U.S. patent number 3,848,130 [Application Number 05/373,465] was granted by the patent office on 1974-11-12 for selective material x-ray imaging system.
Invention is credited to Albert Macovski.
United States Patent |
3,848,130 |
Macovski |
November 12, 1974 |
SELECTIVE MATERIAL X-RAY IMAGING SYSTEM
Abstract
An array of x-ray images are obtained each representing a
different spectral energy distribution. These images are scanned
with the output signals applied to a computer. The computer is used
to produce signals representing the absorption due to specific
materials. These are displayed individually or in a composite color
display.
Inventors: |
Macovski; Albert (Palo Alto,
CA) |
Family
ID: |
23472531 |
Appl.
No.: |
05/373,465 |
Filed: |
June 25, 1973 |
Current U.S.
Class: |
378/98.9; 378/5;
378/157; 378/98.5; 378/53; 976/DIG.435 |
Current CPC
Class: |
A61B
5/1075 (20130101); A61B 6/025 (20130101); A61B
6/4035 (20130101); A61B 6/482 (20130101); G01N
23/043 (20130101); G21K 1/10 (20130101) |
Current International
Class: |
A61B
5/107 (20060101); A61B 6/03 (20060101); A61B
6/02 (20060101); G21K 1/00 (20060101); G21K
1/10 (20060101); G01N 23/04 (20060101); G01N
23/02 (20060101); G01t 001/20 () |
Field of
Search: |
;250/336,363,366,369,482,510 |
References Cited
[Referenced By]
U.S. Patent Documents
Primary Examiner: Lawrence; James W.
Assistant Examiner: Willis; Davis L.
Claims
What is claimed is:
1. Apparatus for providing a plurality of processed x-ray images
represening specific materials in an object comprising:
a plurality of sources each having a different x-ray energy
spectrum;
means for recording a plurality of images each representing the
different x-ray energy spectrum transmitted through the object with
the number of recorded images being at least as great as the number
of processed images;
means for scanning each of the plurality of recorded images to
generate a plurality of scanned signals;
a computer for processing the plurality of scanned signals to
generate the plurality of processed signals represent specific
materials in the object; and
mean for displaying the processed signals whereby processed x-ray
images are formed representing specific materials in the
object.
2. Apparatus as recited in claim 1 wherein the means for recording
the plurality of images each representing the different x-ray
spectrum transmitted through the object comprises:
a scintillating screen for converting the x-rays transmitted
through the object into visible light image; and
means for recording the visible light image.
3. Apparatus as recited in claim 2 wherein the means for recording
the visible light comprises a television camera whose target
receives the light image from the scintillating screen and a video
storage device for storing the electrical video signal generated by
the television camera.
4. Apparatus as recited in claim 2 wherein the means for recording
the visible light comprises photographic film.
5. Apparatus as recited in claim 4 wherein the means for scanning
each of the plurality of recorded film images includes a flying
spot scanner whose light output is imaged onto each of the recorded
film images and a photocell for collecting the transmitted light
and generating the scanned signal.
6. Apparatus as recited in claim 1 wherein the plurality of x-ray
sources comprises an x-ray emitter and a plurality of filters
positioned in the path of the emitted x-rays where each filter
includes materials having a different x-ray transmission
spectrum.
7. Apparatus as recited in claim 1 wherein the plurality of x-ray
sources comprises an x-ray emitter and a plurality of secondary -
emitters positioned in the path of the emitted x-rays each of which
fluoresces and emits a monochromatic spectrum.
8. Apparatus as recited in claim 1 wherein the computer for
processing the plurality of scanned signals to generate a plurality
of processed signals includes means for taking weighted sums of a
pre-calculated constant term and the logarithms of each of the
scanned signals.
9. Apparatus as recited in claim 1 wherein the computer for
processing the plurality of scanned signals to generate a plurality
of processed signals includes means for solving a plurality of
simultaneous integral equations each representing the relationship
between all of the processed signals and a different one of the
scanned signals the relationship specifying each scanned signal
being equal to the integral, over the energy spectrum used, of the
products of the absorptions of each of the specific materials in
the object.
10. Apparatus as recited in claim 9 wherein the means for solving
the plurality of integral equations comprises:
an array of sub-computers for each of the plurality of integral
equations with each sub-computer computing the output for a
different subregion of the energy spectrum;
a plurality of oscillatory signals representing all possible values
of the processed signals which are connected to each of the
sub-computers;
a plurality of final adders for adding the outputs of each of the
sub-computers to generate a plurality of trial signals;
a plurality of comparators for comparing each of the plurality of
trial signals with the scanned signals and generating a comparator
output signal when the trial signal equals the scanned signal;
a coincidence circuit for generating a coincidence signal when all
of the comparator output signals are present; and
a sampling circuit for sampling all of the plurality of oscillatory
signals with the coincidence signal to generate each of the
plurality of processed signals.
11. Apparatus as recited in claim 10 wherein each of the array of
subcomputers comprises:
a source of bias voltage representing the spectral amplitude of the
filtered source in that region of the energy spectrum;
a plurality of amplifiers for each of the plurality of processed
signals having a gain proportional to the absorption coefficient
for the specific material in that region of the energy spectrum and
having the oscillatory signal, representing all values of the
processed signal, as an input;
a sub-adder for adding the source of bias voltage and the output
voltages of each of the plurality of amplifiers; and
means for deriving the exponential of the output of the sub-adder
to form the output of the sub-computer.
12. Apparatus as recited in claim 9 wherein the computer further
comprises:
a memory in which are stored an array of pre-determined values of
each of the plurality of processed signals for each value of each
of the plurality of the scanned signals;
means for addressing the particular arrays of pre-determined values
of each of the plurality of processed signals corresponding to the
particular set of scanned signals being received by the
computer;
means for comparing the particular arrays of pre-determined values
of each of the plurality of processed signals with each other to
determine a set of pre-determined values which provides the closest
match of these signals amongest the arrays; and
means for utilizing the set of pre-determined values which provides
the closest match to form the plurality of processed signals.
13. Apparatus as recited in claim 9 wherein the computer further
comprises:
a memory in which are stored an array of pre-determined values of
sets of the plurality of processed signals for each set of values
of the plurality of scanned signals;
means for addressing a particular set in the array of
pre-determined values of the plurality of processed signals
corresponding to a particular set of the plurality of scanned
signals; and
means for utilizing the particular set of the plurality of
processed signals to form the plurality of processed signals.
14. Apparatus as recited in claim 1 wherein the means for
displaying the processed signals includes a monochrome display
device which is connected to one of the plurality of processed
signals whereby an image is displayed which represents the
absorption due to one of the materials in the object.
15. Apparatus as recited in claim 1 wherein the means for
displaying the processed signals includes a color display device
where each color is modulated by one of the processed signals
whereby an image is displayed which simultaneously represents the
absorption due to the plurality of materials in the object.
Description
BACKGROUND OF THE INVENTION
1. Field of the Invention
This invention relates to x-ray imaging systems. In a primary
application the invention relates to diagnostic x-ray systems where
separate images are created representing specific body materials
and administered contrast material.
2. Description of Prior Art
X-ray images are widely used for industrial testing and for medical
diagnosis. A conventional x-ray image or radiograph records the
transmission of the object to a broad spectrum of x-rays. These
x-rays are normally generated by a high energy electron-beam
stiking a metallic target. The broad-band radiation generated by
this process is called Bremsstrahlung. Different human tissue, such
as soft tissue and bone, have differing absorption vs. energy
characteristics. The bone is highly absorbent at relatively low
energies because of the photoelectric effect where materials with
higher atomic number are dominant. At very high energies, however,
absorption due to Compton scattering is dominant so that absorption
depends almost exclusively on density alone. Thus bone and soft
tissue have similar absorption. The administered contrast
materials, iodine and barrium, have their K absorption edges in
about the middle of the diagnostic x-ray spectrum. It would be
highly desirable if separable images could be made of these various
materials. For example, tumors underlying bone would be made much
more visible on a soft tissue image where the bone structure has
been deleted. Separate images could be made of iodine administered
to the heart and circulatory system which would significantly aid
in medical diagnosis.
Some efforts have been made to provide isolated images of specific
materials. These have been relatively awkward and have involved
mechanically scanned x-ray beams, low-power monochromatic sources,
and mechanical analog computers. A system of this type is described
in Vol. VI of the "Advances in Biological and Medical Physics"
published by the Academic Press in the chapter by B. Jacobson and
R. Stuart Mackay on Radiological Contrast Enhancing Methods. The
section labeled Dichromography, from pages 224 to 231 describes a
system using a x-ray tube having two secondary emitters which
alternately generate two monochromatic x-ray beams. This beam is
mechanically scanned across the region of interest. At each point,
wedge shaped materials of known composition are translated across
the beam until the output beam reaches its predetermined value. The
thickness of the wedges is then a direct indication of the amounts
of the particular material present. A similar approach is described
by B. Jacobson in the American Journal of Roentgenology, Vol. 91,
January 1964, entitled, "X-ray Spectrophotometry in Vivo." In this
article the source was mechanically rotated so as to oscillate
between three monochromatic wavelengths. Wedges representing soft
tissue or water, bone, and iodine were used in a mechanical analog
computer to determine the thickness of these body materials at each
point in the scan.
Although these systems gave interesting results they suffered from
using slow mechanical scans which required a long time to create an
image. Normal heart and respiratory motions during the scanning
time resulted in a blurred, low-resolution image. In addition, the
use of a mechanical analog computer resulted in a relatively long
computation time for each element.
SUMMARY OF THE INVENTION
An object of this invention is to provide images of specific body
materials from x-ray images taken at different spectral energy
distributions.
It is also an object of this invention to create the x-ray images
at different spectral energy distributions in a parallel fashion
whereby every region is recorded simultaneously.
Briefly, in accordance with the invention an array of x-ray images
are recorded using a different x-ray energy spectrum with each
image. The recorded images are scanned providing an array of output
signals for each point. These are processed by a computer to
provide signals representing the thickness of the different
materials. The resultant signals are displayed either individually
or in a composite image.
BRIEF DESCRIPTION OF THE DRAWINGS
For a more complete disclosure of the invention, reference may be
made to the following detailed description of several illustrative
embodiments thereof which is given in conjunction with the
accompanying drawings, of which:
FIG. 1 is a block diagram illustrating an embodiment of the
invention using a fluorscope;
FIG. 2 illustrates an embodiment using a flying-spot scanner
scanning x-ray films; and
FIG. 3 is a block diagram illustrating an embodiment of a computer
for processing the scanned signals.
DESCRIPTION OF THE PREFERRED EMBODIMENT
An understanding of the broad aspects of the invention may best be
had by reference to FIG. 1 of the drawings. An x-ray source 10, of
the conventional electron beam variety generates a diverging beam
of x-rays having a braod energy spectrum. The energy spectrum of
the beam is filtered by filter 11 which represents any of a wide
selection of filters which can be utilized. The object under study
12 is normally a portion of the human anatomy. It is shown as being
composed of regions of different materials 26, 27, and 28. For
example 26 might be a bony region, 27 a soft tissue region, and 28
a large vessel into which iodine contrast material had been
administered. The thicknesses of these various regions is given by
Z.sub.1, Z.sub.2, and Z.sub.3 respectively. Each of these
thickneses are functions of the lateral coordinates and represent
the desired processed images. The transmitted x-rays impinge on
scintillating screen 13 and generate a visible image. As in
conventional fluorscopic practice, this scintillation image is
imaged onto television camera 15 using lens 14. An image
intensifier is often used with the television camera. A separate
image is created for each different filter 11 which is used. For
each image the scanned output signal of television camera 15 is
stored in a different region of video storage system 17 by
switching switch 16. This video storage system can be a few tracks
of a magnetic video disc, or a few video storage tubes such as the
Lithicon made by Princeton Electronic Products. The stored scanned
video signals, 18, 19, and 20, represent the transmission of the
object 12 to various energy spectra as determined by the particular
filter 11. These are applied to computer 21 to calculate the
processed signals which represent thicknesses, Z.sub.1, Z.sub.2,
and Z.sub.3 of the individual materials making up the object 12.
The computer 21 performs the desired calculations and generates the
appropriate processed thickness-indicating signals 22, 23, and 24
representing specific materials. These are displayed either
individually on display 25, or in some composite fashion such as in
color.
The recorded intensity pattern I.sub.n (x,y) due to filter n is
given by
I.sub.n = .intg. a.sub.n (.lambda.) exp -[k.sub.1 (.lambda.)Z.sub.1
+ k.sub.2 (.lambda.)Z.sub.2 + k.sub.3 (.lambda.)z.sub.3
]d.lambda.
where a.sub.n (.lambda.) is the transmitted x-ray energy spectrum
as modified by the inserted filter 11 and the spectral sensitivity
of the screen 13. The various k.sub.m (.lambda.) represent the
linear absorption coefficients of the body materials 26, 27, and
28. Three different materials are given as an example. Each of the
thickness values Z.sub.m are functions of x and y and represent the
desired processed images. A different integral equation will exist
for each new filter 11, which provides a unique a.sub.n (.lambda.).
To obtain a unique solution, the number of integral equations must
be to equal or greater than the number of materials to be
identified. Thus the number of images I.sub.n taken with different
filters 11 providing different spectra a.sub.n (.lambda.) must be
equal to or larger than the number of regions in the object 12.
In addition, to obtaining the different images by fluoroscope, as
illustrated in FIG. 1, x-ray films may be used. Fluoroscopic screen
13 in FIG. 1 is replaced by either x-ray film or the conventional
x-ray screen-film cassettes. As before an array of films are
recorded with each using a different x-ray energy spectrum as
determined by the filter 11. The resultant developed films 34, 35,
and 36 are processed as shown in FIG. 2. Each of the films is
scanned simultaneously. This can be accomplished by a number of
synchronous scanners or, as shown in FIG. 2, using a single scanner
with appropriate beam splitters. Flying spot scanner 30 produces a
scanning spot which is imaged using lens 31 and partially silvered
mirrors 32 and 33 onto x-ray film transparencies 34, 35, and 36.
The transmitted light through each of these films is collected by
photomultipliers 37, 38, and 39 respectively. These produce scanned
signals 18, 19 and 20 which are applied to computer 21 exactly as
the stored signals in FIG. 1. Care must be taken to insure that the
films are properly registered with respect to the raster of flying
spot scanner 30.
Many alternate configurations can be used. The films can be scanned
in sequence with the resultant signals stored on a magnetic disc as
shown in FIG. 1. The films could also be mounted on a rotating drum
scanner with a pickup device for each film.
The scanning signals 18, 19 and 20, giving the intensities due to
the different x-ray spectra at every point in the image are then
applied to computer 21 as shown in FIG. 1. This computer must be
capable of solving the integral equation given previously and thus
find the processed Z.sub.m values when given the scanned signals
representing the intensity values I.sub.n. The solution of this
equation is quite straightforward if monochromatic x-ray sources
are used. In that case the various a.sub.n and k.sub.m values
become constants so that the integral equation becomes an algebraic
equation. For example, using two monochromatic sources a.sub.1 and
a.sub.2 for an object containing two material regions z.sub.1 and
Z.sub.2 the equations are given by
ln I.sub.1 = ln a.sub.1 - [k.sub.11 Z.sub.1 + k.sub.21 Z.sub.2
]
and
ln I.sub.2 = ln a.sub.2 - [k.sub.12 Z.sub.1 + k.sub.22 Z.sub.2
],
where k.sub.12 is the absorption coefficient in the Z.sub.1 region
at the wavelength of the a.sub.2 source. Solving for Z.sub.1 and
Z.sub.2 we have
Z.sub.1 = k.sub.22 ln a.sub.1 - k.sub.21 ln a.sub.2 /(k.sub.11
k.sub.22 - k.sub.12 k.sub.21) - k.sub.22 ln I.sub.1 - k.sub.21 ln
I.sub.2 /(k.sub.11 k.sub.22 - k.sub.12 k.sub.21)
= A - B ln I.sub.1 + C ln I.sub.2
Z.sub.2 = k.sub.11 ln a.sub.2 - k.sub.12 ln a.sub.1 /(k.sub.11
k.sub.22 - k.sub.12 k.sub.21) - k.sub.11 ln I.sub.2 - k.sub.12 ln
I.sub.1 /(k.sub.11 k.sub.22 - k.sub.12 k.sub.21)
= D - E ln I.sub.2 + F ln I.sub.1.
Thus, using monochromatic sources, a simple computer can be built
for finding the processed images Z.sub.1 and Z.sub.2 using I.sub.1
and I.sub.2 scanned signals. The logarithmic operation can be done
in digital fashion using well-known algorithms or with analog
components. One straightforward analog approach is the use of the
forward characteristic of a semiconductor diode where the voltage
is the log of the diode current. The constant terms A,B,C,D,E and F
are all precalculated and built into the computer since only the
scanned signals I.sub.1 and I.sub.2 will vary from point to point.
The extension into more Z regions with more monochromatic sources
is straightforward algebra with the solution for each processed Z
region again requiring the sum of constant terms plus the logs of
the I.sub.n signals.
Monochromatic x-ray sources can be obtaned using radioactive
materials, although these are often relatively weak. To obtain
stronger monochromatic x-ray sources secondary or fluorescent
excitation can be used. Here broad-band x-ray radiation from an
x-ray tube impinges on a target containing an element having a
relatively high atomic number. The bombarded element fluoresces and
emits a monochromatic x-ray beam at its K absorption wavelength.
Thus iodine emits at about 33kev when bombarded with a broad-band
source. The secondary emitter thus becomes filter 11 in FIG. 1
where the emission rather than the transmission of the filter is
used. It is preferable to use the secondary emitted beam which is
emitted at about 90.degree. to that of the source. Thus the
fluorescing element is placed at a 45.degree. angle to the beam to
maximize the energy of the secondary excitation. The references
cited in the "Description of Prior Art" give detailed information
on the generation of monochromatic radiation in the manner.
Significantly stronger sources, however, are obtained with
broad-band filtered sources as shown in FIG. 1. Here again a number
of images I.sub.n are obtained with different spectral regions
a.sub.n (.lambda.). As before the number of scanned images must be
at least as great as the number of distinct Z regions to be
processed. However, since the spectral regions are now broad-band,
it requires the solution of a set of integral equations to evaluate
the various processed Z regions. One method of solution is the use
of a special purpose computer as shown in FIG. 3. Here the integral
equation is divided up into an array of sub-regions of the energy
spectrum where a(.lambda.) and k(.lambda.) are approximately
constant.
Again, using two I.sub.n values and two Z regions for an example,
these equations are given by
I.sub.1 = .sub.i.sup..sigma. w.sub.i a.sub.i exp - (k.sub.li
Z.sub.1 + k.sub.2i Z.sub.2),
and
I.sub.2 = .sub.j.sup..sigma. w.sub.j a.sub.j exp - (k.sub.lj
Z.sub.1 + k.sub.2j Z.sub.2),
where w is the integration interval, .lambda..sub.2 -
.lambda..sub.1, in which a and k are relatively constant. In FIG.
3, as an example, two sub-computers which compute each integration
region are shown for each summation. In the computer two
oscillatory signals 57 and 58 supplying V.sub.1 and V.sub.2 are
used to cycle through all possible values which processed signals
Z.sub.1 and Z.sub.2 might have. For each set of V.sub.1 and V.sub.2
values, a set of I.sub.1 and I.sub.2 trial signals, 74 and 75 are
computed. These trial signal values are compared with the actual
values of scanning signals I.sub.1 and I.sub.2, 18 and 19 obtained
by scanning the appropriate stored images. The comparison takes
place in comparators 71 and 72 which are standard comparator
circuits, such as longtail pairs, which generate a pulse when a
successful comparison is obtained. These comparator output pulses
are both applied to And Gate 73 which, as with any coincidence
circuit, generates an output coincidence signal or pulse only when
both input comparator output pulses are present. The presence of a
coincidence signal thus indicates that the V.sub. 1 and V.sub.2
values at that instant are the correct ones. The coincidence signal
is then applied to sample and hold circuits 59 and 60 which clamp
the V.sub.1 and V.sub.2 values to provide the desired processed
Z.sub.1 and Z.sub.2 output signals 22 and 23. These are used in the
final display 25 as shown in FIG. 1.
In the computer itself an array of sub-computers are used for each
integration interval. For example in one subsection 45, 46, and 47
provide the three terms ln w.sub.1 a.sub.1, k.sub.11 V.sub.1 and
k.sub.21 V.sub.2. The first term is provided by 45, a constant or
bias term, while the second two, 46 and 47, are provided by
amplifiers having gains of k.sub.11 and k.sub.21 respectively with
inputs of oscillatory signals V.sub.1 and V.sub.2 from sources 57
and 58. These are added in sub-adder 61. The resultant sum becomes
the argument of an exponent in 65. This exponential device 65 can
either be a digital system or an analog device such as a
semiconductor diode where the diode current is the exponential of
the diode voltage. The sub-computer output 65 thus represents one
term of the summation of regions of integration in which the a and
k values are relatively constant. A similar term is calculated by
adding constant term ln w.sub.2 a.sub.2 in 48 to k.sub.12 V.sub.1
the output of amplifier 49 and k.sub.22 V.sub.2 the output of
amplifier 50 in sub-adder 62. The exponential of the output of
adder 62 is derived in 66. The output of all of the exponent
devices 65, 66, and the output of similar structures not shown,
such as 76 are all added together in final adder 69 to provide the
computed intensity signal 74 for comparison. An identical complete
system is provided for each intensity signal. For example in FIG.
3, where two scanned intensity signals are used to define two
processed Z regions, sub-adder 63 takes the sum of constant term ln
w.sub.3 a.sub.3 from 51, k.sub.13 V.sub.1 from amplifier 52 and
k.sub.23 V.sub.3 from amplifier 53. The exponential of this sum is
taken by system 67 which is identical to those of 65 and 66. This
outout plus that of 68 and of others, such as 77 are added in final
adder 70 to provide the second computed trial signal 75 for
comparison.
Each of the blocks in FIG. 3 can be well-known analog or digital
circuitry. The number of regions used, where a.sub.n and k are
assumed constant, will determine the resultant accuracy. The
sources of oscillatory signals, 57 and 58, can be a low and high
frequency sawtooth waveform, respectively. Thus, as one waveform is
being varied over its entire range, the other is being rapidly
cycled over its range so as to assume all of its values for every
value of the slow waveform. The processing time for each picture
element will be one cycle of the low frequency sawtooth. With high
speed circuitry this could, for example, be about 10 usec. with the
period of the high frequency sawtooth being about a factor of one
hundred less or about 0.1 usec.
Many variations can be made on the computer shown in FIG. 3. For
example, instead of using regions where the k values are constant,
each region can represent a linear part of the k(.lambda.) curve
where k(.lambda.) is given by
k(.lambda.) = k.sub.o .+-. k.sub.1 .lambda.
Although each region would be somewhat more complex, the number of
separate integration regions would be less since a curve can be
broken up into considerably fewer linear values than constant
values. Other variations include approximating a(.lambda.) in a
linear form for greater accuracy.
Another approach to the computation is the use of a table-look-up
system where the integral equation is solved beforehand using a
variety of processed Z values. Thus, for each scanned intensity
value, an array of possible combinations of processed Z values
which can produce that particular scanned intensity value are
selected. This is done for each scanned intensity signal I.sub.n.
The various listings of combinations of processed Z values are
compared to determine which most closely fits. For example, assume
we are evaluating a two-material region by recording two intensity
values, I.sub.1 and I.sub.2. At each position the values I.sub.1
and I.sub.2 are each used to bring forth a set of Z.sub.1 and
Z.sub.2 values which can produce the values I.sub.1 and I.sub.2 as
determined by pre-calculation. The Z.sub.1, Z.sub.2 set for the
particular I.sub.1 is compared to the Z.sub.1, Z.sub.2 set for the
particular I.sub.2 to determine the closest match, and thus
determine Z.sub.1 and Z.sub.2 for that point. This operation is
best accomplished on a digital computer using a pre-calculated
read-only memory. As an alternative to pre-calculation, the various
Z values corresponding to I values can be determined experimentally
using known materials.
A more rapid digital computation method can be used which also uses
a read-only memory but avoids the comparison of the sets of
processed Z values. A multi-deminsional read-only memory is used
with the number of dimensions determined by the number of scanned
intensity signals used. For each set of scanned intensity signals,
the corresponding set of processed Z values are stored. For
example, if the scanned signals at some point are I.sub.1d,
I.sub.2d, and I.sub.3d, the memory would be addressed using those
three dimensions. The Z values corresponding to those I values
would be read out directly without requiring a comparison
operation. As before, the stored Z values can be pre-determined by
calculation or experiment. For scanned intensity signals which are
intermediate the pre-determined stored values, a system of
interpolation can be used to determine the most accurate set of
processed Z values.
The various systems described are capable of converting the
information from an array of scanned intensity patterns
representing the transmission at different x-ray energies to an
array of processed images representing specific materials within an
object. In medical diagnosis, for most studies, the delineation of
three materials would be very significant. These are bone, soft
tissue which is mostly water, and contrast material containing
iodine or barium. When choosings filters 11 or monochromatic
sources to get the required three intensity pattern, it is
preferable that each spectrum produces relatively different
absorption characteristics in the materials of interest. In theory,
the three material regions can be isolated as long as the three
spectral regions used are, in any way, different. Insufficient
differences, between energy spectra however, will lead to a noise
problem in reconstructing the three material regions. Assume that
the region of interest consists of soft tissue, bone and iodine
contrast material. An example of three energy spectra for this case
is an unfiltered spectrum, a spectrum filtered with iodine material
and a spectrum filtered with tantalum foil. The latter two
materials would each form filter 11 in FIG. 1. The broad unfiltered
spectrum would have significantly higher absorption for bone than
soft tissue in the lower energy regions while having comparable
absorption for the two in the higher energy region dominated by
Compton scattering. The spectrum filtered by tantalum foil however
would have negligible transmission beyond its K edge at about 65
Kev and thus transmit primarily in the region where the bone
absorbs significantly more than does soft tissue. Thus the
unfiltered spectrum and the spectrum with a tantalum filter can
reasonably separate bone and soft tissue. The iodine filter has a
strong absorption-edge at about 33 Kev as does the iodine within
the body. Thus, when the iodine material is used as filter 11, the
iodine contrast in the body is relatively low. When the other two
spectra are used, the unfiltered and the tantalum filter, the
output around 33 Kev is relatively high, causing significant
contrast due to the absorption of iodine within the body. Thus the
three spectra chosen will provide significant absorption
differences for the three materials of interest to be able to
isolate these materials using the computer systems shown. A variety
of other filters can be used to allow a variety of materials to be
isolated. For example, certain materials such as phosphorus are
known to be selectively taken up in diseased regions of the body
such as tumors. The system described here can be used to make an
isolated image of this selectively taken up material to allow
tumors to be found at a relativelyy early stage.
* * * * *