CN101069090A - Nuclear medical imaging device - Google Patents

Abstract

An apparatus for imaging a field of view, according to an embodiment of the present invention, comprises an x-ray source positioned adjacent to the field of view, a source mask located between the x-ray source and the field of view having at least one source aperture defined therethrough, and an emission detector, such as a gamma camera, adjacent to the field of view. The apparatus may allow substantially concurrent x-ray imaging and gamma imaging of the field of view.

Description

Nuclear medical imaging device

Quoting of related application

The application requires the right of priority of following application: the serial number of submitting on September 3rd, 2004 is No.60/607,319 U.S. Provisional Patent Application and the serial number of submitting on February 11st, 2005 are No.60/652,424 U.S. Provisional Patent Application, the full content of these two applications is included in by the mode of quoting at this.

Technical field

The present invention relates in general to imaging device and formation method, more specifically, relates to medical imaging.

Background technology

Medical imaging devices has various ways, comprises that the full content of this application is included in by the mode of quoting at this such as the nuclear medical imaging device described in applicant's the common pending application application.As known to persons of ordinary skill in the art, when the nuclear medical imaging device that uses such as SPECT equipment, it is desirable to determine the radiation decrement that the part by around the imaging region by object causes.

SPECT (single photon emission computed tomography) allows to launch the object imaging by the γ that surveys from object.In medical imaging, take a kind of radioisotopic compound that contains to the patient---this compound arrives the object of being studied such as organ, and launches from this object-detection γ.

γ imaging technique such as SPECT is the emission imaging technique, and what wherein paid close attention to is the distribution of emissive material (as radioactive nuclide).On the contrary, such as x ray cat scan, be the transmission imaging method that the attenuation characteristic of object can be determined to the x radial imaging of object.The emission image of object is also revised by the attenuation characteristic of object.Therefore, very usefully, obtain the transmission and the emission image of object together, correct transmission image so that can consider decay factor.

The SPECT imaging of heart or other organ often because of absorbing radioactive emission in non-homogeneous mode or otherwise making the surrounding tissue of radioactive emission decay become complicated, has hindered the accurate reconstruction of image.X ray or gamma-rays cat scan (often being called as transmission scan) can and SPECT (emission) imaging carry out together, the cat scan data can be used to determine the decay that caused by patient's body.Yet when carrying out routinely, there are many problems in this method.The method of at first, present measurement tissue decay requires to carry out transmission cat scan (adopting x ray or gamma-rays) before or after the SPECT emission scan.In order to make attenuation measurement relevant with the emission image, object must definitely keep motionless between this twice scanning.Although object is tried one's best, usually only a few minutes will take place in the motion of inner structure (as, colonic contents).

In addition, the cat scan device is designed to fast, moves with high photon flux, so that " snapshot " is provided.On the other hand, the SPECT imaging is low photon flux process, and this process in order to obtain the data that are enough to form image, needs the much longer time by nature.So, can be during patient's heart, lung and other are organized in the SPECT imaging by a move distance.This has significantly reduced the correlativity between quick cat scan " snapshot " and " time average " SPECT image.

Therefore, advantageously, collect x transmission of radiation signal in the time interval and SPECT transmits, so that object motion has similar influence to transmission with the emission image at parallel (concurrent).Yet than the SPECT imaging, the x radial imaging is a process faster normally, and does not have previous device can make the x radial imaging and the γ imaging is parallel carries out.Usually, obtain the x ray image fast, obtain the γ image then relatively slowly, caused the serious problems of data related fields.

In a word, may be problematic to the explanation of medical image, and have object, to use many images of different technologies will be favourable, as long as these images can be by easily and accurately interrelated.Therefore, improved imaging technique is to for example realizing the collection of improved imaging data and will being important to the more accurate diagnosis of patient's problem.

Summary of the invention

Allow the x transmission of radiation imaging such as x ray cat scan of object and the emission imaging such as the γ imaging are carried out together according to device of the present invention.This x radial imaging can be determined the attenuation characteristic of object, and these attenuation characteristics can be used to proofread and correct the emission imaging technique such as SPECT.The transmission and the emission image that can walk abreast and obtain object, the accurate correct transmission image so that can consider decay factor.The x radial imaging carries out under high x ray flux level usually, and the γ imaging is carried out under much lower flux level usually.Yet, use has the low duty ratio pulse x rays source of (time of opening is divided by the shut-in time), x transmission of radiation and emission image can form at interval at similar imaging time, and this time interval is as measured till from the beginning image data collection to the end image data collection.Described dutycycle can be low to moderate 1%, and is perhaps lower, as 0.1%.For example, can according to x radiogenic lack " opening " time during the scanning of obtaining or section (section) rebuild the x ray image, and grow " closing " time during form and launch image.If do not launch imaging when the x radiographic source is in " opening " state, this method increases the emission imaging time by a factor relevant with dutycycle.Yet when the radiogenic dutycycle of x was low, this factor may be nonsensical.

Also described improved x transmission of radiation imaging technique, wherein, a plurality of x radiographic sources, aperture, source (aperture) and detector aperture move in phase, make the x beam keep alignment to pass aperture, source and detector aperture in scanning process.This method has improved efficient.In addition, use x beam narrow, that in the field range of device, do not disperse substantially, can reduce by the x radiation exposure of imaging object.Another advantage of the light beam of not dispersing is that the resolution of x radial imaging increases.The low x ray of energy is usually by the scattering of more ground, and causes the fuzzy and noise problem in the conventional x ray CAT equipment.When using conventional x radiographic source, be difficult to cause the mixing of high-energy x ray and low energy x-ray for pulsing operation keeps constant high voltage, this mixing causes the noise problem relevant with scattering.Use has significantly alleviated this problem through the x beam of source and detector aperture collimation.Use alignment clamp can further improve performance, be No.10/933 as the common pending application serial number at us, more abundant description in 036 the U.S. Patent application.

Yet, limiting narrow beam by using detector aperture, the x ray of above-mentioned scattering can not pass through detector aperture, thereby has reduced noise and improved resolution.Narrow beam, be meant the bundle of diameter in the present embodiment less than 5mm, for example diameter is between about 1mm and about 1.5mm, this narrow beam also allows to use high photon flux by the detector that can handle high photon flux, and the low relatively detector of usage count rate capacity (count rate capability) is launched imaging concurrently simultaneously.This detector aperture can be similar to identical (as using similar seam (slot) width) with the size of aperture, source in image slices (slice) plane, so that collimation transmitted beam and avoid any remarkable misconvergence of beams by the visual field.

And the pulse x rays source can be used for improved x ray cat scan device.Use source and detector aperture collimation provide narrow beam, as at 1mm to the bundle between the 1.5mm, and when collimated beam scans by the visual field, utilize this collimated beam of coordination mobile tracking in aperture, alleviated the problem of low energy x-ray scattering like this, also reduced irradiation object.Such imaging time may be longer than conventional equipment, but the expense of this apparatus may be the sub-fraction of conventional equipment.

According to device of the present invention, be in particular x transmission of radiation imaging device, can use together with existing SPECT detector, described SPECT detector is as described in my common pending application application and the patented claim that has been authorized to---for example the serial number of Juni is 10/933,036 U.S. Patent application " Single Photon Emission ComputedTomography System "---those.Can be with arc arranged x radiographic source, aperture, source and detector (or relevant detector aperture), they can combine with existing SPECT system, for example, are described in 10/933,036 the U.S. Patent application as serial number.Term " arc () " when this is used, be used for broadly comprising that arc section, complete circular arrangement, ovoid, other bending section and other are similar to the geometric configuration of bending section.According to device of the present invention, be in particular x transmission of radiation imaging device, can also use together with the existing SPECT detector of more routines, described detector comprises that those have the SPECT detector of smooth substantially detector surface.

Although embodiment has shown the curved arrangement in detector and aperture, source, do not say that the designing requirement detector is for crooked at all.Can adopt smooth detector to put into practice identical principle.In such embodiments, the x radiographic source is disposed on the straight line, and the aperture, source is disposed on the flat board (flat sheet).

Emphasized to finish as quickly as possible the value of scanning generally about the prior art of x ray cat scan.Therefore, do not use the motivation in pulse x rays source, particularly do not use the motivation in the pulse x rays source of low duty ratio, because this can slow down finishing of scanning.Yet as discussed in detail elsewhere, the combination of pulse x rays cat scan and emission image provides valuable and improved data, and with respect to collecting the emission required time of image, the loss of time may be not remarkable simultaneously.Therefore, a kind of improved method from object collection emission data and radiation transmission data comprises provides impulse radiation source, collects the radiation transmission data when open in the source, and collects the emission data when the source is closed.

According to embodiment of the present invention, a kind of being used for comprises near the radiation source of visual field setting and the source baffle (mask) between radiation source and visual field the device of the object imaging in the visual field, the source baffle limits at least one aperture, source of passing this source baffle, passes this at least one aperture, source from the radiation of radiation source.Near the emitter-detector of visual field survey from object, incide the emission on this emitter-detector, and radiation detector is set up, so that survey the radiation of passing the visual field.The attenuation image can form according to the radiation detector signal, and the emission image can form according to emitter-detector signal parallel ground.Radiation detector and emitter-detector can be by the single detector assemblies---for example, can provide the band time index signal detector assembly---provide, when radiation source was closed, this signal was corresponding to emission, when radiation source was opened, this signal was corresponding to attenuation.Radiation source can be driven pulsedly.In other embodiments, radiation detector is set up, so that receive this radiation beam after radiation beam passes the visual field, and emitter-detector is set up, so that receive the emission from object.Utilize radiation shield and/or radiation detector that radiation and emitter-detector are separated, when radiation path direction quilt was inswept in the visual field, this screen was along with moving.This screen may stop the part emission from emitter-detector, and this influence can be left in the basket, and perhaps if necessary, can compensate it.If necessary, can use attenuation effect in the attenuation image rectification emission image.

In embodiments of the invention, radiation source is the x radiographic source, and radiation is the x ray, and the x ray sees through body.Emission comprises the γ emission, is for example sent by the radiolabeled material of object Nei Jia.Detector assembly can comprise x transmission of radiation detector and γ emitter-detector.In other configuration, emitter-detector is to be used for gamma-emitting gamma detector, and x transmission of radiation detector is provided for receiving the radiogenic x ray that passes the aperture, source from x between gamma detector and visual field.X ray shield is placed, so that stop the x ray to be mapped on the emitter-detector substantially or fully, allows simultaneously to arrive emitter-detector from the emission of visual field.Therefore, Bing Hang emission and x ray attenuation (transmission) image can be provided by single assembly.By permission the decay changeability in the object is compensated, x ray attenuation data can be used for increasing the accuracy of γ emission image.

In embodiments of the invention, emitter-detector is a gamma detector, and emission is the γ radiation, and this device makes and can determine x ray information and γ information at object.Embodiment of the present invention permission γ imaging and x radial imaging are parallel to carry out, and wherein the x radial imaging time is similar with the γ imaging time, and overlapping substantially.

Topworks can be used to respect to x radiographic source moving source baffle, and to change the path direction that the x ray passes the visual field, the x ray detector moves according to the change of path direction simultaneously, so that the x ray detector continues to receive the x ray.All right mobile detector shield is to keep off the x ray outside emitter-detector.This x ray detector can be installed on the x ray shield, and this combine component can be by moving with the identical or different topworks of source baffle.

Can be used to provide the emission image (as the γ image) of object from first signal of emitter-detector, can be used to provide x transmission of radiation image from the secondary signal of x ray detector, as with the parallel x ray attenuation image that obtains of emission image.The object parallel ground of living is carried out medical imaging make x ray image and emission image be easy to be explained together, thereby make and to carry out more precise diagnosis to the object situation.Described image can be by stacked or presented to the practitioner side by side.And x ray attenuation image can be used to the variable attenuation by compensation density variation and γ signal, improves the accuracy of γ image.

Can dispose x ray shield in many ways.The x ray detector that comprises its shell can provide x ray shield.This x ray detector can be installed on sheet metal or the similar plate.This x ray shield can only block the sub-fraction visual field of emitter-detector, and the front (emission receiving surface) of x raypath and the inswept emitter-detector of x ray shield.Replacedly, x ray shield can comprise a plurality of shields aperture of passing this x ray shield, and this shield aperture is set up, so that allow to arrive emitter-detector from the emission of visual field, prevents that simultaneously the x ray from arriving emitter-detector.

The x radiographic source is driven between open mode and closed condition pulsedly, so that the x with duration of pulse is provided ray pulse, pulse was separated by the recurrent interval, and the x radiographic source is in closed condition in this recurrent interval.Duration of pulse can be between about 0.01 millisecond and about 200 milliseconds, for example between about 0.5-20 millisecond.Dutycycle (time of opening is divided by the shut-in time) can point, for example less than 0.01.For example, can make the x radiographic source in per second, open 1 millisecond, provide 0.001 dutycycle.

Compare with the x radial imaging, the γ imaging generally is a kind of low photon flux method, so the pulse x rays source can collected the x ray image with the γ imaging time in the parallel x radial imaging time.This x radial imaging time is considered to form the time of x ray image, begins to finish to imaging process from imaging.For the x ray photons of the uniform amt that is used for forming the x ray image, dutycycle is low more, and the x radial imaging time is long more.For in the process of collecting the emission image, further reduce the noise (can disturb the scattered x rays of emission image) that the x ray causes, can only use the signal of collecting during the pulse off-interval to collect the emission image.So, utilize to follow the tracks of the imaging dutycycle (the transmission imaging time is divided by the emission imaging time) of x radiographic source dutycycle, can the time period that be used to launch imaging and transmission imaging is interleaved effectively.Replacedly, if emitter-detector and x ray are separated substantially, the emission imaging can be continuous, and transmission imaging just carries out when only being in open mode in the source.

For example, the flicker gamma detector can move with the flux of 100,000 photons of per second, and the x X-ray detection X can be with the flux operation of millions of photons of per second.By utilizing source and detector aperture collimation x beam to make the x beam not penetrate on gamma detector, can carry out synchronous x radial imaging and γ imaging.For example, can be the x ray pulse of Millisecond for each required angular projection (angularprojection) provides pulse length, and each second be obtained a new angular projection approximately.Utilization is distributed in and forms the millisecond data accumulation formation x ray image of emission image in the required long period.The electronic circuit that is used for generating from detector signal image is known in technical field of imaging, will not be further described.

In other embodiments, can use one or more x radiographic sources, the source baffle can comprise the multiple source aperture, and this multiple source aperture provides the x with a plurality of path directions that pass the visual field ray.With respect to x radiographic source moving source baffle, can change a plurality of path directions that pass the visual field.A plurality of x ray detectors can be set, to survey the x ray of all or some path direction in a plurality of path directions.

Another exemplary means that is used to illustrate the Properties of Objects in the visual field comprises x radiographic source, the detector that is provided with at the source baffle between x radiographic source and the visual field, near the visual field and the detector shield between visual field and detector, this source baffle has the aperture, source of passing this source baffle, makes the x ray that passes the aperture, source enter the visual field.This detector shield has the one or more detector apertures that pass this detector shield, makes the x ray of penetrating on detector have the path direction that passes the visual field that is limited by aperture, source and detector aperture.This detector preferably is provided for receiving the x ray that passes the aperture, source and pass detector aperture.Topworks is with respect to x radiographic source moving source baffle, so that change the path direction that the x ray passes the visual field.

This device can also comprise a plurality of x radiographic sources and the multiple source aperture that is positioned at the source baffle, makes topworks with respect to x radiographic source moving source baffle, and the result changes a plurality of path directions that pass the visual field.A plurality of x radiographic sources can be arranged on first arc substantially, and the multiple source aperture is arranged on second arc substantially, this second arc is positioned at first arc the inside, and concentric with first arc.The detector shield can also have a plurality of detector apertures that pass this detector shield.This detector can be the part of arc and/or circular detector assembly, this detector assembly can comprise along the 3rd arc layout and be provided so that a plurality of detectors that receive the x ray that passes the visual field, perhaps can comprise the one or more detectors with bowed shape.This x radiographic source can be driven between open mode and closed condition pulsedly, so that the x with duration of pulse is provided ray pulse, pulse was separated by the recurrent interval, and the x radiographic source is in closed condition in the recurrent interval.Detector assembly can be all responsive to x ray and γ photon, for example be used to when the x radiographic source is in open mode, form the x ray image, when being in closed condition, the x radiographic source forms the γ image, so that the x ray image and the γ image of the visual field that generates simultaneously are provided.

A kind ofly be used to provide the γ emission image of visual field and the device of x transmission of radiation image to comprise the x radiographic source, this x radiographic source is driven between open mode and closed condition pulsedly, so that the x with duration of pulse is provided ray pulse, pulse was separated by the recurrent interval, and the x radiographic source is in closed condition in this recurrent interval; According to inciding γ photon on the emitter-detector and provide the emitter-detector of emitter-detector signal, and provide the x ray detector of x ray detector signal according to inciding transmission x ray on the x ray detector.Electronic circuit can operate the x transmission of radiation image that forms the visual field from x ray detector signal, and the γ emission image that forms the visual field from the emitter-detector signal.The formation that can in similar x ray and γ imaging time, walk abreast of these images.

Description of drawings

Fig. 1 is arranged in schematic representation of apparatus on the arc with a plurality of x radiographic sources;

Fig. 2 illustrates the path direction that the x ray passes the visual field of device shown in Figure 1;

The path direction that the relative position that Fig. 3-6 shows x radiographic source and aperture, source changes when changing;

Fig. 7 shows to have detector assembly, also has the device at the x of this detector assembly front ray detector;

Fig. 8 shows the device that has scanning x beam and be used for preventing the shield of x ray beam on detector;

Fig. 9 A and 9B show at x ray shield traversing on the searching surface of a detector and the x ray detector that is installed on this x ray shield; And

Figure 10 illustrates the smooth layout of detector.

Embodiment

Embodiment of the present invention provide the improved imaging to object.Can use two electromagnetic wavelength zones to carry out imaging, as using x radial imaging and γ imaging (such as SPECT).The measurement of x ray attenuation can be used to provide improved SPECT image by the variable correction of decay to γ photon in the object is provided.Can suppose that for γ photon or x ray photons attenuation coefficient be identical, or suppose the object model that is used between attenuation coefficient, changing, so that carry out correction for attenuation.

In representative embodiment of the present invention, attenuation measurement is carried out in the decay of the radiation beam by determining to pass object.Radiation source is positioned at the place near the visual field, is being detected after seeing through the visual field from the radiation of radiation source.Pass the path direction of visual field by changing radiation, can obtain radiation transmission (decay) image of object in the visual field.Simultaneously, can be used to the emission (this emission can be identical or different with the emission types that radiation source provides) of object in the visual field to view field imaging.In an embodiment of the present invention, transmitted radiation can be the x ray, and emission can be the γ emission.But, in other embodiments, be used for the emission of imaging can be fluorescence, heat emission, other IR (infrared) emission, visible or other can be so as to emission to the object imaging.The radiation that is used for determining the attenuation of object can be x ray or other radiation, as the laser emission of any wavelength, IR, visible, UV (ultraviolet), THz (Terahertz), microwave or nuclear radiation.Compensate by the variation to the object measured for it or the decay of the emission on any ambient substance then, this radiation attenuation measurement can be used for the correct transmission imaging.Replacedly, can determine attenuation image and emission image respectively carrying out improved analysis to object, and correct transmission image not.

Fig. 1 schematically illustrates the device 10 that is configured to also provide x ray attenuation data when carrying out the SPECT imaging.This device can be the modified version as the SPECT device described in our the common pending application.

This device comprises arcuate detector assembly 12, and detector assembly 12 can be a plurality of detectors of arranging along arc, or one or more arcuate detector.This device also comprises arcuate detector shield 14, and this arcuate detector shield 14 has the detector aperture that passes it, and this detector aperture illustrates with small circle 16A-16E, and is configured to the detector aperture arc.

The latter half of device 10 comprises detector assembly 12 and detector shield 14 among Fig. 1, can be corresponding to the embodiment of SPECT device.Fig. 1 comes down to schematically, and not necessarily pro rata.The part of SPECT device can be according to U.S. Provisional Application 60/607,319 and U.S. Patent application No.10/933, and any embodiment of being discussed in 036 is constructed.

The visual field illustrates at 18 places, and object is placed on wherein.For convenience of description, the synoptic diagram of Fig. 1 can be regarded as top view, and wherein detector aperture 16A-16E is the vertical seam of cardinal principle in the detector shield 14.Although there is not diagram, install 10 " level " collimation alignment clamps that also are preferably incorporated between visual field and the detector assembly 12.These collimation alignment clamps are usually located between detector shield 14 and the detector assembly 12.For example, U.S. Patent application No.10/933 has described the collimation alignment clamp in 036.Detector shield 14 and/or detector assembly 12 can relative to each other and/or with respect to visual field 18 rotate, so that make the inswept visual field of being surveyed 18 of x raypath (line of response that is equivalent to detector assembly).

Device 10 also comprises x radiographic source arc 20, and a plurality of x radiographic source 22A-22E arrange along this arc.This device also comprises source baffle arc 24, and this source baffle arc 24 has and is set up the multiple source aperture 26A-26E that passes this source baffle 24.The aperture, source schematically shows with circle, can be seam or other aperture, and the x ray passes them and enters visual field 18.

Though source baffle 20 be shown with detector assembly 12 be substantially continuous, and source baffle 24 be shown with detector shield 14 be continuous, parts that they are all preferably independent, and can be overlapping to a certain extent.Consider the purpose that the patient enters, each parts of this device can intussusception or withdrawal, so that the passway of leading to visual field 18 is provided.Replacedly, in some embodiments, detector assembly 12 and x radiographic source arc 20 can interconnect, with and/or detector shield 14 and source baffle 24 can interconnect.

And, though there is not diagram, level collimation alignment clamp can be set between visual field 18 and x radiographic source 22A-22E.The horizontal sight device is collimated to the x radiographic source and is parallel in the plane that illustrates the plane, and the aperture, source will pass the x raypath of visual field and be constrained to x ray narrow beam, and this x ray narrow beam also can be described as source line (source line).X ray baffle arc 24 stops the x ray of and source aperture misalignment radiogenic from x.

By x radiographic source and/or aperture, source relative to each other and/or with respect to the visual field are rotated, can make the inswept visual field of path direction from the radiogenic x ray of x.

According to a further aspect in the invention, can coordinate moving of arc 12,14,20 and 24, enter in the detector aperture one, so that be detected device assembly 12 and receive so that x ray narrow beam extends through the aperture, source.Use x ray narrow beam that several advantages are arranged like this.At first, it has limited the x radiation exposure to the patient.The second, by all the x ray being collimated at source end and receiving end, the x ray scattering in patient's body has obviously little influence to the attenuation data of collecting in this process.

There is shown 5 x radiographic sources, aperture, 5 sources and 5 detector apertures.The number of each can change.For example, single x radiographic source can use together with the multiple source aperture.The number in aperture, source needn't mate with the number of detector aperture.

Fig. 2 shows three x radiographic sources, and this x radiographic source is launched the x ray narrow beam that passes the respective sources aperture, makes these bundles and corresponding detector aperture aim at, so that penetrate on detector assembly 12.Clear for diagram, only show three x radiographic sources.As one exemplary embodiment, x radiographic source 22A launches the x ray that passes aperture, source 26A and detector aperture 16C arrival detector assembly 12 along path direction 30.In fact, each x radiographic source 22 can be launched the x ray on a plurality of directions, and horizontal collimating apparatus is collimated to a plane with this x ray, and detector aperture further is collimated into narrow beam with them.Yet diagram is for easy by the narrow beam that collimation produces.Those of ordinary skills are clear that, can pass aperture, more than one source from the x ray in a source, so that form the path direction that passes the visual field more than.The variation of x radiographic source, aperture, source and detector aperture relative position, for example the variation that causes by their relative rotation (or angle sweep) can be used for collecting the data that are used to rebuild x ray attenuation image.

The detector parts that use is extended perpendicular to the diagram plane can form 3-D view.The aperture can be perpendicular to the seam on diagram plane, or as our common unsettled U.S. Patent application No.10/933, the curved slot described in 036.The radiogenic quantity of x shown in the present embodiment is 5.In other embodiments, can use single source, and this single source is scanned in the larger context, perhaps use any a plurality of x radiographic source.

Fig. 3-6 illustrates inswept visual field 18, is in the bundle of a plurality of positions.In a preferred embodiment, each arc moves with friction speed, so that make x beam indexing, makes them respectively run in the detector aperture one.In one embodiment, be arranged in x radiographic source on the arc of source moving together relative to high speed, and x ray baffle arc and corresponding aperture, source are moved with the medium speed, detector aperture moves with lower speed.This makes each projection angle can be acquired to be used for the complete reconstruction of x ray image.Can select rotational speed, make the arrangement that in whole scanning process, is in line of x radiographic source, aperture, source and detector aperture, thereby raise the efficiency.Because transmitted beam discord x radiation detector alignment, thereby need not close any x radiographic source.Those of ordinary skills also will know other combination.

Fig. 3 shows the x ray from x radiographic source 22A, and this x ray passes aperture, source 26A and detector aperture 16D arrives detector assembly 12.Fig. 4 shows the x ray from x radiographic source 22A, and this x ray passes aperture, source 26A and detector aperture 16E arrives detector assembly.Among Fig. 5, the x ray from x radiographic source 22A does not arrive detector assembly.X ray from source 22B passes aperture, source 26B and detector aperture 16E arrival detector assembly 12.Among Fig. 6, pass aperture, source 26C and detector aperture 16E arrives detector assembly 12 from the x ray of source 22C.With 30 marks in addition, this path direction changes along with the change of source, the relative configuration with detector aperture in aperture, source the path direction of discussing among each figure in each figure.

The x ray attenuation of embodiment of the present invention is measured and can be used several different methods to carry out.In one approach, can use the method that is similar to the cat scan method, wherein the x radiographic source is all opened continuously, and rotates each arc and make the x beam pass the combination of all angles of patient, so that obtain one group of complete attenuation data.Then, can close the x radiographic source, and use the detector in the detector assembly 12 to obtain the SPECT image.In the method, the detector assembly 12 transmission x ray and the γ that are used for surveying from the visual field launches both.The x radiographic source generally provides level recently from the much higher x ray of level of patient's γ emission, therefore can suppose, when the x radiographic source was opened, all countings basically that detected by the detector on the arc 12 all were x ray countings.Therefore, can suppose, when the x radiographic source is closed, cause that by the γ emission when the x radiographic source was opened, detector signal was derived from the x ray from the detector signal of detector assembly 12.Can proofread and correct the x ray data that causes owing to baseline γ emission (baseline gamma emission), those of ordinary skills know this point.

Replacedly, emission can have different photon energies because the x ray is with γ, so the detector signal that is provided by detector assembly can comprise the information relevant with the γ signal with the x ray signal simultaneously.Can be from signal extraction γ and x ray information from detector assembly, for example, has the layered probe device that can supply the photon of being surveyed is carried out more than one material for detector (as multiple scintillator material) of energy identification by using pulse strength analysis, pulse shape identification or other method, for example using.

The x radiographic source can be driven pulsedly, make they SPECT scan period off and on the very short time period of high relatively horizontal opening one, such as the 0.5-20 millisecond, for example 1 millisecond.Of short duration " opening " time period can be longer or shorter, as in 0.01 to 200 millisecond scope.Preferably, the x radiographic source is closed " a closing " time period " opening " between the time period.Be somebody's turn to do " closing " time period preferably substantially than " opening " time segment length.When the x radiographic source was opened, can suppose to be detected all " countings " basically that device assembly 12 detects all was that the x ray is counted.The time that the x ray is opened can account for assembly as the very little part of time, but is distributed in the whole imaging process, so that they are not prolonging assembly substantially as the time or reduce under the situation of SPECT imaging accuracy time average decay pattern picture is provided.Drive the x radiographic source pulsedly with high-energy and short duration (low duty ratio) and also have following benefit: can use x radiographic source, and/or this x radiographic source can be kept the longer time with low ratings.

Fig. 7 shows alternate embodiment of the present invention.In this embodiment, in detector shield 14 inside x radiation transducers 40A-40D is set between detector aperture.For example, x ray detector 40A is between detector aperture 16A and 16B.In this embodiment, be converted direction,, do not arrive detector assembly 12 and do not pass detector aperture so that penetrate on x ray detector 40A-4D from the radiogenic x beam of x.This detector assembly is used for surveying the γ photon from the object emission.

In other embodiments, horizontal collimating apparatus is set between x ray detector and visual field.For example, as about at U.S. Patent application No.10/933, a plurality of embodiment of describing in 036 is discussed, the detector shield---is called aperture arc---therein can be placed on the place farther from the visual field, and replace collimation alignment clamp between aperture arc and the detector assembly placing the collimation alignment clamp between aperture arc and the visual field, perhaps the collimation alignment clamp except that aperture arc and detector assembly between in addition between aperture arc and visual field placement collimate alignment clamp.

In the device of Fig. 7, owing to used different sensing systems, so the x ray can transmission when the SPECT imaging is carried out.Detector assembly 12 is used for surveying the γ emission, and separates by detector shield 14 and x ray.Detector aperture can be extended, for example to occupy the most of angular region between the x ray detector, so that detector assembly is passed in more γ emission.

As further alternative plan, it is different that the x radiation transducers can be positioned to, and perhaps can cover the bigger part of aperture arc, so that the x ray under the more perspective can be detected simultaneously.

Fig. 8 shows the device that comprises x radiographic source 60, and x radiographic source 60 provides x beam, and this x beam passes the aperture, source 64 (seam) in the source baffle 62, pass object 66 (this object may be the patient, as people or pet---such as dog, cat or other mammal; Or their organ or other parts; Or do not have the object of life, as parcel, suitcase, food etc.) and incide on the x ray detector assembly.X ray detector assembly comprises x ray detector 70 (as semiconductor detector) and detector shield 68 (for example, lead shield).Source baffle 62 passes aperture, source 64 by making the x ray, as collimating apparatus or focus set.Those of ordinary skills are known that shield 62 preferably is placed on from x radiographic source 60 place enough far away, to obtain the collimation or the focusing of required x ray.This distance can be greater than distance shown in Figure 8, and the latter not necessarily in proportion.

Moving source baffle rather than source are favourable, because the moving source baffle is more easy.When the x beam carried out angle sweep to object, detector shield 68 made the gammacamera 72 that comprises gamma detector 74 separate with the x beam.The aperture that the x beam is prevented from passing in the gammacamera arrives the gamma detector material.

In exemplary device, the direct incident that x ray detector 70 belongs to the x beam can not make the type of its saturated (or losing function).Example x X-ray detection X modulator material comprises CZT (cadmium zinc telluride), zinc telluridse, other chalkogenide, other semiconductor or other high speed x X-ray detection X modulator material.The x ray detector replacedly is made up of gas proportional detector equipment.The x beam can be driven pulsedly, pulsed frequency can with negative correlation release time of x X-ray detection X modulator material.Other means that can be used in the x ray detector comprise microcalorimeter (the single photon calorimeter that comprises common needs cooling), microchannel plate equipment, proportional counter, semiconductor detector (comprising CMOS), scintillator and fluorophor.

Release time when the configuration of Fig. 8 makes the pulsed frequency of x beam can be independent of gamma detector directly to be exposed under the x beam, the situation that gamma detector directly is exposed under the x beam is that this configuration is avoided.Therefore, slow gamma detector material (with respect to x X-ray detection X modulator material) can use together with the x beam that is driven by fast-pulse.The screen of gamma detector makes originally and can be used because of the saturated gamma detector material of the direct incident of x beam.For example, sodium iodide, cesium iodide, bismuth germanium oxide or other scintillation material such as plastic scintillant can be used as the gamma detector material.The x radiographic source that the configuration of Fig. 7 also allows to use high power, driven by fast-pulse can be unsaturated and be used for detecting the material of SPECT information, is not used for detecting on the material of SPECT information because the x ray is not mapped to.On the contrary, the x ray preferably is mapped on the receiver 40 that stitches between 16.Replacedly, when use comprises that the gamma detector of (non-paralyzing) material that does not lose function obtains SPECT information, can not require x alpha ray shield thing.

Because seam collimation of 64 pairs of x beams and blocking of shield 68, gamma detector 74 does not directly receive the x beam.Additional collimation can be provided, for example use other seam, slot array, aperture, metal capillary, shutter, directed x radiographic source etc.X ray detector assembly can also comprise the x ray collimator of the one or more x of being positioned at ray detectors 70 fronts.

If necessary, can also provide the additional mask thing of gammacamera, incide on the gamma detector for example to reduce spuious scattered x rays.

Fig. 9 A shows the view of the x ray detector assembly (comprising detector shield 82 and x ray detector 80) that is positioned at emitter-detector 84 fronts.In this embodiment, emitter-detector is a gammacamera.Fig. 9 B shows the side that detector shield 82 and x ray detector 80 move to gammacamera 84, and with respect to Fig. 9 A, this moves corresponding to the angle sweep of x beam in the visual field.

In this embodiment, the inswept one scan of x beam angle.In this embodiment, the x ray detector can comprise the material to the response of high photon flux, and as bar of semiconductor material, it has being vertically oriented as shown in the figure.X ray detector assembly is along with the angle motion scan relevant with the angle sweep of x beam, make in the angle sweep process (at least for the angle of being paid close attention to, or not so the x beam will drop on angle on the gammacamera), the x beam keeps being incident on the x ray detector.The detector shield can be a lead shield, or comprises other x ray absorbent material.

When x ray detector assembly in the front, aperture of gammacamera by the time, the aperture will temporarily be blocked (as, be blocked 2-3 second).Yet this is the operation of grievous injury gammacamera not, can temporarily be blocked this point at the aperture in the gammacamera signal from gammacamera is numerically proofreaied and correct.This device can be configured to make that the most of photon from the visual field arrives gammacamera, does not block and be not detected the device shield.

Gammacamera is an example of emitter-detector, and it is surveyed the γ emission and some space distribution informations of the γ photon of being surveyed are provided.Gammacamera can comprise scintillation crystal---for example sodium iodide,crystal or cesium iodide, a series of detector collimating apparatuss between scintillation crystal and visual field and detection are by a series of photomultipliers of the scintillation photons of the generation of the γ radiation in the scintillation crystal.Scintillation photons can be visible, and can be comprised that photodiode and other any optical detectors to the semiconductor devices of photo response detect.Gammacamera provides the detector signal relevant with the space distribution of the scintillation photons of being surveyed, and these detector signals can be used for forming two dimension or 3-D view.Use then in methods known in the art, can use electronic circuit to obtain the γ image of object from detector signal.Embodiment of the present invention can be used for object is carried out two and three dimensions γ and/or x radial imaging.

Detector assembly can comprise one or more two-way detector arraies.This detector array can comprise emitter-detector, and this emitter-detector is selected according to the wavelength of the radiation of being surveyed.For the γ emitter-detector, can use the solid state detector that comprises CZT (cadmium zinc telluride) or cadmium telluride or other chalkogenide.Detector can also comprise scintillation material such as sodium iodide or cesium iodide and relevant flash transmission detector, such as photomultiplier or other photodetector such as photodiode.Detector assembly can comprise side by side the multi-disc scintillation material of assembling or the scintillation material crystal of single big bending.Scintillation detector can also comprise position sensitive flash transmission detector and/or scintillation photons is directed at the fiber array of suitable detector.

Therefore, improved CAT and SPECT unit equipment comprise provides the x of x beam radiographic source, mechanism, gammacamera and the x ray detector assembly of the angle sweep of the x beam that passes object are provided, this x ray detector assembly carries out the angle relevant with the angle sweep of x beam and moves, the x ray detector comprises high speed x ray detector and x ray shield, and this x ray shield is not directly incident on the gammacamera x beam.In other embodiments, gammacamera can be omitted, and/or can use other detector systems, for example, and PET imager, thermal imaging device, video or other imaging systems.

Preferably, this approach can also be used to providing CT and PET composite set.In arbitrary combination, the CT/x ray partly allows to carry out correction for attenuation, and allows the body structure in institute's survey region is positioned.For example, if the position in related zone is determined in SPECT scanning, the CT scan with the same area is favourable with the relative position of determining organ and bony structure.The invention provides this ability.As further alternative plan, any design given herein can be used as the CT/x x-ray apparatus, and does not have SPECT or PET aspect.Arbitrary design can be used under the CT/x ray pattern, and need not operate SPECT or PET part, perhaps can only provide CT/x ray ability for equipment.That is, design given herein provides new and useful especially CT device, does not rely on aspect other of this discussion.

Provide the mechanism of the angle sweep of x beam can comprise rotational structure, this rotational structure comprises aperture, array of apertures, x ray reverberator, directed x radiographic source or other structures.

In other embodiments, two or more x beam scannings can be arranged by object, and relevant x ray detector assembly stops the x ray to be directly incident on the gammacamera.

In other embodiments, the x beam can be the bundle (pencil-likebeam) of light cone shape, has suitable collimation, and for example by circular aperture, and the x beam can scan by one or more planes, as two orthogonal planes.In another embodiment, the x radiographic source can about move (for Fig. 8) point-blank, and can with it towards receiver or counter move together.As an embodiment, this source can move on to a plurality of positions, and receiver scans at each position.Although graphic embodiment is preferred at present, as another alternative plan, one or more receivers can be fixed, and move in the source.

In example application, can be patient's organ by the object of imaging, as heart.For example, as U.S. Patent application No.10/933, described in 036, give the patient infusion radiomaterial, this radiomaterial is absorbed by cardiac muscle during with oxygen at cardiac muscle.The γ emission produces from this heart tissue then, and can be detected by gamma detector.Utilize this γ that detects emission to rebuild myocardium image then.Yet patient's heart is surrounded by the dissimilar tissues with different densities.This surrounding tissue absorbs radioactive emission or makes the radioactive emission decay in other mode in a kind of mode heterogeneous, makes the accurate reconstruction of image complicated.This is serious problem in medical imaging.Yet device makes can walk abreast to patient's x ray attenuation imaging and γ imaging and carries out according to embodiments of the present invention, makes and can proofread and correct the γ image at the variable density in the ambient substance such as tissue.

Device can be obtained the x ray image such as x ray attenuation image concurrently with the γ imaging according to embodiments of the present invention.Driving the x radiographic source pulsedly can obtain the x ray image in the similar time range (time-scale) of the time range required to obtaining the γ image.

In other embodiments, the x ray image can combine with dynamic SPECT imaging, for example, and so that the film of the organ function in the time range that x ray and γ view data derive, common to be provided.

In other embodiments, gate SPECT imaging can combine with the pulse x rays view data, to obtain the same phase of repetitive process---for example, the moment of heartbeat---parallel image.This x radiographic source can have long shut-in time section in the unconcerned period.

Embodiment discussed above has illustrated the x ray detector that is used for for example CT imaging or other scannings and has been used for for example combination of the gammacamera of SPECT medical imaging.Yet embodiments of the invention also comprise independently CT scan device.The SPECT imaging of any device disclosed herein or other γ imaging functions are optional.Application comprises heart, brain, kidney or other organs or their function imaging.

Other embodiment of the present invention can adopt dissimilar radiation.For example, can measure by making laser emission scanning carry out laser attenuation by object, wherein laser radiation detector and optional coherent radiation shield move with laser beam.By the radiation that use is sent from object, for example heat radiation, laser-induced fluorescence (LIF), IR, microwave, Terahertz (THz) or other radiation, emitter-detector or other detectors can be used for obtaining view data simultaneously.Device according to the present invention can carry out laser attenuation and radiant image simultaneously.In other embodiments of the invention, the x radial imaging can and PET (PET (positron emission tomography)) imaging combine.

The more details of medical imaging

Other aspects that can be used for the medical imaging devices in the embodiment of the present invention, in my common pending application application and U.S. Patent No. 6,525,321 and 6,525, be described in 320 (both titles all are " Single photon emission computed tomography system "), described common pending application application comprises U.S. Patent application No.10/933,036 and No.10/872,253 (both titles all are " Single photonemission computed tomography system "); No.10/993,012 (" Edgeeffects treatment for crystals "); No.10/358,961, the content of above-mentioned patented claim and patent is all included in by the mode of quoting at this.

The visual field can be configured to comprise patient's trunk, so that carry out cardiac imaging.This trunk can be a level or vertical for imaging.In one embodiment, detector assembly and detector shield are arranged with one heart around the patient.An embodiment that is used for cardiac imaging is at U.S. Patent application No.10/933, description arranged in 036, comprises about 64 emitter-detector modules, and each emitter-detector module is made up of a series of independently unit or pixel.In this embodiment, the detector aperture arc that the detector shield provides radius to be about 30cm, it is the arc of 40cm that detector assembly forms inside radius.In this embodiment, patient's field of view of the about 50cm of diameter is in field range.The area limiting that this visual field can be impaled by source baffle and detector shield or other image-forming blocks.This detector aperture arc and detector assembly can be arranged on how much real arcs, and common arc core is positioned on the longitudinal axis at the center of passing the visual field.Replacedly, any one in them or both can be avette, perhaps are to have the arc of non-common arc core.For example, arc core can be positioned at the not position on above-mentioned longitudinal axis, so that increase the arc radius.In source, aperture, source, detector aperture or the detector configuration any one is can also right and wrong arc.For example, any one can be arranged to one or more straight sections, and perhaps being arranged to partly is that arc part right and wrong are arc.

Device according to the embodiment of the invention can also comprise the dynamometer that is used for the patient body activity, for example to pressurize to heart before imaging.Device can also comprise cardiogram, cardiac defibrillator and/or be used to use the amedrop of radiolabeled medicine or other compounds.

In another embodiment, single photon emission computed tomography (SPECT) device that is used to produce a plurality of faultage images of the type of representing the radioisotopic distributed in three dimensions of photo emissions comprises: substrate, this substrate comprises and is used for supporting patient's stilt that a part that the patient makes the patient is positioned at the visual field that one longitudinal axis is defined and passes the visual field; Detector assembly near the visual field, this detector assembly extends around the visual field between first end and second end at least in part, this first end and second end are spaced apart, so that be limited to the inlet of visual field, whether this detector assembly can be operated to survey has photon to beat on this detector assembly; Collimator assembly, this collimator assembly comprise at least two isolated collimation alignment clamps that the photon attenuation material constitutes, and each alignment clamp is disposed between detector assembly and the visual field; Arc substantially detector shield, this detector shield comprises the photon barrier structure that is arranged between visual field and the detector assembly, this barrier structure has and is defined a plurality of detector apertures (as seam) that pass this member along this member every a segment distance, pass through for the photon of aiming at the aperture seam, the line of response of detector assembly is restricted to from detector assembly passes detector aperture; And displacement topworks, this displacement topworks can operate to move the photon barrier structure with respect to detector assembly, makes the aperture seam move with respect to detector assembly, and makes at least a portion of the inswept visual field of line of response.This device also comprises a plurality of x radiographic sources of arranging near the visual field.Detector assembly can be used for x radial imaging and γ emission imaging, for example forms γ emission image when x radiographic source inertia.Replacedly, can make detector assembly and separate from the radiogenic x ray of x, this x ray has and the inconsistent path direction of detector field of view, and itself and the independent x ray detector that is provided are separated.This x ray detector and optional relevant x ray shield can play a part to stop the x ray to arrive detector assembly.This detector assembly can comprise gammacamera or other emitter-detector.

Source and/or detector aperture can have adjustable size, for example, comprise the seam with adjustable-width.This feasible sensitivity and resolution that can be adjusted to picture.

Although embodiment shows the curved arrangement in detector and aperture, source, do not say that this designing requirement detector is for crooked at all.Can adopt smooth detector to put into practice same principle.In such embodiments, the x radiographic source is disposed on the straight line, and the aperture, source is positioned at dull and stereotyped going up (that is, adopting linearity or almost to arrange).Figure 10 illustrates a kind of device, this device comprises the aperture, source 110 in detector aperture 106, x radiographic source 112 and the source baffle 108 in detector assembly 114, the detector shield 104, in this embodiment, detector assembly 114 comprises scintillator 102 and photodetector 100.X beam 116 is collimated at detector aperture and place, aperture, source, and drops on the detector assembly.This x beam can be narrow, and for example its width is less than about 5mm, for example at about 1mm in the scope of about 1.5mm, and this x beam is not dispersed substantially.Can the coordinates operation of source aperture, detector aperture and the radiogenic translation of (randomly) x, make detector can survey the x beam continuously.Can use more than one x radiographic source, and these one or more x radiographic sources can be driven pulsedly.If the x beam is not driven pulsedly, continuous probe x beam is possible during the translation aperture.Typical case that arrow (D) indication source and detector aperture move may direction, but other to move be possible.Translation mechanism such as topworks and other features have description in the U.S. Patent No. 6,525,320 of Juni, this patent is included in by the mode of quoting at this.

Each embodiment described here is described as the x ray with transmitted radiation, and emission is described as gamma-rays.Yet in other embodiments of the invention, transmitted radiation and/or emission can be other types.

Include at this patent, patented claim or publication of mentioning in this instructions by the mode quoted, degree is just like pointing out that specifically and individually each independent document is included in by the mode of quoting.Particularly, is No.60/607 by the mode quoted with the serial number of submitting on September 3rd, 2004 at this, the serial number that 319 U.S. Provisional Patent Application, on February 11st, 2005 submit to is No.60/652,424 U.S. Provisional Patent Application and serial number are No.10/933, and 036 U.S. Patent application is complete to be included in.

The invention is not restricted to above-described illustrative embodiment.Embodiment does not intend being used for limiting the scope of the invention.Method described here, device, combination etc. are exemplary, do not intend being used for limiting the scope of the invention.Those of ordinary skills will expect variation and other uses among the embodiment.Scope of the present invention is limited by the scope of claim.

Claims (27)

1. one kind is used to illustrate that this device comprises from the device of the x radiant transmittance of the emission of visual field and this visual field:

Near the x radiographic source that this visual field is provided with, this x radiographic source provides x ray;

Source baffle between this x radiographic source and this visual field, this source baffle has the aperture, source,

The x ray passes this aperture, source, and the x ray has the path direction that passes this visual field;

Near the emitter-detector that this visual field is provided with, this emitter-detector is surveyed the emission from this visual field; And

X ray detector, this x ray detector between this emitter-detector and this visual field so that after the x beam passes this visual field, receive this x beam,

This emitter-detector and x ray are separated, and this emitter-detector provides and relevant the transmitting of emission from this visual field,

This x ray detector provides the relevant x ray detector signal of x radiant transmittance with this visual field of this path direction.

2. according to the device of claim 1, it is characterized in that, also comprise topworks, this topworks can operate to move this aperture, source with respect to this x radiographic source, so that the change of the path direction that passes this visual field is provided,

This x ray detector moves according to the change of this path direction, makes this x ray detector continue to receive the x ray,

When this path direction changes, keep this emitter-detector and x ray are separated.

3. according to the device of claim 2, wherein this x ray detector is installed on the x ray shield, and this x ray detector and x ray shield move together according to the change of this path direction.

4. according to the device of claim 1, wherein this emitter-detector is a gamma detector, and emission is the γ emission from this visual field.

5. according to the device of claim 4, wherein this device is used to provide from first signal of this emitter-detector the γ emission image of this visual field,

This device also is used to provide from the secondary signal of this x ray detector the x transmission of radiation image of this visual field.

6. according to the device of claim 1, it is characterized in that, also comprise x ray shield, this x ray shield has a plurality of shields aperture of passing it, this shield aperture is provided so that the emission energy that makes from this visual field arrives this emitter-detector, and this x ray shield stops the x ray to arrive this emitter-detector.

7. according to the device of claim 1, wherein this x radiographic source is driven between open mode and closed condition pulsedly, so that the x with duration of pulse is provided ray pulse, this pulse was separated by the recurrent interval, this x radiographic source is in closed condition in this recurrent interval, this x radiographic source has dutycycle, and this dutycycle equals this duration of pulse divided by this recurrent interval.

8. according to the device of claim 7, wherein should the duration of pulse between about 0.01 millisecond and about 200 milliseconds.

9. according to the device of claim 1, wherein this source baffle comprises the multiple source aperture, and the x with a plurality of path directions that pass this visual field is provided ray,

This device also comprises topworks, and this topworks can operate to move this source baffle with respect to this x radiographic source, so that revise a plurality of path directions that pass this visual field.

10. according to the device of claim 9, it is characterized in that this device also comprises a plurality of x ray detectors, these a plurality of x ray detectors are provided to survey at least a portion of the x ray with a plurality of path directions.

11. the device according to claim 9 is characterized in that, also comprise a plurality of x radiographic sources that are arranged in substantially on first arc, and wherein the multiple source aperture is arranged in substantially on second arc.

12. a device that is used to illustrate the visual field, this device comprises:

The x radiographic source;

Source baffle between this x radiographic source and this visual field, this source baffle has the aperture, source,

Make the x beam that passes this aperture, source enter this visual field;

Near the detector that this visual field is provided with, this detector has detector aperture, and this detector receives this x beam after the x beam passes this detector aperture; And

Topworks, this topworks can operate to move this source baffle with respect to this x radiographic source, so that scanning x beam passes the path direction of this visual field,

Wherein this aperture, source and detector aperture make the x beam divergently not pass this visual field substantially with the certain size manufacturing.

13. according to the device of claim 12, wherein this device comprises:

A plurality of x radiographic sources;

Multiple source aperture in the baffle of source; And a plurality of detector apertures,

Described topworks can operate to move this source baffle with respect to described a plurality of x radiographic sources,

So that a plurality of x beams of this visual field are passed in scanning.

14. according to the device of claim 13, wherein:

Described a plurality of x radiographic source is arranged on first arc substantially,

Described multiple source aperture is arranged on second arc substantially, and

Described a plurality of detector aperture is arranged on the 3rd arc.

15. according to the device of claim 13, wherein in the scanning process of the x beam that passes this visual field, coordinate moving of this x radiographic source, this aperture, source and detector aperture, make the x beam to be received continuously by this detector.

16. according to the device of claim 12, wherein this detector is the part of arcuate detector assembly.

17. device according to claim 12, wherein the x radiographic source is driven between open mode and closed condition pulsedly, so that the x with duration of pulse is provided ray pulse, this pulse was separated by the recurrent interval, and this x radiographic source is in closed condition in this recurrent interval.

18. device according to claim 17, wherein the detector signal that obtains when this x radiographic source is in open mode of this device utilization provides the x ray image of this visual field, and this device also utilizes the detector signal that obtains when this x radiographic source is in closed condition that the emission image of this visual field is provided.

19. according to the device of claim 18, wherein this emission image is the image from the γ emission of this visual field.

20. according to the device of claim 17, wherein should the duration of pulse between about 0.01 second and about 200 milliseconds.

21. according to the device of claim 17, wherein should the duration of pulse between about 0.5 millisecond and about 20 milliseconds.

22., wherein should be 10 double-lengths of this pulse length in the recurrent interval at least according to the device of claim 17.

23. one kind is used to provide the emission image of visual field and the device of x ray image, this device comprises: the x radiographic source, this x radiographic source is driven between open mode and closed condition pulsedly, so that the x with duration of pulse is provided ray pulse, this pulse was separated by the recurrent interval, and this x radiographic source is in closed condition in this recurrent interval;

Emitter-detector, this emitter-detector provides the emitter-detector signal according to the emission from this visual field;

The x ray detector, this x ray detector provides x ray detector signal according to the x ray that passes this visual field and incide on this x ray detector; And

Electronic circuit, this electronic circuit can be operated:

Form the x ray image of this visual field from this x ray detector signal, and

Form the emission image of this visual field from this emitter-detector signal, this emission image is the image from the emission of this visual field.

24. according to the device of claim 23, wherein this emitter-detector and x ray detector are provided by same detector assembly, this detector assembly provides detector signal,

This x ray detector signal is the detector signal of this x radiographic source when being in open mode,

This emitter-detector signal is the detector signal of this x radiographic source when being in closed condition.

25. according to the device of claim 23, wherein this pulse length of this pulse-to-space ratio is big more than 100 times.

26. according to the device of claim 23, wherein this x ray image and this emission image formed in the basic parallel time period.

27. according to the device of claim 23, wherein this emission is the γ emission.

Images