CN101011257A - Focus-detector arrangement for generating projective or tomographic phase contrast recordings - Google Patents

Focus-detector arrangement for generating projective or tomographic phase contrast recordings Download PDF

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CN101011257A
CN101011257A CN 200710007968 CN200710007968A CN101011257A CN 101011257 A CN101011257 A CN 101011257A CN 200710007968 CN200710007968 CN 200710007968 CN 200710007968 A CN200710007968 A CN 200710007968A CN 101011257 A CN101011257 A CN 101011257A
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focus
detector
ray
grating
distance
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CN101011257B (en
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乔基姆·鲍曼
克里斯琴·戴维
马丁·恩格尔哈特
乔尔格·弗洛伊登伯格
埃克哈德·亨普尔
马丁·霍黑塞尔
托马斯·默特尔迈耶
弗朗兹·法伊弗
斯蒂芬·波普斯库
曼弗雷德·舒斯特
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Paul Scheler Institute
Siemens Healthineers AG
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Siemens AG
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
    • A61B6/48—Diagnostic techniques
    • A61B6/484—Diagnostic techniques involving phase contrast X-ray imaging
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
    • A61B6/42—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for detecting radiation specially adapted for radiation diagnosis
    • A61B6/4291—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for detecting radiation specially adapted for radiation diagnosis the detector being combined with a grid or grating
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N2223/00—Investigating materials by wave or particle radiation
    • G01N2223/40—Imaging
    • G01N2223/419—Imaging computed tomograph
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N2223/00—Investigating materials by wave or particle radiation
    • G01N2223/60—Specific applications or type of materials
    • G01N2223/612—Specific applications or type of materials biological material

Abstract

A focus-detector arrangement of an X-ray apparatus is disclosed for generating projective or tomographic phase contrast recordings of an observed region of a subject. In at least one embodiment, the arrangement includes a radiation source which emits a coherent or quasi-coherent X-radiation and irradiates the subject, a phase grating which is arranged behind the subject in the beam path of the radiation source and generates an interference pattern of the X-radiation in a predetermined energy range, and an analysis-detector system which detects at least the interference pattern generated by the phase grating in respect of its phase shift with position resolution. Further, the beam path of the X-radiation used diverges in at least one plane between the focus and the detector.

Description

Produce the focus-detector arrangement of projection or tomographic phase contrast contrast images
Technical field
The present invention relates to a kind of being used for to checking the viewing area (=FOV of object, the visual field) focus-detector arrangement of the X-ray equipment of generation projection or tomographic phase contrast contrast images, have relevant or accurate relevant X ray of emission and fluoroscopic examination object radiation source, be arranged in the radiation path of radiation source, check the phase grating after the object, this phase grating produces the relevant pattern of X ray in the predetermined power scope, and analyzing and testing device system, be used for spatially-resolvedly at least the relevant pattern that is produced by phase grating being detected phase shift with the detected phase grating.
Background technology
In general mostly observe two effects that when X ray passes material, occur for x-ray imaging, promptly to the phase shift of the absorption of specific X ray component and the X ray launched.
For by equation (1) at the given refractive index of X ray,
n＝1-δ-iβ (1)
The size of imaginary number attenuation β is depended in described absorption, and this attenuation forms certain relation by equation (2) and mass-absorption coefficient,
μ/ρ＝4πβ/λ (2)
Wherein λ is a wavelength, and μ is a linear absorption coefficient, and ρ is a mass density.
Phase shift is derived from the real part of refractive index 1-δ.The phase shift Δ of X ray ripple is compared with vacuum by equation (3) and is provided in the material,
Δ＝2πδT/λ (3)
Wherein T is a material thickness, and δ is the real number attenuation of refractive index.
In the X ray radiology, check object, and the record X ray passes object intensity afterwards with X-radiation.Can produce the projected image of the absorption that displaying causes by object by this measurement.In the x-ray tomography radiography, adopt many projected images to calculate the three-dimensional data group of the spatial distribution of performance absorptance μ.
For phase-contrast radiology and phase-contrast tomography, must analyze the phase shift that causes by object.Imaging is similar with absorbing, and can calculate the three-dimensional data group of spatial distribution of the real part 1-δ of performance refractive index.
Owing to can't directly measure the phase place of ripple, therefore at first by interfering the examine ripple that phase shift is converted to measurable intensity with reference wave.This measurement not only at projected image but also at the practical embodiments of computed tomography images as being illustrated in European patent application EP 1447046A1 and enjoying in the German patent application 102006017290.6,102006015358.8,102006017291.4,102006015356.1 and 102006015355.3 of equal priority.
The method utilization of showing in the document is arranged at the phase grating of checking after the object on radiation path, this phase grating is divided into as diffraction grating work and with X ray+1 with the ray on-1 rank.Wave field after being arranged in phase grating, the ray of diffraction is interfered under the situation that forms the X ray stationary field mutually.Check that object causes local phase shift, this phase shift meeting makes wavefront distortion and therefore changes local amplitude, phase place and the side-play amount of stationary field.Therefore the measurement that can provide about phase place, amplitude and the intermediate value of the information of stationary field such as static ripple is provided, can be calculated local phase shift and pass the influence of checking object.For the resolution scan wave field to require, analyser gratings moves on this wave field step by step, adopts relevant detection device individual element ground synchronization monitoring intensity simultaneously.
In above-mentioned European patent application EP 1447046A1, adopt parallel X ray to come the scanography object.Can be from the following fact for surface observation: at how much on ray that use is dispersed with will check that object correspondingly is positioned under the situation on the radiation path and can realize enlarge-effect arbitrarily.If but investigate ray in the refraction effect of checking the object place, then as if can not measure phase shift again, because be certain to occur " out of order " pattern of deflection ray, this pattern can not cause available image to reproduce.Owing to can't adopting phase grating to carry out the X ray phase-contrast at present in amplifying geometry, this reason measures.
Summary of the invention
Therefore the technical problem to be solved in the present invention is to find a kind of focus-detector arrangement that is used for X ray phase-contrast radiology and X ray phase-contrast tomography, and it can produce checks that projection that is amplified to strong amplification and tomography that the object refractive index spatial distributes show.
In principle, for the X ray phase-contrast measurement of being undertaken by phase grating and relevant or accurate relevant X ray be also noted that following some:
Laboratory x-ray source (X-ray tube, by-end, plasma source, radioactive source, parameter x-ray source, channeling radiation) and first to the emission of the x-ray photon of third generation conventional synchronization radiation source based on stochastic process.Therefore the X ray of being launched itself does not have spatial coherence.If but viewing angle is enough little, radiographic source manifests under this viewing angle to observer or object, grating or detector, and then the ray of x-ray source is at phase-contrast X ray photography and phase-contrast tomography or just the same with the situation of spatial coherence ray in the interference experiment arbitrarily.Tolerance as the spatial coherence of the x-ray source that enlarges can provide so-called space/lateral coherence length L c:
L c = λ a s
At this λ is wavelength, and s is horizontal radiographic source size, and a is the distance between radiographic source and the observer.Exact value is deputy; Importantly the size of the area of space that should interfere mutually with ray is compared, and coherence length L is very big.
In the scope of present patent application, coherent ray should be understood to produce the ray of relevant pattern under the condition of distance between the X ray grating of given geometry and expectation.Certainly spatial coherence and spatial coherence length are therefore always determined by these 3 parameters of wavelength, radiographic source size and viewing distance.For the purpose of compactness, this situation is reduced to notion such as " relevant X ray ", " relevant x-ray source " or " being used to produce the point source of relevant X ray ".The basis of this simplification is the penetration capacity of the inspection object by expectation in the application of here discussing on the one hand, the wavelength (or ENERGY E) of restriction X ray in the frequency spectrum that the laboratory x-ray source provides on the other hand.Constituting at the laboratory that is used for the nondestructive examination of materials or medical diagnosis apart from a between radiographic source and the point of observation is subjected to some restriction.Thereby mostly radiographic source s is left last degree of freedom, strict restriction is arranged equally even the pass between radiographic source size and the x-ray power ties up to this.
If adopt the source grating of suitable dimension, then adopt the stronger radiation source of power and so bigger focal spot size here in the focus-detector arrangement that can provide.The narrow gap of source grating is responsible for keeping the spatial coherence of desired all rays that penetrate from same slit.Photon from same slit can be interfered mutually, just phase place overlaid correctly.In contrast, from can not phase place between the photon in the different slits of source grating correctly overlapping.But, at suitable tuning source grating cycle g 0With relevant pattern period g 2And source grating G 0With phase grating G 1Between distance 1 and phase grating G 1With relevant pattern G 2Between apart from d the time, can according to
g 0/g 2＝l/d (5)
First carry out the ripple maximum and the ripple minima of stationary field correctly overlapping at least according to intensity in approximate.In the reduced representation of present patent application, adopt the notion of " accurate coherent ray " or " accurate coherent ray source ".
The monochromaticity of X ray or x-ray source is incident to be the time coherence of ray or vertically relevant.Have enough monochromaticity or temporal coherent length here in the application that the X ray of characteristic curve is discussed.Connecting monochromator the preceding or the grizzly bar height by phase grating can also be from bremstrahlen frequency spectrum or the enough narrow spectral range of filtering the frequency spectrum synchronously, therefore satisfied requirement to the temporal coherent length in the shown device to the selection of resonant energy.
Can not to be used for the professional recognition that phase-contrast measures opposite with the structure for amplifying of focus-detector arrangement, and the inventor finds to suppose can realize gratifying imaging results on the contrary with all.
Advise a kind of focus-detector arrangement that is used for the viewing area (=FOV, visual field) of checking object is produced the X-ray equipment of projection or tomographic phase contrast contrast images according to this understanding inventor, this device has following feature at least:
Relevant or the accurate relevant X ray of emission and the radiation source of transmission inspection object,
Be arranged in the radiation path of radiation source, check the phase grating after the object, this phase grating produces the relevant pattern of the X ray that is positioned at the predetermined power scope, and
Analysis-detector system is used for the phase shift with the detected phase grating of relevant pattern that spatially-resolved detection produces by phase grating, wherein
The radiation path of employed X ray is dispersed at least one plane between focus and detector, just is equivalent to fan ray.
In another embodiment, also can constitute this focus-detector arrangement like this, make and disperse in two planes of radiation path between focus and detector of employed X ray, and therefore be equivalent to the circular cone ray.
In order to form compact structure, particularly preferably be employed beam and in a plane, open 5 ° at least at least, preferably open 10 ° at least.In the application in medical CT (computer tomography) field, even use surpasses 45 ° fan angle.
Diversity according to the ray geometry that is adopted, the observed zone of the inspection object of seeing in the projection of the optical axis direction of radiation path can be less than the use zone of the phase grating after being arranged in radiation path, and the use zone of this phase grating is less than the use zone of the analysis-detector system after being arranged in radiation path.Certainly the size that begins to increase gradually when observing in the other direction from focus also is significant.
In particularly preferred embodiments, the distance of suggestion from radiation source to analysis-detector system is the twice from radiation source to the distance of checking object at least.The phase-contrast that can use phase grating and described analysis-detector system effectively to amplify is first thus taken, and wherein only shows phase shift in this image.This amplification coefficient can be amplified to 10 times even be amplified to 1000 times by corresponding selection x-ray source and distance between inspection distance between objects and x-ray source and the analysis-detector system under needing accordingly.
Suggestion keeps following geometrical relationship concerning the cycle of phase grating and analyser gratings in focus-detector arrangement of the present invention:
g 2 = 1 2 r 1 + d m r 1 g 1 - - - ( 6 )
D wherein mBe the distance between the grating, r 1Be the distance between radiation source and the phase grating, g 2Be the cycle of analyser gratings, g 1It is the cycle of phase grating.
Utilize relational expression r 2=r 1+ d mEquation (6) can also be rewritten as
g 2 = 1 2 r 2 r 1 g 1 .
Advise such positioning analysis-detector system in addition, make the analyser gratings when analysis-detector system is made up of the detector with analyser gratings or the plane of incidence and the distance between the phase grating of the detector when analysis-detector system is made up of the detector that does not have analyser gratings make that stationary field is a maximum.For rich (Talbot) distance of so-called tal fibre, following equation is set up in first is similar to:
d m = ( m - 1 2 ) · g 1 2 4 · λ - - - ( 7 )
Wherein:
d mDistance between=phase grating and the analyser gratings, promptly so-called tal fibre is won distance;
The rich exponent number of interfering of m=tal fibre; M=1,2,3,
g 1The cycle of=phase grating;
The wavelength of λ=employed X ray.
Equation (7) is described the accurate distance at infinite ray.When using the taper ray equation (7) only first approximate in effectively because along with and phase grating between the increase of distance, relevant pattern is also increasing, and is described as equation (6).This equation is equivalent to the grating cycle g along with the increase phase grating of distance 1Also increasing effect.
According to the present invention, in this embodiment of focus-detector arrangement, can adjust two different distortion that are oppositely arranged of phase grating and analysis-detector system.If phase grating distance analysis-detector system on radiation direction checks that than distance object is nearer, then the grating cycle of the amplitude grating in the analysis-detector system is less than the grating cycle of phase grating, and is typically approximately half as large.
In alternative focus-detector was provided with, phase grating distance on radiation direction checked that object is nearer than distance detector, and then analyser gratings is with bigger grating cycling.Analyser gratings even can use grating cycling greater than phase grating.
Above-mentioned two distortion can be implemented with such analysis-detector system, this system replaces analyser gratings with detector, each detector element of this detector constitutes shape of stripes again, its direction is corresponding to the grid stroke of phase grating, wherein these stripeds must have cycle of 1/3 that maximum equals the corresponding cycle of analyser gratings, so that just can determine the phase shift of X ray in detector element with one-shot measurement.
In order to produce relevant X ray, the inventor advises that radiation source has the focus that constitutes little focus about the geometry of focus-detector arrangement in first substitute mode.
According to another substitute mode, if be arranged on X ray grating on the radiation direction in addition, be that so-called source grating is used to produce necessary coherence, then radiation source can also have the focus of dispersing.Though the resolution that just can reach has provided restriction thus, can improve performance, thereby for example can reduce needed irradiation time.
Although in above-mentioned distortion, provided the preferred embodiments of the present invention, all other known, the x-ray sources that produce relevant X ray light such as free electron laser, the 4th generation synchrotron equally within the scope of the invention, precondition is respectively the radiation geometry of dispersing.
Understanding according to the inventor, also advise combining use with focus-detector arrangement of the present invention and the x-ray system that is used to produce the projected phase contrast images or with the X ray computer tomographic system that is used to produce the tomographic phase contrast contrast images, these systems can amplify respectively and show and check object.The analysis of in most cases this system and small sample combines use, but uses can also carry out the details imaging in medical computer tomograph the time or when checking toy.
Description of drawings
Describe the present invention in detail by the preferred embodiment in the accompanying drawing below, wherein only show and understand the feature of wanting required for the present invention.Use the following drawings labelling at this: 1: computer-tomographic system; 2: the first X-ray tubes; 3: the first detectors; 4: the second X-ray tubes; 5: the second detectors; 6: rack shell; 7: the patient; 8: patient's bed; 9: system's axle; 10: control and computing unit; 11: memorizer; D: phase grating G 1With analyser gratings G 2Between distance; D: detector; d m: tal fibre is won distance; E i, E j: detector element; F: focus; G 0: the source grating; G 1: phase grating; G 2: analyser gratings; g 1, g 2: grating cycle I (E x(x G)): in pattern displacement is x GThe time at detector element E xOn the intensity that records; I: the intensity of the photon stream that records; M: relevant pattern; P: sample; Prg n: program;
Figure A20071000796800101
: the distance between radiation source and the analyzer-detector system;
Figure A20071000796800102
: the distance between radiation source and the sample; r 1: focus is to the radial distance of phase grating; r 2: focus is to the radial distance of analyzer-detector system; S i: X ray; x G: the displacement of analyser gratings; : the phase shift on the detector element Ex;  Ij: the relative phase shift between the detector element; λ: the wavelength of employed X ray.
Specifically illustrate:
Fig. 1: the longitudinal section that the schematic diagram of the focus-detector arrangement with phase grating, analyser gratings and detector that is used to show interference is shown;
Fig. 2: be illustrated on the detector element of selection and the relative position relevant Strength Changes of analyser gratings to relevant pattern;
Fig. 3: the schematic section that has strong enlarge-effect and be arranged near the focus-detector combination of the phase grating analyzer-detector system according to of the present invention is shown;
Fig. 4: the schematic section that has strong enlarge-effect and be arranged on the focus-detector combination of checking near the phase grating the object according to of the present invention is shown;
Fig. 5: the schematic section that has strong enlarge-effect and use the focus-detector combination of the analyzer-detector system that does not have analyser gratings according to of the present invention is shown;
Fig. 6: illustrate according to of the present invention and have strong enlarge-effect and be arranged near the phase grating analyzer-detector system and on radiation source, adopt the schematic section of the focus-detector combination of source grating;
Fig. 7: illustrate according to of the present invention and have strong enlarge-effect and be arranged on the schematic section of checking near the phase grating the object and on radiation source, adopting the focus-detector combination of source grating;
Fig. 8: the sketch map that has according to the computer-tomographic system of focus-detector combination of the present invention is shown, and this focus-detector combination has enlarge-effect and phase grating and employing source grating on radiation source.
Below better understanding, the phase-contrast basic principle of measurement is described with Fig. 1 and Fig. 2.
The specific embodiment
Fig. 1 illustrates from the accurate coherent ray of radioactive source or from the independent coherent ray of source grating, and ray passes checks object or sample P, wherein produces phase shift when checking object P passing.Passing grating G 1The time produce the relevant pattern that shows by gray shade, this relevant pattern is by grating G 2Detector D of Lian Jieing and detector element E thereof in the back i, E jThe last generation radiant intensity different to each detector element wherein forms relevant pattern or X ray stationary field with the rich distance of so-called tal fibre.
If for example according to analyser gratings G 2Relative position x GInvestigate detector element E iAnd intensity I (E i(x G)) be this relative position x GFunction, then obtain detector element E iThe sinusoidal of last intensity changes process, as shown in Figure 2.If at each detector element E iOr E jRadiant intensity I and the displacement x measured GRelevant, then can use function I (E the different detector element of the space X ray between final formation focus and respective detector element i(x G)) or function I (E j(x G)) be similar to.From this function, can determine relative phase shift  between phase shift  and the detector element for each detector element Ij
The phase shift of the ray of therefore determining each detector pixel by the measurement that utilizes the analyser gratings that staggers respectively at least 3 times or being investigated for each ray in the space, therefrom can under the situation that the projection X ray is taken, directly calculate the pixel value of projected image, can under the situation of CT examination, produce the projection that pixel value equals phase shift on the other hand, thus can be thus by known reproducting method itself calculate which volume element of checking in the object corresponding to the phase shift that records which partly.Calculate cross-sectional image or stereo data thus, it is with regard to the effect of the phase shift reflection inspected object of X ray.Because the fine difference in forming or the fine difference of thickness will produce very strong effect to phase shift, the details of therefore can reproduction itself more approaching material, especially organ-tissue is enriched and the strong stereo data of contrast.
By the analyser gratings of multiple shift and the radiant intensity of measuring on the detector element that is positioned at after this analyser gratings detect the phase shift of passing the X ray of checking object, be to have moved respectively in analyser gratings must carry out under the situation of a part in grating cycle with every X ray to be measured as condition at least 3 times.
Also there is such probability in principle: do not use such analyser gratings but adopt enough high-resolution detector, the loss of strength that causes in the grizzly bar of analyser gratings owing to absorb can not take place in this case, and just can determine phase shift between each ray/pixel with one-shot measurement.
In order to measure that phase-contrast need be used coherent ray or to be accurate coherent ray at least.This ray for example can the focus by point-like produce, and perhaps produces as the field of the coherent ray separately structure by source grating after the focus that is positioned at the plane and constitutes or the corresponding grating type by the speckle (Brennfleck) that burns on the anode that is used for this grating of balance.
Should select the line orientation of grating like this, the striated structure of the feasible detector element that has the grid stroke of grating now and exist in case of necessity is parallel to each other.In addition preferably but not necessarily be, grid stroke is parallel to or is directed perpendicular to the system axle ground in the focus-detector system shown in this.
Fig. 3 illustrates the sketch map that has the focus-detector combination of focal point F according to of the present invention, and this focus penetrates on the direction of sample or inspection object P has ray S iThe diverging ray bundle.After passing inspection object P, fall to this beam expansion the first phase grating G 1On, in this phase grating, producing relevant pattern, this pattern comprises analyser gratings G by what connect later 2Thereafter analysis-detector system of detector D is analyzed.This analysis is by carrying out at this analysis-detector system shown in this, this analysis-detector system have analyser gratings and be connected after, the detector that comprises a plurality of detector element, described as Fig. 1 and Fig. 2.In the grating space of this grating G2, also show the material of high-absorbable for the effect of improving analyser gratings G2.But the analyser gratings of pointing out not have this packing material in the grating space also within the scope of the invention.
In addition at the important radial distance that illustrates below this figure between the main element of focus-detector combination, as focus and phase grating G 1Between radial distance r 1And the radial distance r between focus and the analysis-detector system 2For the amplification characteristic of describing diverging ray is drawn out distance between focus or radiographic source and the sample equally
Figure A20071000796800131
And the distance between radiographic source or focus and the analysis-detector system
Figure A20071000796800132
Amplification coefficient V is by the distance between radiographic source or focus and the analysis-detector system
Figure A20071000796800133
And the distance between radiographic source or focus and the sample
Figure A20071000796800134
Ratio provide, wherein
v = QD ‾ QP ‾ . - - - ( 8 )
Check the projected size and the back phase grating G that are scanned zone (=FOV=visual field) in the object 1The ratio in use zone and all corresponding with above-mentioned how much situations according to scanography object of the present invention the time with the ratio in the zone of the analyzer-detector system subsequently that uses.
Equally according to the distortion of focus-detector of the present invention system, wherein the distance between the analysis-detector system of phase grating and back obviously increases shown in Fig. 4.The inventor recognizes, can and/or pass through to amplify phase grating cycle g by the rich exponent number m of the bigger tal fibre of selection 1Increase the rich distance of tal fibre.Amplify g 1Also can cause the increase in analyser gratings cycle.But at first increase the cycle of stationary field to be scanned and the cycle that therefore increases analyser gratings by amplifying geometry.Reduce length-width ratio thus and also therefore simplify the manufacturing of grating.If implement not have the analysis-detector system of analyser gratings, then preferably can be by low slightly the requirement of above-mentioned geometry selection to the position resolution of detector.
Shown in Figure 5 have a phase grating G 1The distortion of this focus-detector system, this phase grating forms with the analysis that is connected later-detector system interferes, detector is divided into the single detector element in this analysis-detector system, and these detector element of the position resolution of definite detector are divided into shape of stripes corresponding to the grid stroke of phase grating again, to measure the phase shift of each detector element.At this also with phase grating G 1And the distance between the detector D of back is chosen as, and to equal tal fibre rich apart from d m
Distortion in focus-detector system shown in Fig. 6 and Fig. 7 has wherein also connected a source grating, thereby also can produce accurate relevant X ray for the focus that enlarges between focal point F and inspection object P, can use obvious higher power/intensity work thus.
The projection X-ray equipment or the computer-tomographic system of this focus-detector system and medical application can also be combined use thus.
Grating distance proportion each other is identical with distance proportion among Fig. 3 and Fig. 4 among Fig. 6 and Fig. 7.
Example-the computer-tomographic system 1 of medical applications shown in Fig. 8, this system have one or optional two according to focus-detector of the present invention system.Rack shell 6 is shown, is provided with first X-ray tube 2 in the shell and is positioned at the detector system 3 on its opposite, also integrated phase grating shown in above-mentioned accompanying drawing in this detector system.Optionally, the focus-detector system that another has second X-ray tube 4 and second detector system 5 can also be set.In order to scan, can will move through the opening of support as the patient 7 who checks object by removable patient's bed 8 along system's axle 9.Move the control and the analysis of computer-tomographic systems by control and computing unit 10, in this control and computing unit 10, be provided with and comprise program Prg 1-Prg nMemorizer.In this control and computing unit 10, can also analyze and carry out reproduction to image.
Point out, utilize in this focus-detector system that in this document, shows and not only can carry out the phase-contrast measurement, but also can carry out absorptiometry.When analyzing each pixel, obtain phase information and absorption information.
Be to be understood that the combination that above-mentioned feature of the present invention not only can be used for respectively providing but also can under the situation that does not depart from the scope of the invention, be used for other combination or use separately.

Claims (14)

  1. One kind be used for to the viewing area of checking object produce the X-ray equipment of projection or tomographic phase contrast contrast images focus-detector arrangement (F, D), this device has:
    1.1. radiation source (2), be used to launch relevant or accurate relevant X ray and transmission check object (7, P),
    1.2. be arranged in the radiation path of radiation source, check object (7, P) phase grating (G afterwards 1), this phase grating produces the relevant pattern of the X ray that is positioned at the predetermined power scope, and
    1.3. analysis-detector system (G 2, D), be used for spatially-resolved detection by phase grating (G 1) the relevant pattern that produces is with the phase shift of detected phase grating, it is characterized in that,
    1.4. the radiation path of employed X ray is dispersed in the plane between focus (F) and detector (D) at least.
  2. 2. focus-detector arrangement according to claim 1 is characterized in that, the radiation path of employed X ray is dispersed in two planes between focus (F) and detector (D).
  3. 3. focus-detector arrangement according to claim 1 and 2 is characterized in that, the observed zone of the inspection object of seeing in the projection of the optical axis direction of radiation path is less than the phase grating (G after being arranged in radiation path 1) the use zone, and this phase grating (G 1) the use zone again less than the analysis-detector system (G after in radiation path, being arranged at 2, use zone D).
  4. 4. according to each described focus-detector arrangement in the claim 1 to 3, it is characterized in that, from described radiation source (2) to analysis-detector system (G 2, distance D) ( ) be at least from radiation source (2) to check object (7, distance P) (
    Figure A2007100079680002C2
    ) twice.
  5. 5. according to each described focus-detector arrangement in the claim 1 to 4, it is characterized in that, from described radiation source (2) to analysis-detector system (G 2, the distance of detector D) (
    Figure A2007100079680002C3
    ) be at least from radiation source (2) to check object (7, distance P) (
    Figure A2007100079680002C4
    ) 10 times.
  6. 6. according to each described focus-detector arrangement in the claim 1 to 5, it is characterized in that described phase grating (G 1) distance analysis-detector system (G on radiation direction 2, D) than distance check object (7, P) nearer.
  7. 7. according to each described focus-detector arrangement in the claim 1 to 5, it is characterized in that described phase grating (G 1) distance inspection object on radiation direction (7, P) than distance analysis-detector (G 2, D) nearer.
  8. 8. according to each described focus-detector arrangement in the claim 1 to 7, it is characterized in that described analysis-detector system (G 2, D) have analyser gratings (G 2) and after being arranged on the radiation direction, comprise a plurality of detector element (E x) detector (D).
  9. 9. focus-detector arrangement according to claim 8 is characterized in that, described phase grating (G 1) and analyser gratings (G 2) between distance (d m) satisfy following geometrical relationship:
    d m = ( m - 1 2 ) · g 1 2 4 · λ
    Wherein:
    d m=phase grating (G 1) and analyser gratings (G 2) between distance;
    m＝1，2，3，...；
    g 1=phase grating (G 1) the grating cycle;
    The wavelength of λ=employed X ray.
  10. 10. according to each described focus-detector arrangement in the claim 1 to 9, it is characterized in that, keep following geometrical relationship:
    g 2 = 1 2 r 1 + d r 1 g 1
    Wherein d is phase grating (G 1) and analyser gratings (G 2) between distance, r 1Be the distance between the radiation source and first grating, g 2Be analyser gratings (G 2) cycle, g 1Be phase grating (G 1) cycle.
  11. 11., it is characterized in that described radiation source has the focus that constitutes little focus about the geometry of focus-detector arrangement, and is wherein preferred according to each described focus-detector arrangement in the claim 1 to 10:
    s ≤ λ r 1 g 1
    Wherein s is the size of focus, and λ is the wavelength of employed ray, r 1Be focal point to the radial distance of phase grating, g 1It is the grating cycle of phase grating.
  12. 12., it is characterized in that described radiation source has focus (F) and is arranged on X ray grating (source grating) (G on the radiation direction according to each described focus-detector arrangement in the claim 1 to 11 0).
  13. 13. an x-ray system is used to produce the phase contrast image that can show the projection of checking object enlargedly, it is characterized in that, it has according to each described focus-detector arrangement in the claim 1 to 12.
  14. 14. an X ray computer tomographic system is used to produce and can shows the tomographic phase contrast contrast images of checking object enlargedly, it is characterized in that it has according to each described focus-detector arrangement in the claim 1 to 12.
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