means of the x x radiation x come pictorial display comprise at least a radiopaque chemical element the x x-ray apparatus of being checked object, x x-ray apparatus use and for example mammal, especially the people's is checked the imaging x ray comparison process of carrying out on the object.
By means of the medical diagnosis of x x radiation x is the field that is used for the development of the technology height of medical diagnosis on disease, for example is used for earlier detection, is used for radiophotography identification, is used to other pathological changes of characterizing and being used for tumor, angiopathy and human body.This technology very effectively and show high usability.
In order to produce the x x radiation x, the x ray tube that for example has W-, Mo-or Rh-rotating anode and Al-, Cu-, Ti-, Mo-and Rh wave filter is available.Use suitable filtering, the part of bremstrahlen is leached, and makes under favourable situation, and characteristic radiation occurs from the x ray tube basically.
About detector, use conventional x radiographic film, digiboard or digital flat panel (plat-bed) detector.In computerized tomography, use a strip detector line or a few strip detector line.Equally, several detector can be connected in parallel.In order to make the x x radiation x be directly changed into the signal of telecommunication; Use mainly by cadmium telluride (CT), tellurium zinc cadmium (CZT), amorphous salt or semiconductor detector (M.J.Yaffe amorphous or that crystalline silicon is formed; J.A.Rowlands; ' X-Ray Detectors for Digital Radiography, ' Med.Biol.
42(1) (1997) 1-39).
At US5,434, pointed out the instance of the design of this detector among the 417A.Same in order to make the energy sensitivities to detector become possibility, which floor detector formed by.Guiding has the x x radiation x of different-energy through the different depth in this detector; And said x x radiation x produces the signal of telecommunication through photoelectric effect in each layer, thereby can read this signal of telecommunication according to said layer and according to the energy of the x ray photons that can be identified as current impulse immediately.
Computer tomography (CT) is for a long time as the routine in the common clinical practice.Use CT, obtain faultage image, compare, use CT to realize better spatial resolution with using conventional projection photography through health.Although the density resolution of CT also apparently higher than the density resolution of conventional x ray technology, still needs contrast agent in order to detect many pathological changes reliably.Contrast agent has improved the quality of morphologic information.In this case, on the one hand, through contrast agent Presentation Function process (secretion, perfusion, permeability) in vivo, and on the other hand,, contrast given prominence to morphology (in various tissues different contrast concentration) through being provided.
In many cases, can not use conventional x ray technology, reason is the insufficient contrast of the tissue of examine.For this reason, developed the x ray-contrast media, it produces high radiophotography density in the tissue that they gather.Typically, suggestion is 32,42,44-52,54-60,62-79,82 and 83 element are as shading element (opacifying elements) and use the chelate of atomic weight as 56-60,62-79,82 and 83 element iodine, bromine and atomic weight.About iodine compound, for example can use meglumine sodium-or lysine-cardiografin (meglumine-Na-or lysine-diatrizoate), iothalamate (ester) (iothalamate), ioxithalamic acid, iopromide, iohexol, iomeprol, iopamidol, ioversol, iobitridol, iopentol, iotrolan, iodixanol and ioxilan (INN) (EP 0885616A1).
In some cases, although bestowed the x ray-contrast media, can not obtain enough tissue contrasts.In order to obtain correlated extra increase, introduced digital subtraction angiography (DSA), image subtracts each other with enhancing back image (logarithmic) each other before wherein strengthening.The image subtract that is used in the mammography is disclosed in EP 0885616A1: for the projection mammography; Suggestion at first record strengthens preceding mammary gland photography photo; About 30 seconds to 1 minute records strengthen back mammography photo then with urinary tract x ray-contrast media intravenous injection patient commonly used, and in injection end back.The couplet that will be relative to each other from the data that two images obtain then preferably subtracts each other each other.
New development in the CT field relates to excitation side, and the for example use of synchrotron radiation among the CT (F.A.Dilmanian, " Comupted Tomography with Monochromatic X-Rays ", Am.J.Physiol.Imaging,
314(1992) 175-193).For example obtain good x ray image, wherein used the absorptance that significantly increases in the binding energy of k electronics of atom by means of " the K edge subtracts shadow CT " (F.A.Dilmanian, op.cit, the 179th page).Elemental iodine has the K edge under the energy of 33.17keV.Unfortunately, this process only works under the help of the synchrotron radiation that can adopt the big storage ring that for example has DESY, and reason is to have only this radiation to have monochrome and the intensity useful to said process.Conventional x ray tube does not produce any monochromatic radiation but continuous spectrum.Therefore they are not easy to be fit to this species diversity measurement.
Another probability has been described:,, proposed a kind of process here, wherein used the x ray radiation source of two x ray anodes with different materials manufacturing in order to write down projection mammography photo in DE 10118792A1.In order to write down the mammography photo, at first the x ray-contrast media is bestowed the patient.Then, use in two x ray anodes first to write down first projected image, write down second projected image with the 2nd x ray anodes then.Through from overlapping with from each independent pixel of second image of each independent pixel of first image, create associated image then.The characteristic radiation of two x ray anodes is matched the absorption spectrum of x ray-contrast media: the emission energy of an x ray anodes is lower than the absorption ability of shading element in the x ray-contrast media slightly, and the absorption ability of a little higher than shading element of the emission energy of the 2nd x ray anodes.The defective of this process is such fact, that is, conventional x ray tube must only use an x ray anodes from double anode valve to replace.
In addition, for the transmission radiophotography, the emission radiophotography has been described also:
Thereby; In WO 2004/041060A2, described have probe be used for noinvasive in the body confirm the people prostate chemical element equipment, be used for exciting chemical element with the irradiation system that produces the radiation emission, be used to make the radiation detector in the probe of emitted radiation imaging and be used in signal record, processing and the display system of reproducing the amount of prostate chemical element corresponding to each point of emitted radiation imaging.Emitted radiation comprises fluorescent radiation in fact.With regard to prostate research, preferably confirm the distribution of Zn in the tissue.
In addition, in DE 3608965A1, the process of the ratio of various chemical elements in a kind of one deck of confirming the inspection area by means of gamma or x x radiation x has been described.In this case, detect Compton (Compton) and Rayleigh (Rayleigh) scattering radiation individually.Confirm that according to measured value the process of differential scattering coefficient receives the scale effect that is included in the various chemical elements in the independent pixel.Therefore, can confirm the ratio of these chemical elements according to them.For this reason; In the middle of many directions; Primary beam is conducted through the inspection area; And detect by the detector means the outside all places in inspection area in the radiation of leaving from the inspection area under the various angles, confirm the differential scattering coefficient of various burst transmissions thereafter according to the measured value of each pixel that is used for layer that obtains in this case.
And Quanwen, people such as Yu be at " Preliminary Experiment of Fluorescent X-Ray Computed Tomography to Detect Dual Agents for Biological Study ", J.Synchrotron Rad. (2001),
8, proposed in biomedical research, to use x ray fluorescence method to confirm the very non-radioactive substance of low concentration among the 1030-1034.By means of these methods, can obtain image, utilize said image, using fluorescence K in the blood flow in test example such as brain quantitatively and the single research of brain cell density
αLine can detect plurality of reagents simultaneously.In current research, will compare by means of these methods image that generates and the image that obtains by means of x transmission of radiation tomography.
Yet the defective that x ray fluorescence of in above-mentioned disclosing, describing or x ray scattering light method have is checked that it is unlikely that object develops on very little details, and reason is the imaging difficulty.On the contrary, only obtain high-resolution and develop, make less details be difficult to figure ground and develop.
Therefore, problem of the present invention is to avoid above-mentioned defective, especially finds the enough different radiopaque chemical elements of ability to produce the device and the process of image.In addition, also can write down the x ray image with simple, easy, no expensive mode.This technology is available on basis widely.Equally, the possible radiation dose with the enough minimums of ability makes the less pathological changes of being checked in the object visible with high-order bit resolution.Motion artifacts will be avoided.
Through the x x-ray apparatus of being checked object that comprises at least a radiopaque chemical element by means of the imaging of x x radiation x according to claim 1; The use of this x x-ray apparatus according to claim 11, and imaging x ray comparison process according to claim 25 has solved this problem.The preferred embodiments of the present invention have been described in the dependent claims.
If in description of the present invention and following claim, use a technical term " emission "; Should it be interpreted as so and comprise the x ray fluorescence on the one hand; That is, the radiation emission after exciting the raying material by means of electromagnetic radiation preferably includes rayleigh radiation on the other hand.Under latter event, emitted radiation once more under not from the situation of the burst transmissions of radiant matter, yet therefore, because the orbital electron in the atom of radiation can not resemble under the situation of fluorescence this material of generation is excited to excited state.
Utilize the x x-ray apparatus, use transmission through being checked object the x x radiation x and from being checked that the x x radiation x that object is launched carries out pictorial display.For this reason, x x-ray apparatus according to the present invention has following characteristic:
A. at least one x ray radiation source, it launches pleochroic x x radiation x in fact;
B. first detector or first detector cell (unit comprises the several detectors that are connected in parallel and/or arrange) are used for confirming first intensity level of the x x radiation x of transmission through being checked object;
C. second detector or second detector cell are used for confirming second intensity level from the x x radiation x of being checked the object emission;
D. at least one correlation unit, be used to make transmission the x x radiation x first intensity level and the x x radiation x of launching second intensity level each other by pixel be associated; And
E. at least one output unit, it is used for being checked that according to making through the picture element signal that first intensity level is associated with second intensity level obtain object develops.
Can simultaneously or detect the x x radiation x of transmission and the x x radiation x of launching in succession.
This x x-ray apparatus can be advantageously used in by means of the x x radiation x to come being checked that object carries out pictorial display, and this is checked that object preferably comprises at least a radiopaque chemical element.The radiopaque chemical element preferably is incorporated into by the x ray-contrast media and is checked in the object, and for example bestows the object of being checked such as the human or animal for this reason.
The shading chemical element with low atomic weight of Lock-in only has a spot of x ray fluorescence in being checked object, makes to use these element imagings to seem also infeasible.In addition, the energy of x ray fluorescence photon is low in this case, makes that their sphere of actions in bodily tissue are little.Especially, from the line of departure be 28.6 with the beginning of the elemental iodine (Z=53) of 32.3keV, to leave the photoluminescence line of being checked the enough distances of object be obtainable and thereby can be by device in the outside detector recording of object.Under the situation of the chemical element of low atomic weight, can select the layout of second detector, wherein second detector arrangement is become as close as possible examine zone (ROI: area-of-interest).
According to the present invention, X-ray apparatus is used to carry out x ray comparison process.Said process comprises following process steps:
A. preferably bestow at least a radiopaque chemical element;
B. checked object with pleochroic in fact x x radiation x irradiation;
C. confirm first intensity level of the x x radiation x of transmission through being checked object;
D. confirm by second intensity level of being checked the x x radiation x that object is launched;
E. first intensity level of the x x radiation x of transmission is associated with second intensity level of the x x radiation x of launching with pursuing pixel;
F. according to coming being checked that object develops through the picture element signal that first intensity level is associated with second intensity level obtain.
Compare with the known method of only carrying out x transmission of radiation tomography (TXCT) or only detecting x ray fluorescence (FXCT); Here simultaneously or measure transmission and emission in succession; And these two kinds of technological combinations with one another according to the present invention; Wherein in this case, carry out overlapping through suitable correlated process to the image that obtains respectively.In this program, use the advantage separately of two kinds of technology:
That is to say that x transmission of radiation tomography can provide the advantage of high-spatial and temporal resolution, make in principle, can also tell minimum pathological changes or other details in examinate's body.Yet the insufficient contrast that often obtains is so that these details are visible.This is particularly useful for the test of pathological changes in the soft tissue.In addition, also receiving skeleton with some body region of TXCT process check hinders.
By comparison; X ray fluorescence tomography provides the advantage of high contrast radiography; Reason is that only some chemical element issues the radio magnetic radiation suitable the exciting of these elements, makes these elements of in inspection area (ROI), finding be suitable for as tetchy measuring probe.Yet the FXCT method has the defective of low spatial resolution, makes less pathological changes is developed.
Only the intensity level of the intensity level of the x x radiation x through making transmission and the x x radiation x of launching by pixel be associated; And according to the picture element signal that obtains through being associated to being checked the development of object, can be produced the detail image of the high-contrast that receives inspection area (ROI).That is to say that light-blocking image partly has low resolution.Yet because necessary details are derived from the radiating intensity level of measuring by means of TXCT, therefore through making each value couplet that be relative to each other, this defective obtains rectification to a great extent.
The present invention can be used in particular for the scrutineer.The present invention is suitable for producing the radiograph that is used to make agglomerate, blood vessel and perfusion development; For example be used to make esophageal-gastric intestinal passage to develop; Be used for bronchography, gallbladder radiography, angiography and angiocardiography; Be used for CAG and be used for the perfusion measurement, be used for mammography and be used for lymphography.The focus of application project of the present invention is computer tomography (MS-CT; μ CT) and merge mode (other method of PET-CT (PET), SPECT (single photon emission computed tomography), ultrasonic examination and optical imagery).In principle, the present invention also can be used in the non-living material of research, for example in the testing of materials field.
In order to carry out inspection, write down by the transmitted radiation of being checked that object is decayed by means of first detector in the course of the beam that is located at the x ray tube.By means of being arranged in outside this course of the beam, preferably become the second detector measures emitted radiation at about 90 ° of angles with course of the beam.Yet, can not be conducted through under the detected situation of the beam of being checked object in principle, arrange this second detector with any other position, angle with respect to the x beam, for example become 45 ° or 135 ° with the beam that begins from the x ray radiation source.If find the x ray tube at 12 o ' clock positions, the common computer tomography is equipped with a series of detectors at 6 relative o ' clock positions so.Second detector preferably can be arranged in 3 o ' clock positions and/or 9 o ' clock positions.By means of this second detector, can write down x ray fluorescence and x ray scattering (Rayleigh scattering, Compton scattering).
For with having used second detector of the x x radiation x of launching to come optionally detected image, can measure the energy of emission x x radiation x with distinguishable mode.In being checked object, exist under the situation of predefined emission chemical element; It is particularly advantageous in differentiation by the x x radiation x that is derived from this shading element of second detector recording and other the x x radiation xs launched and the fluorescent radiation that is derived from other chemical elements from for example scattering radiation (Compton radiation, rayleigh radiation).Thereby make and might make some zone (ROI) highly selective visible through the concentration that for example in some organ of human body, increases the shading chemical element, so that producing high especially contrast tissue, it is visible that this tissue is compared with surrounding tissue.Equally, the structure from the pictorial display that skeleton produces is compared unimportantly with the development of tissue in this case, makes skeleton in fact can show by jamming pattern.
In order to detect and characterize emitted radiation, preferably use the energy dispersion detector.Yet also possibly use simpler detector for this reason, and guarantee the sign of launching by x ray optics module (filter combination, monochromator).
In addition, this principle can apply to the intensity level with the x x radiation x of the first detector measures transmission in the same manner.Equally, in this case, realize the selectivity of being checked shading chemical element rich region (ROI) in the object is developed.
Therefore, can also the soft tissue in the human body for example be developed with high-contrast of the present invention.The x x radiation x through making the transmission that detector writes down and the energy or the energy range of the x x radiation x of launching are coordinated with the type of shading chemical element mutually, compare effective increase that can realize contrast with conventional process.
In order to produce the x x radiation x, can use general goods x ray tube, for example has the anodic pipe of Mo, W or Rh with continuous spectrum.The voltage range that the emission of continuous radiation is become possibly apply is up to for example surpassing 100keV, and this depends on the type that is included in the shading chemical element of being checked in the object.
In principle, can operation x ray radiation source under the filtering situation be not being carried out in emitted radiation, so that polychromatic radiation appears in the overall optical spectral limit of being checked on the object.Yet, in order to reduce the radioactive exposure of being checked object, also possibly from the spectrum of heterogeneous x rays radiation source, leach this x x radiation x, its energy is inessential or not favourable for detecting.For this reason, for example use Al or Cu wave filter, it leaches the energy (soft radiation) of scope for≤20keV.Thereby continuous spectrum is defined as scope at >=0keV, and is preferred >=15keV, especially preferred >=17keV; And very especially preferably >=20keV; For example, wherein compare, do not stress the spectral region in these limits or get rid of other scopes with other up to the x x radiation x of 100keV.The upper limit of emission spectra is confirmed by the voltage that is applied to the x ray anodes.Preferably leach radiating low-yield scope to eliminate the dosage coherent radiation of human body.
Usually, checked object with the heterogeneous x rays radiation by suitable detector.Alternatively, the energy dispersion detector can also be used for confirming the energy of incident photon.
About energy dispersion detector and detector cell, available in principle two kinds of designs:
A. according to the energy dispersion detector of the type of Cd (Zn) Te detector, of the preface part of description.Use this detector series, can measure the x ray spectrum of emission x x radiation x by pixel ground.
B. use simple x ray detector.Comprise that under the simplest situation the descriminator of suitable filters combination is arranged in the front of detector.Yet select for energy, also can use monochromator, for example regulate this monochromator according to the x ray fluorescence of bestowing contrast agent.
Yet c., also make detector directly be suitable for contrast agent technically probably.Thereby, can use Gd (Zn) Te detector or Dy (Zn) Te detector.
In all cases, the feasible Compton scattering of measuring minimum of positioning detector as far as possible.
In order to confirm intensity level and, photon to be detected be divided at least two different-energy scopes that it for example comprises K by the energy of being checked the x x radiation x that object is launched
αAnd K
βThe line of departure.In order to increase the element specificity, can carry out the Compton alternatively and correct.Yet instance as will be described as further below is said, and this is always necessary.
If ignore the contrast of intrinsic x ray, can the x ray-contrast media be bestowed and checked object, people for example is to carry out according to process of the present invention.For example can especially bestow the x ray-contrast media through intestinal or without intestinal through intravenous, intramuscular or subcutaneous injection or infusion.Then, obtain the x ray image.These those contrast agent that in selected SPECTRAL REGION, show high attenuation quotient are suitable.Its absorption element has the K edge of absorption spectrum in selected spectral region contrast agent also is specially suitable.This x ray-contrast media comprises the shading chemical element; Its atomic weight is 35 or greater than 35 (in this case; This is the bromated contrast agent of bag), atomic weight be 47 or greater than 47 (in this case, these are the contrast agent that comprises iodine), atomic weight be 57 or greater than 57 (in this case, this is the contrast agent that comprises lanthanide series; Especially the contrast agent that comprises gadolinium) or atomic weight be 83 (in this case, these are the bismuthiferous contrast agent of bag).Therefore, comprising atomic weight is that the x ray-contrast media of 35 (bromines) to the shading chemical element of 83 (bismuths) is suitable.Especially suitable is, and to have atomic weight be the contrast agent of 53 (iodine) to the shading chemical element of 83 (bismuths).Also suitable is, and to have atomic weight be 57 or greater than the contrast agent of 57 (lanthanide series) to the shading chemical element of 83 (bismuths), and especially preferred be to have the contrast agent that atomic weight is the shading chemical element of 57-70 (lanthanide series: La, Ce, Pr, Nd, Pm, Sm, Eu, Gd, Tb, Dy, Ho, Er, Tm and Yb).
The suitable iodine x ray-contrast media that contains is such as the chemical compound that comprises the triiodo aromatic, for example the U.S. alcohol of amidotrizoic acid, iohexol, iopamidol, iopanoic acid, iopodic acid (iopodinic acid), iopromide, iopronic acid, iopydone, iotalamic acid, iopentol, ioversol, Ioxaglic Acid, iotrolan, iodixanol, iotroxic acid, ioxaglic acid, ioxithalamic acid and iodine (INN).Containing iodine x-ray contrast agent trademark name?
(Schering),?
(Schering),?
(Schering),?
(Schering) and?
(Schering).
What also be suitable as contrast agent is metal complex, for example Gd-DTPA (
(Schering)), Gd-DOTA (Gadoterate, Dotarem), Gd-HP-D03A (Gadoteridol;
(Bracco)), Gd-EOB-DTPA (Gadoxetat, Primavist), Gd-BOPTA (Gadobenat, MultiHance), Gd-DTPA-BMA (Gadodiamide;
(Amersham, Health)), Dy-DTPA-BMA, Gd-DTPA-polylysine and Gd-DTPA-series connection polymer, wherein DTPA=diethylene triamine pentacetic acid (DTPA); DOTA=1,4,7; 10-four nitrogen tetraacethyl cyclododecanes, HP-D03A=10-(hydroxypropyl)-1,4; 7,10-tetraazacyclododecanand-1,4; The 7-triacetic acid, EOB-DTPA=3,6; 9-three nitrogen-3,6,9-three (carboxymethyl-4-(4-ethoxy benzyl) hendecane dicarboxylic acid); BOPTA=(4-carboxyl-5,8,11-three (carboxymethyl)-1-phenyl-2-oxa--5; 8; 11-three azepine tridecane-13-oic, benic acid), DTPA-BMA=diethylene triamine pentacetic acid (DTPA) ester-two (Methanamides); DTPA-polylysine=diethylene triamine pentacetic acid (DTPA) ester-polylysine, the DTPA-polymer of connecting.
Can bestow the x ray-contrast media through intestinal or without intestinal.Under situation about bestowing, preferably select vein (i.v) to bestow without intestinal.Preferred dose is the dosage that contains the iodine non-ionic contrast medium in the I/kg body weight up to 0.75g.This is corresponding to the I/kg body weight of about 6mmol.In addition, said dosage can preferably be increased to the I/kg body weight (corresponding to the about I/kg body weight of 12mmol) of 1.5g and under special circumstances up to the I/kg body weight of 2 (corresponding to about 16I) or 5g (corresponding to the about I/kg body weight of 39mmol).Under the situation of lanthanide complexes, preferred dose is about 0.1mmol/kg body weight.Up to the 0.3mmol/kg body weight or up to the dosage of 1mmol/kg body weight is suitable, and also is preferred in addition.
The line of departure of gadolinium is about 43.0 and 48.7keV, and promptly far above the line of departure of iodine, it is about 28.6 and 32.3keV.Replace the gadolinium atom, metal complex also can comprise for example every other lanthanide series, for example lanthanum, dysprosium or ytterbium.
Digital detector provides a period of time (for example: The BBI newsletter, in February, 1999, the 34th page by various manufacturers; H.G.Chotas, J.T.Dobbins, C.E.Ravin; " Principles of Digital Radiography with Large-Area; Electronically Readable Detectors:A Review of the Basics, " Radiol., 210 (1999) 595-599).They usually comprise amorphous silicon or other semi-conducting materials.In x x-ray apparatus according to the present invention; Following detector is suitable: the detector with phosphorus plate is (for example from Fuji Chemical Industries; Konica), the detector that has amorphous silicon is (for example from GE Medical; Philips Medical; Siemens Medical), have salt detector (for example from Philips Medical, Toshiba), have the detector (for example from Kodak) of thiosulfuric acid gadolinium, have cadmium telluride (CT) or the semi-conductive detector of tellurium zinc cadmium (CZT), have yttrium silicate detector, have the silicic acid lutecium detector, have the detector of sodium iodide or bismuth germanium oxide.Use so-called C (Z) T detector, promptly realize especially good result by the detector that cadmium-(zinc)-tellurium-(C (Z) T) quasiconductor is formed.
At US 5,434, describe the design of the energy dispersion detector that forms by quasiconductor among the 417A in detail.In this case, dividing semiconductor band with x x radiation x irradiation from the front is provided.Radiation is conducted through semi-conducting material and interacts up to it and semi-conducting material.Penetration depth depends on the energy of x ray photons.With compare with more low-energy x ray photons, under situation than the x ray photons of macro-energy, radiation by guiding deeper through interacting up to it and detector material and through photoelectric effect generation current impulse.Can be by means of the release current pulse in the independent fragment of detector that electrically contacts that applies.Handle current impulse with input amplifier.
On the one hand, detector can be designed to the form of flat-panel detector.In this embodiment, all pixels are to be detected simultaneously and be delivered to correlation unit evaluation.In this case, the independent detecting sensor that detector is arranged by large tracts of land is formed, preferably to have the matrix form of this pick off of row and column.
In addition, a kind of detector cell can also be provided, it is used for confirming emission x x radiation x and writes down the emission image alternatively, and is designed to have the x ray optics module that is used for the energy selection for this reason.
Replace flat-panel detector, can also use to be suitable for obtaining the thread detector of single pixel or the matrix of several detectors.Under the situation of nearest detector, send simultaneously from the x x radiation x of being checked object via x ray fibre-optic light guide.Many this fibre-optic light guides are combined into surface detectors.
In addition, detector can be designed to obtain independent pixel and can be movably to obtain all pixels.In this embodiment, detector can only detect the energy dependence intensity in the independent pixel during measuring.Test example is like the independent intensity of pixel line by line in succession, and it is delivered to correlation unit further handles.
In addition, detector can also have the array that is designed for the detector sensor of obtaining pixel in each case, and can be movably to obtain all pixels.According to the present invention, the detector sensor of the detector sensor of arranging of being in line and another layout of arranging such as rectangular is defined as the array of detector sensor.In this embodiment, detector line by line or alternatively also block-by-block ground detect the intensity level in the independent pixel.In order to obtain all intensity levels, detector is preferably perpendicular to the main axle moving of array during measuring.The intensity level that to during measuring, confirm is transferred to correlation unit.
For example for the distribution of pictorial display shading chemical element in being checked object, advantageously use identical weight detection radiant intensity in all cases, said radiant intensity is launched by space element separately.In addition, for this reason, also advantageously making separately in each case, the space element white, quiet clothes carry the identical radiant intensity from the x ray radiation source.In fact; These accuracies result only is ballpark, and reason is on the one hand, and the x x radiation x of irradiation is attenuated through absorption in varying degrees; This depends in being checked object what to be from radiating distance; And on the other hand, the radiation of being launched by the space element of being checked in the object is attenuated through self-absorption in varying degrees, and this depends on how many space element and distances between the detector in being checked object be.
This problem occurs in all emission-spectrographic techniques.In order to address this problem; Consider absorption and/or the self-absorption of the x x radiation x in being checked object, launched of the x ray of irradiation; At first correct second intensity level, and only after this correction first and second intensity levels each other just by pixel be associated.Can be checked the geometry of object and considered that simultaneously this correction is carried out in the digital processing of the relevant x ray of apparent position opacity at least by means of utilization.In order to confirm that the position relies on x ray opacity, can use the image that generates from first intensity level.Absorb and self-absorption in order to confirm that the position relies on, relying on x ray opacity from this position of measuring acquisition can be as baseline the first approximation, and reason is the absorptance that the absorptance of irradiation x x radiation x is similar to emitted radiation.
Because the self-absorption of emitted radiation; The structure heterogeneity in the object is checked with compensation in the position and the position, angle of further advantageously during measuring, for example on circular split path, moving second detector with respect to inspection area (ROI), and said structure heterogeneity depends on that viewing angle and point of observation have the variable absorption effect.In this case, will after the correction of the self-absorption of carrying out through averaging, obtain pictorial display.
The signal that will be derived from input amplifier then sends at least one correlation unit, uses said correlation unit that the image of the x x radiation x of launching from the intensity of being checked the detected x x radiation x of object pixels and same pixel (x ray scattering and x ray fluorescence) is associated.Correlation unit can be corresponding data programmed processing unit.
For the intensity level of the photon that makes two kinds of mode (transmission image with emission image) is associated, the couplet that is relative to each other preferably subtracts each other or is divided by each other with making two kinds of mode one next pixels each other.For this reason, can use comparator in one case, and under another kind of situation, can use with pursuing pixel except that an execution correction.Certainly, also can carry out other mathematical operations to be used to correct transmission and the intensity level of launching the x x radiation x from image.
For the measured intensity value of processed pixels, the following equipment that can in data processing unit, carry out preferably is provided, that is:
D1. first memory element can be pursued first intensity level of pixel ground storage transmission x x radiation x by enough its,
D2. second memory element can be pursued second intensity level of pixel ground stored transmit x x radiation x by enough its, and (for example, having element I, Gd and Yb),
D3. computing unit, it provides two to generate the suitable relevant of image data sets, and thereby from transmission data set with from the x ray emission, the information of the data of preferred x ray fluorescence generates or the computed image data set.
As a result, possibly make all intensity values of pixels couplet that be relative to each other in transmission and the emission, wherein, make the emission image adapt to the contrast agent of use via the characteristic line of departure.If (for example use by the x ray-contrast media;
and
) or comprise the mixture that the material of iodine and lanthanide series (for example Gd or Dy) is formed; The line of departure that is characteristic so in each case can be used in the emission imaging; Wherein measurement data set is associated with pursuing pixel each other and is used for pictorial display then; Perhaps wherein alternatively; Intensity level is associated with pursuing pixel each other separately, and the data that obtain then are used for pictorial display.For this reason, with data one next pixel that obtains be transported to output unit, said output unit for example comprises monitor (CRT or LCD display) or diagraph.
For the present invention is explained in more detail, use following figure and instance.For the direct diagram that provides the present invention how to work, under any circumstance can not attempt to correct the measurement of x ray spectrum according to the absorption and the self-absorption of exciting beam.Here, specifically:
Fig. 1 has shown the image of the test set in the computer tomography;
Fig. 2 has shown that experiment is provided with or the diagram of imaging device shows;
Fig. 3 has shown that the diagram that is used to produce the test set that first prosthese measures shows;
Fig. 4 has shown and is filled with water (Fig. 4 a);
(Fig. 4 b); The emission spectra of the prosthese of the Fig. 3 of
(Fig. 4 c);
Fig. 5 shown be filled with water (Fig. 5 a), the emission spectra of the prosthese of Fig. 3 of
(Fig. 5 b),
(Fig. 5 c); Wherein in each case, be that the PMMA dish of 5cm is arranged between detector and the prosthese with thickness;
Fig. 6 has shown based on the position/displacement of the prosthese of Fig. 3 at the selected intensity of launching in (corresponding to K α and K β the line) (iodine: Fig. 6 a, gadolinium: Fig. 6 b, the mixture of being made up of iodine and gadolinium: Fig. 6 c) of being with;
Fig. 7 has shown the CT faultage image (transmission image) of the prosthese that is filled with Gd, iodine/Gd mixture, iodine, air and water.
In Fig. 1, shown the photographic process of the test set in the computer tomography with glueballs 1, said glueballs 1 is fastened to support 2.Glueballs is arranged in the center of computer tomography.In various tests, glueballs is filled with air, water and different contrast agent solution.Manage (on glueballs at CT; Demonstration) and between the thread detector (under visible estrade under the glueballs, invisible) find said ball.
For the detection of x ray fluorescence, with and CT pipe, glueballs and detector between connecting line at an angle of 90, location survey chamber 3.Use and should experiment be provided with, the tissue, tumor or the analog that are filled with contrast agent are modeled to the checked object of being checked in computer tomography.For this reason, the said object of layering ground scanning, and measure scattering spectrum in this case.
The experiment setting of in this test, using is shown in greater detail among Fig. 2.The sketch map has here shown ball 1, and it is considered to be in the prosthese in the isocenter of frame 4.CT pipe 5 is arranged in 12 o ' clock positions and remains fixed in the there.With with the directed at an angle of 90 measuring chamber 3 that comprises detector 6 and lead pipe 7 of x ray conical beam, said conical beam produces from the CT pipe and arrives prosthese (ball) (along the z direction; Referring to arrow).
In order to detect the x x radiation x, use CZT detector 6 with 3mm * 3mm * 2mm cadmium zinc telluride crystal and 100/400 μ m perforate (Amptek, Inc., USA).Via amplifier the fluorescence detector recorded data is sent to MCA 9 from detector, and delivers to
that be stored on the PC10 (Microsoft) electrical form then.Thereby can obtain signal intensity SI=SI (E) as the function of energy E with digital form.
In Fig. 3, shown to be used to produce schematically showing of test set that first prosthese measures.Can see that measuring chamber 3 is used to measure the part of fluorescence in the left side that shows, and ball 1 is shown in the center of demonstration.By being created in vertical independent cross section Fig. 3 from top incident x ray fan beam, fluorescence gets into measuring chamber from this independent cross section.Dashed lines labeled the CT pipe position separately on profile image.Horizontal scale is indicated the displacement of fan beam and is therefore indicated the cross section (excitation layer) that is addressed in each case in the ball.
At+45mm and therefore carry out " zero measures " in the outside of excitation beam.
After each spectra re-recorded, whole measurement structure is moved further 10mm (along the z direction) in frame, and writes down new spectrum.Thereby, produce various spectrum based on the position separately of ball in the beam or corresponding to the geometry of sphere shape hierarchy.
Use this measurement structure, thereby can be based on the topography structure measurement x ray fluorescence of prosthese, wherein at the z=-60mm place; Near the layer of detector by irradiation, and at z=0, away from the layer of detector by irradiation (thereby; The self-absorption minimum of emission at the z=-60 place, and maximum at the z=0 place; Because spherical geometries, therefore make the absorption effect of irradiation remarkable) at higher contrast concentration place.Example 1:
In first measures, the water filling ball, and corresponding to each position of the ball in the beam of Fig. 3, at 89kV, this ball of each 80s ground measurement (parameter: detector: XR-100.CZT (perforate 0.1mm), ball-detector distance: 18.0cm under the 50mA; Ball-CT manages distance: 32.0cm).
In Fig. 4 a, described the scattering spectrum of water in the prosthese for each position.
In second measures; Iodine aqueous solution
filling ball with 50mmol/l; And for each position; At 80kV, this ball (parameter: detector: XR-100.CZT (perforate 0.1mm)) is measured on each 80s ground under the 50mA.
Reproduced the emission spectra that obtains in each position among Fig. 4 b.Can be clear that K α and the K β line (28.6 and 32.3keV) of iodine.According to this chart, the measured intensity of x ray fluorescence is tangible to the dependency of the geometry of prosthese.The irradiation layer of prosthese is big more, and measured intensity is high more.
In the 3rd measures; Gadolinium aqueous solution
filling ball with 50mmol/l; And for each position; At 80kV, this ball (parameter: detector: XR-100.CZT (perforate 0.1mm)) is measured on each 80s ground under the 50mA.
In Fig. 4 c, reproduced the emission spectra that obtains in each position.Can be clear that the K of gadolinium
αAnd K
βLine (43.0 and 48.7keV).The result shows especially that in K line scope the intensity of measuring emitted radiation depends on the geometry of ball in the radiation field.
Example 2:
In the independent measurement of this test, in each case that 5cm is thick PMMA dish is placed between detector and the prosthese as wave filter, with the self-absorption of simulation x ray fluorescence radiation through surrounding tissue.
In Fig. 5 a, described the scattering spectrum of water in the prosthese for each position.
In second measures; Iodine aqueous solution
filling ball with 50mmol/l; And for each position; At 80kV, this ball (parameter: detector: XR-100.CZT (perforate 0.1mm)) is measured on each 80s ground under the 50mA.
In Fig. 5 b, reproduced the emission spectra that obtains in each position.The intensity of fluorescent radiation reduces owing to inserting the PMMA dish.Empirical tests, it is low more to coil thick more intensity.Yet even in the maximum layer of ball (at the center), the K line is still measurable.
In the 3rd measures; Gadolinium aqueous solution
filling ball with 50mmol/l; And for each position; At 80kV, this ball (parameter: detector: XR-100.CZT (perforate 0.1mm)) is measured on each 80s ground under the 50mA.
In Fig. 5 c, reproduced the emission spectra that obtains in each position.Equally here, fluorescent radiation reduces owing to inserting the PMMA dish.Because the K of gadolinium
αAnd K
βLine is approximately 43.0 or 48.7keV, therefore with under the situation of foregoing iodine emission compares, and under the situation that has the thick PMMA dish of 5cm, can detect the fluorescent radiation of remarkable greater strength.Therefore, even in this case, the K line still can be measured in (at the center) in the maximum layer of ball.
Example 3:
In another test,, confirm and record intensity of fluorescence value based on the location of ball with respect to the x ray beam.
In first measures; Iodine aqueous solution
filling ball with 50mmol/l; And for each position; At 80kV, this ball is measured on each 80s ground under the 50mA.
In Fig. 6 a, based on the intensity that fluorescent radiation has been drawn in the position/displacement of prosthese in selected can being with, this selectes the K that can be with corresponding at the iodine of 28.6keV
αLine and at the K of the iodine of 32.3keV
βLine.Can detect scattergram according to this figure by the emissive porwer that shape produced of ball.
In second measures; Gadolinium aqueous solution
filling ball with 50mmol/l; And for each position; At 80kV, this ball is measured on each 80s ground under the 50mA.
In Fig. 6 b, based on the intensity that fluorescent radiation has been drawn in the position/displacement of prosthese in selected can being with, this selectes the K that can be with corresponding at the gadolinium of 43.0keV
αLine and at the K of the gadolinium of 48.7keV
βLine.Also can detect scattergram according to this figure by the emissive porwer that shape produced of ball.
In the 3rd measures; With the iodine
of 25mmol/l and gadolinium aqueous solution
filling ball of 25mmol/l; And for each position; At 80kV, this ball is measured on each 80s ground under the 50mA.
In Fig. 6 c, based on the intensity that fluorescent radiation has been drawn in the position/displacement of prosthese in selected can being with, this selectes the K that can be with corresponding at the iodine of 28.7keV
αLine, at the K of the iodine of 32.3keV
βLine, at the K of the gadolinium of 43.0keV
αLine and at the K of the gadolinium of 48.7keV
βLine.In Fig. 6 c, can see, in direct drafting, be not enough to reproduce the ball scattergram as the signal intensity of position function.This maybe be owing to the absorption of excitation side and the self-absorption of transmitting party, and this makes image fault.Lower contrast concentration and the pictorial display that the correction of the self-absorption of the absorption of former beam and x ray fluorescence has been caused ball on a dimension.
Example 4:
Fig. 7 has shown the CT faultage image that writes down in the x ray fluorescence instance formerly.From upper left and bottom right, can see the ball, the ball that is filled with the mixture of forming by gadolinium and iodine that are filled with gadolinium, be filled with the ball of iodine, the ball that is filled with the ball of pure water and is filled with air.Inflatable ball has minimum x ray attenuation significantly, is the water-filling ball afterwards.When use has the ball of shading element of 50mmol/l, to compare with the water-filling ball, the x ray attenuation is more remarkable; (Hounsfield units HU) enough carries out quantitative assessment really surely, the ball of filling element-specific is assessed with regard to allowing but only add x ray fluorescence image via the CT pad value.
Claims (33)
1. one kind is used for being checked that object carries out the X-ray apparatus of pictorial display; Wherein this is checked that object comprises at least a radiopaque chemical element; This X-ray apparatus is checked the x x radiation x of object and is carried out said pictorial display by the said x x radiation x of being checked that object is launched that through said said x x-ray apparatus comprises by means of transmission:
A. at least one x ray radiation source, it launches pleochroic x x radiation x in fact;
B. first detector or first detector cell are used for confirming that transmission is through said first intensity level of being checked the x x radiation x of object;
C. second detector or second detector cell; Be used for definite from said second intensity level of being checked the x x radiation x of said at least a radiopaque chemical element emission that object comprises; Wherein, said second detector or second detector cell are arranged to as close as possible examine zone;
D. at least one correlation unit, be used to make said transmission the x x radiation x said first intensity level and the said x x radiation x of launching said second intensity level each other by pixel be associated; And
E. at least one output unit, it is used for according to through making said first intensity level picture element signal that obtains that is associated with said second intensity level that the said object of being checked is developed.
2. x x-ray apparatus according to claim 1 is characterized in that, said correlation unit has following equipment:
D1. first memory element is used for said first intensity level by the x x radiation x of the said transmission of pixel ground storage;
D2. second memory element is used for said second intensity level by the said x x radiation x of launching of pixel ground storage;
D3. computing unit, be used to make said transmission the x x radiation x said first intensity level and the said x x radiation x of launching said second intensity level each other by pixel be associated.
3. x x-ray apparatus according to claim 1 wherein, can detect said second intensity level with distinguishable mode based on the energy of the said x x radiation x of launching.
4. x x-ray apparatus according to claim 1; Wherein, Utilize said second detector or utilize said second detector cell; Can distinguish mutually with the x x radiation x that other are launched being included in the said x x radiation x of being checked that the shading chemical element in the object is launched according to the energy of x x radiation x.
5. x x-ray apparatus according to claim 1; Wherein, Checked in the object the absorption of the x x radiation x of irradiation and/or pro-carried out in the self-absorption of the said x x radiation x of launching correct according to considering said, can make said first intensity level and said second intensity level each other by pixel be associated.
6. x x-ray apparatus according to claim 1, wherein, said first and/or said second detector be flat-panel detector.
7. according to the described x x-ray apparatus of one of claim 1-5, wherein, said first and/or said second detector be designed to obtain independent pixel and can move to obtain all pixels.
8. according to the described x x-ray apparatus of one of claim 1-5, wherein, the detector cell that is designed to have the x ray optics module that is used for the energy selection is provided, to detect the said x x radiation x of launching.
9. according to the described x x-ray apparatus of one of claim 1-5; Wherein, Said first and/or the array of said second detector with detector sensor, said detector sensor is designed to obtain in each case pixel and can moves to obtain all pixels.
10. according to the described x x-ray apparatus of one of claim 1-5; Wherein, Said x x-ray apparatus uses such as PET (PET), single photon emission computed tomography (SPECT) and ultrasonographic other radiology formation methods, and optical imaging method.
11. a use is carried out the method for pictorial display according to the described x x-ray apparatus of one of claim 1-10 to checking object, comprises the steps:
A. checked that to this object provides at least a radiopaque chemical element;
B. come the said object of being checked of irradiation with pleochroic in fact x x radiation x;
C. confirm that transmission is through said first intensity level of being checked the said x x radiation x of object;
D. confirm by second intensity level that is provided for the said x x radiation x that said said at least a radiopaque chemical element of being checked object launches;
E. said first intensity level of the x x radiation x of said transmission is associated with said second intensity level of the said x x radiation x of launching with pursuing pixel; And
F. according to through making said first intensity level picture element signal that obtains that is associated with said second intensity level come the said object of being checked is developed.
12. the method for the said x x-ray apparatus of use according to claim 11 wherein, based on the energy of the said x x radiation x of launching, can be measured said second intensity level with distinguishable mode.
13. the method for the said x x-ray apparatus of use according to claim 11 wherein, according to x x radiation x energy, is distinguished with the x x radiation x that other are launched being included in the said x x radiation x of being checked that the shading chemical element in the object is launched mutually.
14. the method for the said x x-ray apparatus of use according to claim 11; Wherein, Correct according to considering said the inspection in the object to the absorption of the x x radiation x of irradiation and/or to the pro-that the self-absorption of the said x x radiation x of launching is carried out, make said first intensity level and said second intensity level each other by pixel be associated.
15. the method for the said x x-ray apparatus of use according to claim 11 wherein, provides first and second detectors or first and second detector cells.
16. the method for the said x x-ray apparatus of use according to claim 15, wherein, said first and/or said second detector be flat-panel detector.
17. the method for the said x x-ray apparatus of use according to claim 15, wherein, said first and/or said second detector be designed to obtain independent pixel and can move to obtain all pixels.
18. the method for the said x x-ray apparatus of use according to claim 15; Wherein, Said first and/or the array of said second detector with detector sensor, said detector sensor is designed to obtain in each case pixel and can moves to obtain all pixels.
19. the method for the said x x-ray apparatus of use according to claim 15 wherein, provides the detector cell that is designed to have the x ray optics module that is used for the energy selection, to detect the said x x radiation x of launching.
20. the method for the said x x-ray apparatus of use according to claim 11, wherein, said shading chemical element is selected from the group that is made up of following each material, comprising: bromine, iodine, lanthanide series and bismuth.
21. the method for the said x x-ray apparatus of use according to claim 11, it is used for the pictorial display of element-specific or quantitatively demonstration are carried out in the said inspection area of object of being checked that comprises at least a shading chemical element.
22. the method for the said x x-ray apparatus of use according to claim 11; It is in radiology is found and such as PET (PET), single photon emission computed tomography (SPECT) and ultrasonographic other radiology formation methods, and optical imaging method is combined.
23. one kind for being checked that object carries out the control methods of x ray, this process is checked the x x radiation x of object and is carried out to picture from the said x x radiation x of being checked that object is launched that through said said process may further comprise the steps by means of transmission:
A. checked that to this object provides at least a radiopaque chemical element;
B. come the said object of being checked of irradiation with pleochroic in fact x x radiation x;
C. confirm that transmission is through said first intensity level of being checked the x x radiation x of object;
D. confirm by second intensity level that is provided for the x x radiation x that said said at least a radiopaque chemical element of being checked object launches;
E. said first intensity level of the x x radiation x of said transmission is associated with said second intensity level of the said x x radiation x of launching with pursuing pixel; And
F. according to through make said first intensity level be associated with said second intensity level acquisition picture element signal come the said object of being checked is developed.
24. x ray according to claim 23 control methods wherein, based on the energy of said emission x x radiation x, can be measured said second intensity level with distinguishable mode.
25. x ray according to claim 23 control methods wherein, according to x x radiation x energy, is distinguished with other emissions x x radiation x being included in the said x x radiation x of being checked that the shading chemical element in the object is launched mutually.
26. x ray according to claim 23 control methods; Wherein, Correct according to considering said the inspection in the object to the absorption of the x x radiation x of irradiation and/or to the pro-that the self-absorption of the said x x radiation x of launching is carried out, make said first intensity level and said second intensity level each other by pixel be associated.
27. x ray according to claim 23 control methods wherein, provides first and second detectors or first and second detector cells.
28. x ray according to claim 27 control methods, wherein, said first and/or said second detector be flat-panel detector.
29. x ray according to claim 27 control methods, wherein, said first and/or said second detector be designed to obtain independent pixel and can move to obtain all pixels.
30. x ray according to claim 27 control methods; Wherein, Said first and/or the array of said second detector with detector sensor, said detector sensor is designed to obtain in each case pixel and can moves to obtain all pixels.
31. x ray according to claim 27 control methods wherein, provides the detector cell that is designed to have the x ray optics module that is used for the energy selection, to detect said emission x x radiation x.
32. x ray according to claim 23 control methods, wherein, said shading chemical element is selected from the group that is made up of following each material, comprising: bromine, iodine, lanthanide series and bismuth.
33. x ray according to claim 23 control methods; It is in radiology is found and such as PET (PET), single photon emission computed tomography (SPECT) and ultrasonographic other radiology formation methods, and optical imaging method is combined.
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| Application Number | Priority Date | Filing Date | Title |
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| DE102005026940A DE102005026940A1 (en) | 2005-06-06 | 2005-06-06 | X-ray arrangement for image presentation of an examination subject and use of the X-ray arrangement |
| DE102005026940.0 | 2005-06-06 |
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| CN2006800198800A Expired - Fee Related CN101203179B (en) | 2005-06-06 | 2006-04-20 | X-ray arrangement for graphic display of an object under examination and use of the x-ray arrangement |
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| CN111915538A (en) * | 2020-08-19 | 2020-11-10 | 南京普爱医疗设备股份有限公司 | Image enhancement method and system for digital blood vessel subtraction |
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| DE102007018102B4 (en) | 2007-04-16 | 2009-09-03 | Bayer Schering Pharma Aktiengesellschaft | Device for the radiotherapeutic treatment of tissue by means of an X-ray CT system or a diagnostic or Orthovolt X-ray system |
| DE102007024158B4 (en) * | 2007-05-24 | 2017-09-14 | Bayer Intellectual Property Gmbh | Selection procedure for two contrast agents for use in a dual-energy CT examination, combination of contrast agents and generation of CT images with a contrast agent combination with different energy spectra |
| DE102007027460B4 (en) * | 2007-06-14 | 2017-03-23 | Siemens Healthcare Gmbh | Method for carrying out an imaging measurement with an energy-selective X-ray detector |
| US9724010B2 (en) | 2010-07-08 | 2017-08-08 | Emtensor Gmbh | Systems and methods of 4D electromagnetic tomographic (EMT) differential (dynamic) fused imaging |
| KR101689867B1 (en) | 2010-09-15 | 2016-12-27 | 삼성전자주식회사 | Method for processing image, image processing apparatus and medical image system for performing the same |
| US9230311B2 (en) | 2011-02-01 | 2016-01-05 | Dexela Limited | High dynamic range mammography using a restricted dynamic range full field digital mammogram |
| RU2465825C1 (en) * | 2011-06-17 | 2012-11-10 | Федеральное государственное бюджетное учреждение "Ростовский научно-исследовательский онкологический институт" Министерства здравоохранения и социального развития Российской Федерации | Diagnostic technique for soft tissue tumours |
| CN103094030A (en) * | 2011-10-28 | 2013-05-08 | 和鑫生技开发股份有限公司 | Transmission type x-ray tube and reflection type x-ray tube |
| CA2936145C (en) | 2012-11-21 | 2021-06-15 | Emtensor Gmbh | Electromagnetic tomography solutions for scanning head |
| US20140275944A1 (en) | 2013-03-15 | 2014-09-18 | Emtensor Gmbh | Handheld electromagnetic field-based bio-sensing and bio-imaging system |
| US9072449B2 (en) * | 2013-03-15 | 2015-07-07 | Emtensor Gmbh | Wearable/man-portable electromagnetic tomographic imaging |
| JP7065611B6 (en) | 2014-11-20 | 2022-06-06 | コーニンクレッカ フィリップス エヌ ヴェ | X-ray flux reducer for photon counting detector |
| RU2597026C1 (en) * | 2015-06-22 | 2016-09-10 | Российская Федерация, от имени которой выступает Государственная корпорация по атомной энергии "Росатом" (Госкорпорация "Росатом") | Method for recording radiographic images generated by means of ionizing radiation |
| DK3361955T3 (en) | 2015-10-16 | 2020-10-26 | Emtensor Gmbh | ELECTROMAGNETIC INTERFERENCE PATTERN RECOGNITION TOMOGRAPHY |
| CA3044844A1 (en) | 2016-11-23 | 2018-05-31 | Emtensor Gmbh | Use of electromagnetic field for tomographic imaging of head |
| EP3659508A4 (en) | 2017-07-27 | 2020-07-15 | FUJIFILM Corporation | Radiography imaging system, phantom, and evaluation method |
| CN112912768B (en) * | 2018-11-06 | 2024-04-16 | 深圳帧观德芯科技有限公司 | Method of using X-ray fluorescence imaging |
| DE102019213983A1 (en) * | 2019-09-13 | 2021-03-18 | Fraunhofer-Gesellschaft zur Förderung der angewandten Forschung e.V. | DEVICE AND METHOD FOR DETERMINING AN ACQUISITION PARAMETERS AND / OR FOR PROVIDING A MAINTENANCE RECOMMENDATION FOR A COMPUTER TOMOGRAPHY SYSTEM |
| CN113759412B (en) * | 2020-06-03 | 2023-08-22 | 上海联影医疗科技股份有限公司 | Method and device for acquiring beam shape and energy detection unit response characteristics |
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| NL8003354A (en) * | 1980-06-09 | 1982-01-04 | Philips Nv | RADIATION EXAMINATION DEVICE WITH IMAGE SUBTRACTION. |
| DE3608965A1 (en) * | 1986-03-18 | 1987-10-01 | Philips Patentverwaltung | METHOD FOR DETERMINING THE SPATIAL STRUCTURE IN A LAYER OF AN EXAMINATION AREA |
| US6399951B1 (en) * | 2000-02-02 | 2002-06-04 | Ut-Battelle, Llc | Simultaneous CT and SPECT tomography using CZT detectors |
| RU2209644C2 (en) * | 2000-07-05 | 2003-08-10 | Кумахов Мурадин Абубекирович | Roentgen means for detecting location and radiation therapy of malignant neoplasms |
| WO2002083238A1 (en) * | 2001-04-16 | 2002-10-24 | Muradin Abubekirovich Kumakhov | Radioscopy using k$g(a) gadolinium emission |
| WO2004098649A2 (en) * | 2003-05-06 | 2004-11-18 | Philips Intellectual Property & Standards Gmbh | Apparatus and method for examining an object by means of elastically scattered x-ray radiation and contrast agent |
| DE10347961A1 (en) * | 2003-10-10 | 2005-06-09 | Schering Ag | X-ray arrangement and X-ray contrast method for imaging on an examination subject containing at least one X-ray contrast element and use of the X-ray arrangement |
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Cited By (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN111915538A (en) * | 2020-08-19 | 2020-11-10 | 南京普爱医疗设备股份有限公司 | Image enhancement method and system for digital blood vessel subtraction |
| CN111915538B (en) * | 2020-08-19 | 2024-03-19 | 南京普爱医疗设备股份有限公司 | Image enhancement method and system for digital blood vessel subtraction |
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| WO2006131175A1 (en) | 2006-12-14 |
| CN101203179A (en) | 2008-06-18 |
| DE102005026940A1 (en) | 2006-12-14 |
| RU2007148223A (en) | 2009-11-27 |
| CA2610964A1 (en) | 2006-12-14 |
| BRPI0611181A2 (en) | 2010-08-24 |
| IL187846A0 (en) | 2008-03-20 |
| AU2006254747A1 (en) | 2006-12-14 |
| MX2007015406A (en) | 2008-02-19 |
| EP1890604A1 (en) | 2008-02-27 |
| JP2008541963A (en) | 2008-11-27 |
| RU2449729C2 (en) | 2012-05-10 |
| CN101203179B (en) | 2011-12-28 |
| KR20080020616A (en) | 2008-03-05 |
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