GB1603796A - Creación de Inventos y Patentes con Inteligencia Artificial

GB1603796A – High speed computerized tomography imaging system
– Google Patents

GB1603796A – High speed computerized tomography imaging system
– Google Patents
High speed computerized tomography imaging system

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Publication number
GB1603796A

GB1603796A
GB2367578A
GB2367578A
GB1603796A
GB 1603796 A
GB1603796 A
GB 1603796A
GB 2367578 A
GB2367578 A
GB 2367578A
GB 2367578 A
GB2367578 A
GB 2367578A
GB 1603796 A
GB1603796 A
GB 1603796A
Authority
GB
United Kingdom
Prior art keywords
ray
array
detectors
detector
sources
Prior art date
1977-10-03
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)

Expired

Application number
GB2367578A
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)

General Electric Co

Original Assignee
General Electric Co
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
1977-10-03
Filing date
1978-05-26
Publication date
1981-11-25

1977-10-03
Priority claimed from US05/838,458
external-priority
patent/US4129783A/en

1978-05-26
Application filed by General Electric Co
filed
Critical
General Electric Co

1981-11-25
Publication of GB1603796A
publication
Critical
patent/GB1603796A/en

Status
Expired
legal-status
Critical
Current

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Classifications

H—ELECTRICITY

H01—ELECTRIC ELEMENTS

H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS

H01J47/00—Tubes for determining the presence, intensity, density or energy of radiation or particles

H01J47/02—Ionisation chambers

A—HUMAN NECESSITIES

A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE

A61B—DIAGNOSIS; SURGERY; IDENTIFICATION

A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment

A61B6/02—Devices for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis

A61B6/03—Computerised tomographs

A61B6/032—Transmission computed tomography [CT]

A—HUMAN NECESSITIES

A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE

A61B—DIAGNOSIS; SURGERY; IDENTIFICATION

A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment

A61B6/40—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for generating radiation specially adapted for radiation diagnosis

A61B6/4007—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for generating radiation specially adapted for radiation diagnosis characterised by using a plurality of source units

Description

(54) HIGH SPEED COMPUTERIZED TOMOGRAPHY
IMAGING SYSTEM
(71) We, GENERAL ELECTRIC
COMPANY, a corporation organized and existing under the laws of the State of New
York, United States of America, residing at 1
River Road, Schenectady, 12305, State of New
York, United States of America, do hereby declare the invention, for which we pray that a patent may be granted to us, and the method by which it is to be performed, to be particularly described in and by the following statement:- This invention relates to computerized x-ray tomographic imaging apparatus. More particularly, this invention relates to tomographic imaging systems wherein a plurality of x-ray source are simultaneously pulsed to produce x-ray absorption data along a number of intersecting ray paths, and is an improvement in or modification of the subject of our patent No. 1,562,768.
Computerized x-ray tomography is a system for producing images of internal body organs which are free from the shadows of intervening structures. Prior art tomographic equipment, has generally, comprised an x-ray source disposed opposite one or more x-ray detectors on a movable structure. The source and detectors rotate and/or translate in a plane which passes through the body organs undergoing examination to produce electrical signals which are representative of x-ray transmission data along a plurality of ray paths.
The signals are then combined, usually in digital computer equipment, to reconstruct shadow-free images of internal body sections.
Tomography equipment of this type is well known as prior art and described, for example, in U.S. Patent 3,778,614 to Hounsfield and 3,881,110 to Hounsfield et al.
The rate of production of images in a tomography system which incorporates moving sources and detectors is necessarily limited by the time required to accomplish the physical translation or rotation of the mechanism and is, typically, limited to less than one image per second. Such equipment is, therefore, unsuited for viewing moving body organs, for example, a beating heart. Dr. Earl Wood of the Mayo Clinic in a personal communication has recently proposed a tomographic system for imaging moving body organs wherein a plurality of x-ray sources are sequentially pulsed to rapidly produce x-ray transmission data along a number of diverse ray paths.
Methods and circuits for pulsing x-ray tubes are well known in the x-ray arts and are described, for background purposes, for example, in United States Patents 1,647,478; 3,333,104; and 3,567,940.
The x-ray detectors utilized in prior art x-ray tomography apparatus have generally comprised scintillation crystals or phosphor screens coupled to optical detectors, for example, image orthicon or photomultiplier tubes.
Such devices are rather large and must, generally, be utilized with collimation apparatus to achieve fine spatial resolution.
Such scintillation detectors and collimation apparatus are relatively inefficient detectors of x-ray energy. It is, therefore, necessary to expose a patient undergoing tomographic examination in such equipment to a relatively high dose of ionizing radiation.
Our Patent No. 1,561,174 describes a high pressure, xenon filled ionization chamber array which is characterized by high detection efficiency and fine spatial resolution when utilized in x-ray tomography equipment. The detector comprises a large plurality of detector cells separated by substantially parallel metal collector plates which may be focused on a single source of diverging x-rays. X-ray photons entering the detector cells produce ionelectron pairs which drift under the influence of an electric field, to the collector plates.
Derectors of this type are well suited for the efficient detection of diverging x-ray energy which, for example, may be produced from a single x-ray source and collimated to provide a planar, fan-like spatial distribution.
The ion chamber array of that disclosure is, however, relatively inefficient for detecting x-ray energy which originates from an array of spatially separated x-ray sources of the type utilized in the above-described, high speed tomographic equipment. United
States Patents 1,647,478; 3,333,104; 3,567,940; 3,778,614; and 3,881,110 are incorporated herein by reference solely as background material exemplifying prior art.
The invention provides an improvement in or modification of the high speed, tomographic, x-ray imaging system claimed in claim 1 of Patent No. 1,562,768, wherein the x-ray detectors illuminated in each salvo are adapted to be activated in concert with the pulsing of the corresponding x-ray source salvo, and said means for the collection of data are adapted to receive the data produced by said activated detectors.
The invention will be described by way of example with reference to the accompanying drawings, wherein: Figure 1 is a high speed tomography system of the prior art;
Figure 2 is a high speed tomography system of the present invention;
Figure 3 is a single detector cell of the prior art; and
Figure 4 is an ionization chamber array useful with the present invention.
FIG. 1 illustrates a high speed x-ray tomography system of the prior art. An array of pulsed x-ray sources 20 is disposed opposite an array of x-ray detectors 22. Each individual x-ray detector of the array 22 comprises a phosphor screen 24 adapted to emit light in proportion to incident x-ray intensity. Light from the screen 24 is focused by a lens 26 on a television camera type pick-up tube, typically an image orthicon 28. Electrical signals, from each tube 28, which represent a linear distribution of x-ray intensities across the width of a screen 24, are transmitted to a digital computer for processing into x-ray tomographic images.
Body structures 30 undergoing examination are interposed between the source array 20 and the detector array 22. Each x-ray source in the array 20 is sequentially pulsed to produce a swath of ionizing radiation 32 which is attenuated in varying degrees by the body suucture 30 and impinges on the detector array 22. The individual elements of the array 20 may be pulsed in rapid sequence to provide x-ray transmission information along a plurality of intersecting paths through the body structure 30 from which image information may be constructed. Each source in the array 20, however, necessarily illuminates substantially the entire detector array 22 and the rate of sequential pulsing of the individual sources is, therefore, necessarily limited by the speed at which data may be read from the detector elements (i.e., pick-up tubes 28). Information produced from a single x-ray pulse must be completely read out from a detector 28 before another source in the array 20 is pulsed in order to eliminate a redundancy of information which would occur if x-rays from two sources reached the same tube during a single readout period.
FIG. 2 represents an improved high speed tomography system of the present invention.
A substantially semicircular array of x-ray sources 20 comprises a plurality of individual x-ray tube anodes 40 separated by an array of collimators 42. The geometry of the collimators 42 is selected so that the xray beam from each anode 40 is restricted to a substantially planar, sectorial swath. X-ray energy in each swath passes through a body structure 30 and impinges on a curvilinear array of closely spaced, ionization chamber, detectors 44 disposed in the plane of the x-ray swath. The dimensions and geometry of the collimators 42 are adapted to limit the width of each x-ray swath so that it illuminates only a substantially small sector of the array 44. Thus, in the illustration of FIG. 2, xrays from anode 40a pass through collimator 42a to form a sectorial swath 46a which impinges on a small group 48a of detectors in the array 44. Likewise, x-rays from the anode 40b pass through the collimator 42b and impinge on a separate and distinct group 48b of detectors in the array 44.
The x-ray sources in the array 20 are pulsed in salvos under the control of the sequential salvo pulse firing control unit 45, the grouping of sources in each salvo being chosen so that the individual sources 40 in the salvo illuminate separate and distinct groups of detectors in the array 44. The x-ray detectors illuminated in each salvo are activated in concert with the pulsing of the corresponding x-ray source salvo in that, after each salvo of sources is pulsed, data from the detectors is converted into digital signals by the analogto-digital converter 47 (shown connected to the sequential salvo pulse firing unit 45 to indicate activation of the detectors in concert with the pulsing of the sources in that salvo) and is sent to a digital computer 49 for processing. Another salvo of sources, similarly chosen to illuminate other distinct detector groups, is then pulsed also under control of the firing unit 45.
Each detector in the array 44 will, in general, receive x-ray data from a number of sequential salvos. The groups of the individual detectors which are illuminated by the sources in each salvo will, however, change. The number of sources which may be simultaneously pulsed in each salvo is, of course, a function of the system and collimator geometry which, in turn, is determined by the size of the body structure examined, the spatial resolution required, and the desired image production time. Depending on this geometry and the number of detectors and sources in the arrays, the speed of image processing may be increased by a factor of two or more over prior art tomography systems.
The detector array 44 may comprise ionization chambers of the type described in the above-mentioned patent No. 1,561,174, which is incorporated herein, by reference, as background material. That detector comprises an array of detector cells defined between individual sheet collector electrodes which are disposed substantially parallel to the direction of the incident x-ray beam and perpendicular to the plane of the x-ray swath. The individual cells of such a detector are focused on a single source to provide high efficiency x-ray collection and detection, and such a detector is well suited for use in conventional tomography
apparatus which comprises a single x-ray source. When used in a multiple source tomography system, this array suffers from a substantial loss of detection efficiency for x-rays which originate off the focal point of its individual cells. The cause of this inefficiency may be noted by reference to FIG. 2 and FIG.
3 which is an enlarged view of an individual detector cell illuminated by the x-rays from a source lying outside its focal region and
incident on the plane of the cell at an angle ,8.
If R is the radius of the detector arc and P is the radius of the field of view at the body
30, the maximum value of the angle , occurs
at the edge of each view such that sin ,B= P/R. In a typical system of the type illustrated
in FIG. 2 used, for example, for viewing a beating heart, P equals approximately 20 centimeters and R equals approximately 75 centimeters, yielding a maximum angle, , of 16″.
The efficiency of the cell for oblique detection angles is determined by the snacing d of the collector electrodes. The spacing d is determined, among other factors, by the degree of spatial resolution required by the system and by the time required for the electrons and ions produced within a cell to drift under the influence of an electric field to the individual electrodes. If, for example, the cell is filled with a xenon detector gas at a pressure of approximately 20 atmospheres, a spacing, d, of approximately 1 mm is required to obtain a 1 millisecond response time. The response of such a cell, with 1 millimeter electrode spacing, for x-rays incident at an angle of 16 will be only approximately 14 percent of its efficiency for x-rays incident at an angle of 0 . This loss of efficiency introduces serious calibration problems into image reconstruction algorithms and necessarily increase the radiation dose which is required to produce an image of given resolution. The calibration problem in a multiple source array is, of course, greatly increased by the fact that the angle of incidence of x-rays on each cell is different for each detector and large numbers of calibration factors must, therefore, be stored and utilized.
FIG. 4 is an ion chamber array which has a substantially constant detection efficiency for varying angles of x-ray incidence. A pair of planar, conductive anodes 50 and 52 are disposed parallel to an incident sheet of x-ray radiation 54. A plurality of rod-like cathodes 56 are disposed, equi-distant between the anodes 50 and 52 and substantially parallel, one to the other, with their longest dimension generally parallel to the incident x-rays. One terminal of a voltage source 58 is connected to the anode sheets 50 and 52. Each of the cathodes 56 is connected through one of a plurality of current detector circuits 60 to the other terminal of the voltage source 58. In a preferred embodiment of the invention, a common node of the voltage source and the current detectors represents ground potential.
It will be recognized, by those skilled in the art, that the polarity of the voltage source and the position of the ground connection may be varied without affecting the utility of the invention and that the designation of the collection electrodes 50, 52, and 56, as anodes and cathodes is for ease of description only.
A detector gas 62 fills the space between the anode sheets 50 and 52 and the cathodes 56. The gas type, gas pressure, and the spacing
W between the electrodes are chosen using methods well known to the art so that a large fraction (typically more than 70 percent) of the incident x-ray photons are absorbed within the gas. The detector gas 62, typically comprises rare gas of high atomic number; for example, xenon, krypton, argon, or a molecular gas comprising atoms having an atomic weight greater than that of argon (i.e., 39.9); at a pressure in the range from approximately 10 atmospheres to approximately 100 atmospheres.
Incident x-rays 54 interact with the detector gas 62 between the anodes 50 and 52 to produce electron-ion pairs. The electrons drift under the infiuence of the electric field, imposed by the voltage source 58, to the anode plates 50 and 52 while the ions are similarly collected on the cathodes 56. Ion current flow to any individual cathode 56 is proportional to the number of interactions between photons and gas atoms in the region of that cathode so that the distribution of current flow among the individual current detector circuits 60 of the array is a function of the distribution of xray intensity along the detector array. The direction of electron and ion motion within the detector is substantially perpendicular to the array length and to the incident x-ray beam.
The cathodes 56 may be arrayed parallel one to the other to produce a linear detector array. Alternatively, the detectors may lie at small angles, one to the other, to define a curved or semicircular array of the type illustrated in Fig. 2.
The tomography system described herein allows fast and accurate imaging of internal body organs and is insensitive to the blurring effects which motion of those organs tends to produce in prior art systems. The system is also highly efficient for producing moving pictures of body organs3 for example, of a beating heart.
WHAT WE CLAIM IS:
1. An improvement in or modification of the high speed, tomographic, x-ray imaging system claimed in claim 1 of patent No.
1,562,768, wherein the x-ray detectors illuminated in each salvo are adapted to be activated in concert with the pulsing of the corresponding x-ray source salvo, and means for the collection of data from the detectors are adapted to receive the data produced by said activated detectors.
2. A system as claimed in claim 1 wherein said array of x-ray sources is a substantially semicircular array.
3. A system as claimed in claim 1 or 2 wherein said array of x-ray detectors is a substantially semicircular array.
4. A system as claimed in any preceding claim wherein said x-ray detectors are ionization chambers.
5. A system as claimed in any preceding claim wherein said collimating means are further adapted to confine the emission of xrays emerging from each of said sources into a substantially planar3 fan-like beam.
**WARNING** end of DESC field may overlap start of CLMS **.

Claims (5)

**WARNING** start of CLMS field may overlap end of DESC **. also highly efficient for producing moving pictures of body organs3 for example, of a beating heart. WHAT WE CLAIM IS: 1. An improvement in or modification of the high speed, tomographic, x-ray imaging system claimed in claim 1 of patent No.

1,562,768, wherein the x-ray detectors illuminated in each salvo are adapted to be activated in concert with the pulsing of the corresponding x-ray source salvo, and means for the collection of data from the detectors are adapted to receive the data produced by said activated detectors.

2. A system as claimed in claim 1 wherein said array of x-ray sources is a substantially semicircular array.

3. A system as claimed in claim 1 or 2 wherein said array of x-ray detectors is a substantially semicircular array.

4. A system as claimed in any preceding claim wherein said x-ray detectors are ionization chambers.

5. A system as claimed in any preceding claim wherein said collimating means are further adapted to confine the emission of xrays emerging from each of said sources into a substantially planar3 fan-like beam.

GB2367578A
1977-10-03
1978-05-26
High speed computerized tomography imaging system

Expired

GB1603796A
(en)

Applications Claiming Priority (1)

Application Number
Priority Date
Filing Date
Title

US05/838,458

US4129783A
(en)

1976-05-06
1977-10-03
High speed computerized tomography imaging system

Publications (1)

Publication Number
Publication Date

GB1603796A
true

GB1603796A
(en)

1981-11-25

Family
ID=25277126
Family Applications (1)

Application Number
Title
Priority Date
Filing Date

GB2367578A
Expired

GB1603796A
(en)

1977-10-03
1978-05-26
High speed computerized tomography imaging system

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JP
(1)

JPS5464489A
(en)

DE
(1)

DE2842730A1
(en)

GB
(1)

GB1603796A
(en)

NL
(1)

NL7809984A
(en)

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* Cited by examiner, † Cited by third party

Publication number
Priority date
Publication date
Assignee
Title

JPS51126088A
(en)

1975-03-20
1976-11-02
Emi Ltd
Device for inspecting body by transmissive radiation

NL7611391A
(en)

1975-10-18
1977-04-20
Emi Ltd

ROENTGENTER.

JPS5438787A
(en)

1977-09-02
1979-03-23
Toshiba Corp
X-ray source apparatus

1978

1978-05-26
GB
GB2367578A
patent/GB1603796A/en
not_active
Expired

1978-09-30
DE
DE19782842730
patent/DE2842730A1/en
not_active
Withdrawn

1978-10-03
JP
JP12127878A
patent/JPS5464489A/en
active
Pending

1978-10-03
NL
NL7809984A
patent/NL7809984A/en
not_active
Application Discontinuation

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Publication number
Publication date

JPS5464489A
(en)

1979-05-24

NL7809984A
(en)

1979-04-05

DE2842730A1
(en)

1979-04-12

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