Filter assembly for X-ray filter system for medical imaging contrast enhancement

A system for creating an image of the internal features of an object includes an X-ray source and detector array positioned to interpose the object between the X-ray source and the detector array. An X-ray beam is passed through the object along a first path. While passing through the object, the beam is successively filtered twice, each time with a different filter. The successive filtration of the beam results in the production of two electrical signals by the detector which are processed to create an image signal for the path. The process is repeated for a plurality of paths through the object and the resulting image signals are combined using traditional computer tomography techniques to produce a composite image of the object.

FIELD OF THE INVENTION

The present invention pertains generally to devices and methods for imaging the internal features of an object. More particularly, the present invention pertains to improved devices and methods for imaging the internal features of an object while using a conventional broadband X-ray source. The present invention is particularly, but not exclusively, useful for producing an enhanced-contrast image of the internal features of an object by using filtered X-ray radiation.

BACKGROUND OF THE INVENTION

The ability to image the internal features of an object is important in many applications. Two examples include medical diagnosis and the non-destructive testing of structural components to detect configuration or discover internal flaws. In all applications, it is desirable to produce an image having high contrast and spatial resolution. Radiation within the X-ray spectrum is often used to image internal features because of the ability of X-ray radiation to penetrate matter and because different matter absorbs X-ray radiation at different rates. Typically, a conventional X-ray source produces an emission of X-ray radiation having a broad range of energies. In conventional imaging applications, these X-rays are directed through the object for subsequent capture by a film or detector. The imaging films and detectors used are responsive to the intensity of the radiation received, and thus are able to produce an image of the internal features of the object when those internal features have differing absorption characteristics.

To enhance the contrast and spatial resolution of an image, contrast agents are often used. Specifically, these agents include chemical elements that have absorption rates that are significantly different than the constituents of the object to be imaged. For example, Iodine can be administered within the body as a contrast agent. Once administered, the Iodine is selectively absorbed by certain tissues or is present within the blood vessels. Subsequently, when an X-ray image is formed, areas of the body with large amounts of Iodine will absorb relatively greater amounts of X-ray radiation than areas of the body without Iodine. Thus, contrast agents can be used with good efficacy to increase both the contrast and the spatial resolution of the image.

FIG. 1 shows the variation of absorption coefficient with radiation energy for a typical chemical element. In simple terms, the absorption coefficient decreases as the energy increases until an energy is reached that is sufficient to knock a K-shell electron from it's orbit. At this energy, E K-EDGE , the value of the absorption coefficient jumps. For purposes of the present disclosure, the term K EDGE is used to denote the energy at which the jump in absorption coefficient occurs. Continuing with FIG. 1 , it can be seen that further increases in energy again result in a gradual decrease in absorption coefficient.

The present invention recognizes that the variation in absorption coefficient near K EDGE can be utilized to increase image contrast. Specifically, the present invention recognizes that image contrast can be increased by first introducing a contrast agent having a known K EDGE into the object. Next, a first image can be formed using radiation filtered by a first element having a K EDGE just less than K EDGE for the contrast agent and a second image formed using radiation filtered by a second element having a K EDGE just greater than K EDGE for the contrast agent. When this is done, the resulting two images can be subtracted to produce a high contrast image of the internal features of the object. This image is equivalent to the image obtained by using a quasi-monochromatic radiation having an energy band between K EDGE, FIRST ELEMENT and K EDGE, SECOND ELEMENT .

A different way to produce the quasi-monochromatic X-ray radiation described above is to use a crystal monochromator. Unfortunately, when a crystal monochromator is used in conjunction with a conventional X-ray source, the intensity of the resulting monochromatic radiation is so reduced that the radiation is insufficient for almost all practical imaging uses. One way to produce monochromatic radiation at a suitable intensity for imaging is to pass the high intensity radiation from a synchrotron source through a double crystal monochromator. As can be expected, producing radiation with a synchrotron source is very expensive. Further, the beam produced by the synchrotron source/double crystal monochromator is fixed in direction and, consequently, cannot be rapidly moved as required in a typical tomographic scan.

In light of the above, it is an object of the present invention to provide devices and methods suitable for the purposes of producing a digital image signal that is substantially equivalent to an image signal obtained by passing quasi-monochromatic radiation (i.e. radiation having a narrow energy band) through an object. It is another object of the present invention to provide devices and methods for producing images of the internal features of an object having enhanced contrast and high spatial resolution. It is yet another object of the present invention to provide devices and methods for use in conjunction with standard computer tomography or angiography equipment to enhance the contrast and increase the spatial resolution of the images produced. It is yet another object of the present invention to provide devices and methods for enhancing image contrast and increasing spatial resolution that can be used with a variety of different contrast agents. Yet another object of the present invention is to provide an X-ray Filter System For Medical Imaging Contrast Enhancement which is easy to use, relatively simple to manufacture, and comparatively cost effective.

SUMMARY OF THE PREFERRED EMBODIMENTS

The present invention is directed to a system for creating an image of the internal features of an object. Specifically, the present invention is directed at imaging an object that contains a contrast agent. For the present invention, the system includes an X-ray source configured to produce a spectrum of X-ray radiation. An optional collimator may be provided to collimate the radiation emitted from the X-ray source into one or more beams. As such, each beam emanates from the X-ray source in a slightly different direction, and consequently, along a separate path. For the present invention, the X-ray source is oriented relative to the object to direct all such paths towards the object. Further, a mechanism is provided to move the X-ray source relative to the object to cause each radiation beam emanating from the X-ray source to successively travel on different paths through the object. For example, the X-ray source can be slideably mounted on a circular track that extends around the object.

A detector array is positioned on the opposite side of the object to interpose the object between the X-ray source and the detector array. Preferably, the detector array includes a plurality of detectors, one detector for each beam that emanates from the X-ray source/collimator assembly. Further, a mechanism can be provided to move the detector array as the X-ray source is moved. Specifically, the detector array can be moved to allow each detector to track a single X-ray beam, as that X-ray beam travels on successive paths through the object. In response to the receipt of an X-ray beam, the detector produces an electrical signal that is proportional to the intensity of the radiation received.

An important aspect of the present invention is that the X-ray radiation is filtered between the X-ray source and the detectors. Specifically, for each X-ray beam on each path, the beam is successively filtered twice, each time with a different filter. Each time the beam is moved to a new path, the beam is once again filtered two times. Each time the beam is successively filtered two times, two different electrical signals are produced by a detector. For the present invention, these two electrical signals can be manipulated by a processor to produce an image signal for the path. Once an image signal is established for each desired path, conventional tomography techniques can be used to combine all the image signals (one image signal for each path) into a composite image that reveals the internal features of the object.

For the present invention, a filter pair having two different filters is used to successively filter each beam on each path. In accordance with the present invention, a unique filter pair is designed for use with the specific contrast agent that is prescribed for introduction into the object. Specifically, the chemical constituents and thickness of each filter in the filter pair are determined with reference to the specific contrast agent that is being used. For a contrast agent with a chemical element having a K EDGE, CONTRAST AGENT , a filter pair is used having a first filter with a chemical element having a K EDGE that is slightly greater than K EDGE, CONTRAST AGENT , and, a second filter with a chemical element having a K EDGE that is slightly less than K EDGE, CONTRAST AGENT .

A mechanism is provided to successively interpose each filter of the filter pair between the X-ray source and the object to thereby allow the successive filtration of the beams emanating from the X-ray source. For example, the filter pair can be mounted on an oscillating frame or a rotating wheel. For the embodiment with the wheel, the filter pair is mounted on the wheel, and a motor is provided to rotate the wheel about the wheel's axis. The wheel and motor can be attached to the X-ray source to allow the wheel, filters and motor to travel with the X-ray source/collimator assembly as the assembly moves with respect to the object.

In operation, first the contrast agent is introduced into the object, and the object is placed between the X-ray source and the detector array. Next, the X-ray source is located at a first position and activated to produce one or more beams travelling through the object on a first set of paths (one path for each beam). Next, the wheel containing the filters is rotated to successively interpose each filter of the filter pair between the X-ray source/collimator assembly and the object to filter each of the beams with each of the two filters. The result is the production of two intensity-proportional signals by the detector(s) for each path through the object.

For the present invention, these two signals can be manipulated either on-line or off-line by a processor to produce an image signal for the corresponding path. Specifically, the processor subtracts the digital signal produced by the detector with the second filter interposed along the path from the digital signal produced by the detector with the first filter interposed along the path. The result of this is an image signal that simulates the image signal that would be obtained if a quasi-monochromatic beam having an average energy approximately equal to the energy of K EDGE, CONTRAST AGENT were to be passed through the object along the path.

Once image signals are obtained for the first set of paths, the X-ray source/collimator assembly can be moved to a second position to cause the beams emanating from the assembly to travel along a new set of paths. While the X-ray source/collimator assembly is at the second position, the wheel is again rotated to successively interpose both filters between the X-ray source/collimator assembly and the object to again filter each of the beams with each of the filters. Again, two intensity-proportional signals are produced by a detector for each beam. For the present invention, these two signals can be manipulated by a processor as described above to produce an image signal for each new path. This process of moving the X-ray source/collimator assembly and producing an image signal for each new path can be repeated as desired. Further, it is to be appreciated that the X-ray source/collimator assembly can be moved at a continuous rate around the object. When this technique is used, the wheel containing the filters can be rotated continuously as the X-ray source moves. By rotating the wheel very rapidly, each beam is effectively filtered by each of the two filters before significant movement of the beam occurs. Thus, in effect, each beam remains on a single path while the successive filtration takes place. Once image signals are produced for all paths of interest, conventional tomography techniques can be used to combine all the image signals (one image signal for each path) into a composite image that shows the internal features of the object.

DESCRIPTION OF THE PREFERRED EMBODIMENTS

Referring initially to FIG. 2 , an imaging system in accordance with the present invention is shown and generally designated 10 . As shown in FIG. 2 , the system 10 includes an X-ray source 12 configured to produce a spectrum of X-ray radiation 14 . An optional collimator 16 may be provided to collimate the radiation 14 emitted from the X-ray source 12 into one or more beams 18 a-c . As such, each beam 18 emanates from the X-ray source 12 in a slightly different direction, and consequently, along a separate path 20 a-c . It is to be appreciated that the use of three beams 18 is merely exemplary and that as many beams 18 as desired may be used in accordance with the present invention. In detail, as shown in FIG. 2 , beam 18 a initially travels substantially along path 20 a , beam 18 b initially travels substantially along path 20 b and beam 18 c initially travels substantially along path 20 c.

Referring still to FIG. 2 , a detector array 22 is shown positioned to receive the beams 18 from the source 12 . Specifically, the detector array 22 is shown having three detectors 24 a-c , with detector 24 a positioned to receive beam 18 a , detector 24 b positioned to receive beam 18 b and detector 24 c positioned to receive beam 18 c . For the present invention, an object 26 can be interposed between the X-ray source 12 and the detector array 22 to thereby allow the beams 18 to be modified by passing through the object 26 before reaching the detectors 24 . In accordance with the present invention, the detectors 24 can be any type of detector known in the pertinent art capable of receiving radiation and producing an electrical signal that is proportional to the intensity of the radiation received. For example, the detectors 24 can be solid state detectors (separate or having a charge couple detector structure), gas-filled detectors or scintillators with photo-multipliers. Preferably, each detector 24 is a small-area X-ray detector. For the present invention, the output of each detector 24 is electrically wired to a computer (not shown) to allow the signals generated by the detectors 24 to be processed.

Also shown in FIG. 2 , the X-ray source 12 can be slideably mounted on a circular track 28 that extends around the object 26 . Additionally, as shown, each detector 24 or the entire detector array 22 can be slideably mounted on the track 28 . As such, the X-ray source 12 and detectors 24 can be moved either continuously or incrementally around the track 28 and relative to the object 26 . The dashed lines in FIG. 2 show an exemplary second position for the X-ray source 12 and detectors 24 . By moving the X-ray source 12 , each radiation beam 18 emanating from the X-ray source 12 can be caused to successively travel on different paths 20 through the object 26 . For example, as shown in FIG. 2 , when X-ray source 12 is in the initial position represented by the solid lines, beam 18 a travels substantially along path 20 a , and when X-ray source 12 is moved to a second position represented by dashed lines, beam 18 a travels substantially along path 20 d . Similarly, beam 18 b travels substantially along path 20 e and beam 18 c travels substantially along path 20 f when the X-ray source 12 is in the position indicated by dashed lines. Accordingly, the detector array 22 can be moved in conjunction with the X-ray source 12 to allow each detector 24 to track a single X-ray beam 18 , as that X-ray beam 18 travels on successive paths 20 through the object 26 .

An important aspect of the present invention is that the X-ray radiation 14 is filtered between the X-ray source 12 and the detectors 24 . By cross-referencing FIGS. 2 and 3 , it can be seen that a wheel 30 having two attached filters 32 , 34 can be used to successively filter each X-ray beam 18 a-c on each path 20 . As further shown, a motor 40 having a shaft 42 can be used to rotate the wheel 30 and filters 32 , 34 to successively filter each beam 18 twice while the beam 18 travels substantially along a single path 20 . Thus, for a path 20 , the beam 18 is first filtered with filter 32 and then filtered with filter 34 . Additionally, each time a beam 18 is moved to a new path 20 , the wheel 30 is rotated through one complete revolution to once again successively filter the beam 18 with each filter 32 , 34 . Alternatively, the wheel 30 can be located between the X-ray source 12 and the collimator 16 (this configuration not shown). As shown, a bracket 44 can be used to attach the motor 40 to the X-ray source 12 to allow the wheel 30 , the filters 32 , 34 , the motor 40 and the shaft 42 to travel with the X-ray source 12 as the source 12 moves along the track 28 relative to the object 26 . Each time a beam 18 is successively filtered by filter 32 and filter 34 , two different electrical signals are produced by a detector 24 (i.e. one electrical signal for filtration with filter 32 and one electrical signal for filtration with filter 34 ). For the present invention, a computer processor (not shown) can be configured to manipulate the two electrical signals created for each path 20 to produce an image signal for the path 20 . For example, each path 20 can be used to produce an image signal that represents a single pixel in the final image. Or stated another way, a computer processor can be configured to subtract, pixel by pixel, the digital images created by each filter 32 , 34 to produce the contrast enhancement image. Once an image signal is established for each desired path 20 , conventional tomography techniques known in the pertinent art can be used to combine all the image signals (one image signal for each path 20 ) into a composite image that shows the internal features of the object 26 .

Referring now to FIG. 3 , a filter pair having two different filters 32 , 34 is mounted on the wheel 30 to allow each beam 18 on each path 20 to be successively filtered twice It is to be appreciated that a plurality of identical filter pairs, with each pair having two different filters 32 , 34 , can be mounted on the wheel 30 (multiple filter pair not shown). For example, when two identical filter pairs are used, the wheel 30 is rotated through 180 degrees for each path 18 . As further detailed below, a unique filter pair is designed for use with a specific contrast agent that is prescribed for introduction into the object 26 . Specifically, the chemical constituents and thickness of each filter 32 , 34 is determined with reference to the specific contrast agent that is being used. FIG. 4 shows an exemplary filter 32 having layers 46 , 48 , 50 and 52 . Specifically, the filter 32 can include an optional transparent layer 46 , a filtering layer 48 , an optional additional balance layer 50 and an optional protective layer 52 . It is to be appreciated that each filter 32 , 34 will have different layers 46 , 48 , 50 , 52 , the layers 46 , 48 , 50 , 52 differing in both chemical makeup and thickness. For the present invention, the optional transparent layer 46 can be included to support as well as protect the other layers 48 , 50 , 52 . The optional protective layer 52 can be included to protect the other layers 48 , 50 from corrosion or other environmental factors. The function of the filtering layer 48 and the additional balance layer 50 are discussed below. As seen by cross-referencing FIGS. 3 and 4 , a metal ring 54 can be used to hold the layers 46 , 48 , 50 , 52 together and attach them to the wheel 30 .

When used in conjunction with a contrast agent containing a chemical element having a K EDGE CONTRAST AGENT , a filter pair is constructed in accordance with the present invention having a filter 32 with a filtering layer 48 that contains a chemical element having a K EDGE that is greater than K EDGE, CONTRAST AGENT , and a filter 34 with a filtering layer 48 that contains a chemical element having a K EDGE that is less than K EDGE CONTRAST AGENT . The invention includes specific chemical elements and thickness' sufficient to create filter pairs for various contrast agents as shown in Table 1.

Referring back to FIG. 2 , in the operation of the present invention, a contrast agent is first introduced into the object 26 . Once introduced, the contrast agent will be selectively absorbed or localized in specific regions to thereby establish portions of the object 26 having differing concentrations of contrast agent. Table 1, below, lists a number of suitable contrast agents that are either in current use for imaging portions of the human body or are contemplated for future use. It is to be appreciated that conventional methods of administering the contrast agent that are known in the pertinent art can be employed. Further, it is anticipated that the present invention is applicable to the imaging of a non-human object 26 , such as a structural component for a machine or device (not shown). In this case, a material in the structural component can be used as a contrast agent and a suitable filter pair constructed accordingly.

TABLE 1 Combinations of useable contrast elements and filter elements to be applied to K EDGE subtraction technique for image contrast enhancement K EDGE , Filter 32 Filter 34 Atomic (CONTRAST chemical element chemical element Contrast Number AGENT) and thickness and thickness Element Z keV ( m) ( m) I 53 33.17 55 Cs 290.0 52 Te 102.0 Xe 54 34.56 56 Ba 180.0 52 Te 123.0 Cs 55 35.98 56 Ba 180.0 53 I 148.0 Ba 56 37.44 57 La 105.0 55 Cs 380.0 Sm 62 46.83 63 Eu 136.0 60 Nd 117.0 Eu 63 48.52 64 Gd 120.0 62 Sm 138.0 Gd 64 50.24 65 Tb 140.0 63 Eu 236.0 Tb 65 51.99 66 Dy 130.0 64 Gd 151.0 Dy 66 53.79 67 Ho 130.0 65 Tb 149.0 Ho 67 55.62 68 Er 130.0 66 Dy 149.0 Er 68 57.48 69 Tm 135.0 67 Ho 156.0 Lu 71 63.31 72 Hf 110.0 70 Yb 235.0 Hf 72 65.35 73 Ta 97.0 71 Lu 175.0 Ta 73 67.42 74 W 84.0 72 Hf 131.0 W 74 69.52 75 Re 80.0 73 Ta 108.0 Re 75 71.68 76 Os 80.0 74 W 100.0 Os 76 73.87 77 Ir 80.0 75 Re 90.0 Ir 77 76.11 78 Pt 90.0 76 Os 92.0 Bi 83 90.53 90 Th 170.0 82 Pb 230.0 Once a contrast agent has been introduced, the object 26 can be placed between the X-ray source 12 and the detector array 22 as shown in FIG. 2 . Next, the X-ray source 12 is located at a first position and activated to produce one or more beams 18 a-c travelling through the object 26 on a first set of paths 20 a-c . Next, the wheel 30 containing the filters 32 , 34 , is rotated to successively interpose each of the two filters 32 , 34 , between the X-ray source 12 and the object 26 to filter each of the beams 18 with each of the two filters 32 , 34 . This results in the production of two intensity-proportional signals by a detector 24 for each beam 18 . It is to be appreciated that the two signals will be temporally spaced from each other, the spacing corresponding to the time the beam 18 strikes the wheel 30 between adjacent filters 32 , 34 .

Referring now to FIG. 5A , a typical emission spectrum for a conventional X-ray source 12 that has passed through a portion of the body having no contrast agent is shown by curve 56 . When the spectrum represented by curve 56 reaches a detector 24 , an electronic signal that is approximately proportional to the area under curve 56 (the intensity of the emission) is produced. Curve 60 in FIG. 5A represents the spectrum that results after radiation produced by a typical X-ray source 12 is passed through a portion of the body having exemplary contrast agent, Gd, in the absence of filters. Referring now to FIG. 5B , curve 58 represents the spectrum that results after radiation producing curve 56 in FIG. 5A is now passed through filter 34 and a portion of the body having no contrast agent. In this case, filter 34 has a filtering layer 48 having a chemical element with a K EDGE of approximately 49 keV. Accordingly, the electronic signal (hereinafter referred to as the filter 34 signal) produced by a detector 24 when filter 34 is interposed between the X-ray source 12 and the detector 24 will be approximately proportional to the area under curve 58 .

Similarly, a curve representing the spectrum that results after radiation producing curve 65 in FIG. 5A is now passed through filter 32 and a portion of the body having no contrast agent is shown in FIG. 5 C and designated curve 65 . Accordingly, the electronic signal (hereinafter referred to as the filter 32 signal) produced by a detector 24 when filter 32 is interposed between the X-ray source 12 and the detector 24 will be approximately proportional to the area under curve 58 . The processor subtracts the filter 34 signal produced by the detector 24 with the filter 34 interposed along the path 20 from the filter 32 signal produced by the detector 24 with the filter 32 interposed along the path 20 to produce an image signal for the path 20 . It is to be appreciated that the image signal simulates an image signal that would be obtained if a quasi-monochromatic beam having an average energy approximately equal to K EDGE CONTRAST AGENT were to be passed through the object 26 . More specifically, the image signal produced for paths 20 having no contrast agent simulates the exemplary quasi-monochromatic spectrum shown in FIG. 6 A and designated 66 . Similarly, the image signal produced for paths 20 having contrast agent simulates the exemplary quasi-monochromatic spectrum shown in FIG. 6 B and designated 68 . These image signals constitute the data processed for tomography or angiography. The image signal strongly varies with concentration and thickness of the contrast element due to the variation of absorption. This results in an enhanced contrast image between the region with the contrast agent and the region without.

Referring now to FIG. 7 , the effect of additional balance layers 50 in a filter pair is shown. Specifically, FIG. 7 compares the quasi-monochromatic signal that is simulated without additional balance layers 50 (curve 70 ) and the quasi-monochromatic signal that is simulated with additional balance layers 50 (curve 72 ). The curve 72 was generated for a filter pair having a filter 32 with a filtering layer 48 that includes 140.0 m of 65 Tb and an additional balance layer 50 of 200.0 m of 65 Tb and a filter 34 with a filtering layer 48 that includes 236.0 m of 63 Eu and an additional balance layer 50 of 200.0 m of 65 Tb. With cross reference to Table 1 and FIG. 7 , these two filters 32 , 34 can be used in a filter pair in conjunction with the contrast agent Gd to generate the image signal. As shown in FIG. 7 , the use of additional balance layers 50 reduces the non-zero difference of the filter transmission outside the energy pass band. Of course, this effect is obtained by paying the price of reducing the radiation intensity within the pass band (by a factor of about two, in this case). In practice, the additional balance layer 50 is designed to provide a compromise between the enhancement of the quality of monochromatization (i.e. a thicker additional balance layer 50 providing better balance) and the intensity level within the energy pass band (i.e. a larger number of photons to provide a better Signal-To-Noise ratio).

Referring back to FIG. 2 , once image signals are obtained for the first set of paths 20 a-c , the X-ray source 12 and collimator 16 can be moved to a second position (shown by dashed lines) to cause the beams 18 a-c emanating from the collimator 16 to travel along a new set of paths 20 d-f . While the X-ray source 12 and collimator 16 are at the second position, the wheel 30 is again rotated to successively interpose each of the filters 32 , 34 between the X-ray source 12 and the object 26 to again filter each of the beams 18 a-c with each of the two filters 32 , 34 . Again, two intensity-proportional signals are produced by a detector 24 for each beam 18 . For the present invention, these two signals can be manipulated by a processor (not shown) to produce image signals for each new path 20 d-f . This process of moving the X-ray source 12 and producing two image signals for each new path 20 can be repeated as desired. Further, it is to be appreciated that the X-ray source 12 can be moved continuously around the object 26 . When this technique is used, the wheel 30 containing filter 32 and filter 34 can be rotated continuously as the X-ray source 12 moves. By rotating the wheel 30 very rapidly, each beam 18 can be filtered by each filter 32 , 34 before significant movement of the beam 18 occurs. Thus, in effect, each beam 18 remains on a single path 20 while the successive filtration takes place. It is to be appreciated that the image signals described above may also be obtained by first acquiring electrical signals for all paths 18 with the filter 32 interposed along the paths 18 , followed by the acquisition of electrical signals for all paths 18 with filter 34 interposed along the paths 18 . Once an image signal is produced for all paths 20 of interest, conventional tomography techniques can be used to combine all the image signals (one image signal for each path 20 ) into a composite image that shows the internal features of the object 26 .

Referring now to FIGS. 8A-8C , another embodiment of an imaging system in accordance with the present invention is shown and generally designated 10 . As shown in FIG. 8A , the system 10 includes an X-ray source 12 configured to produce a spectrum of X-ray radiation 14 . As further shown, a detector array 22 is shown positioned to receive the radiation 14 from the source 12 . For the present invention, an object 26 is interposed between the X-ray source 12 and the detector array 22 to thereby allow the radiation 14 to be modified by passing through the object 26 before reaching the detector array 22 . For the present embodiment, the object 26 can be a human body, suitcase, machine component or any other object that requires internal imaging. As further shown, a filter set 74 is provided to filter the radiation 14 before the radiation 14 reaches the detector array 22 . Preferably, in this embodiment, the filter set 74 and detector array 22 are stationary during the imaging procedure.

With cross reference now to FIGS. 8A , 8 B and 8 C, it can be seen the filter set 74 includes a plurality of filters 32 and a plurality of filters 34 . It is to be appreciated that the filters 32 a-p and 34 a-p (see FIG. 8B ) as well as the filters 32 q-r and 34 q-r (see FIG. 8C ) are only exemplary. As best seen in FIG. 8B , the filters 32 , 34 are preferably arranged in a planar, two dimensional array. For an object 26 having a contrast agent containing a chemical element having a K EDGE CONTRAST AGENT , each filter 32 contains a chemical element having a K EDGE that is greater than K EDGE, CONTRAST AGENT , and each filter 34 contains a chemical element having a K EDGE that is less than K EDGE CONTRAST AGENT . It is to be further appreciated that the specific chemical elements and thickness' shown in Table 1 can be used to prepare the filters 32 , 34 in the filter set 74 .

As best seen in FIG. 8B , within the planar, two dimensional array, the filters 32 , 34 are preferably arranged in an alternating, checker board pattern. With this pattern, a plurality of filter pairs is established, with each pair containing one filter 32 and an adjacent filter 34 . For example, filter 32 a and 34 a constitute a filter pair for the present invention. Similarly, filter 32 b and 34 b constitute a filter pair for the present invention and so on.

As best seen with cross reference to FIGS. 8A and 8C , the detector array 22 includes a planar array of detectors 76 , of which detectors 76 a-d are exemplary, with one detector 76 for each filter 32 , 34 . In accordance with the present invention, the detector array 22 is preferably an amorphous silicon array of digital detectors 76 , with each detector 76 producing an electrical signal that is proportional to the intensity of the radiation received. Furthermore, a pair of detectors 76 , such as detector 76 a and detector 76 b , is provided for each filter pair ( 32 , 34 ). As shown, the detector pair 76 a , 76 b is positioned to receive filtered radiation from the filter pair ( 32 q , 34 q ). For the present invention, the output of each detector 76 is electrically wired (via wires 78 , of which wires 78 a-d are exemplary) to a computer (not shown) to allow the signals generated by the detectors 76 to be processed. It is to be appreciated that for each filter pair ( 32 , 34 ), a corresponding pair of detectors 76 produces two different electrical signals (i.e. one electrical signal for filtration with filter 32 and one electrical signal for filtration with filter 34 ).

For the present invention, a computer processor (not shown) can be configured to manipulate the two electrical signals created for each filter pair to produce an image signal for the filter pair ( 32 , 34 ). More specifically, the processor subtracts the electrical signal corresponding to filtration with filter 34 from the electrical signal corresponding to filtration with filter 32 to produce an image signal for the filter pair ( 32 , 34 ). It is to be appreciated that each filter pair ( 32 , 34 ) can be used to produce an image signal that represents a single pixel in the final image. Once an image signal is established for each filter pair ( 32 , 34 ), the processor can be used to combine all the image signals (one image signal for each filter pair ( 32 , 34 ) into a composite image that shows the internal features of the object 26 .

In another embodiment of the present invention, the detector array 22 and filter set 74 as shown in FIG. 8 a are formed as linear arrays. It is to be appreciated that a single filter pair 32 , 34 can be used in this embodiment. Preferably, for this embodiment, the X-ray source 12 , linear detector array 22 and filter set 74 are mounted on a track (such as the track 28 shown in FIG. 2 ) for movement relative to the object 26 . During imaging, the X-ray source 12 is moved along the track 28 to successive positions, and an image signal is generated (as described above) from the filter pair ( 32 , 34 ) for each position of the X-ray source 12 . Once an image signal is produced for each desired position of the X-ray source 12 , conventional tomography techniques can be used to combine all the image signals into a composite image that shows the internal features of the object 26 .

While the particular imaging systems and methods as herein shown and disclosed in detail are fully capable of obtaining the objects and providing the advantages herein before stated, it is to be understood that they are merely illustrative of the presently preferred embodiments of the invention and that no limitations are intended to the details of construction or design herein shown other than as described in the appended claims.