WO2015146691A1 - X線撮影装置 - Google Patents
X線撮影装置 Download PDFInfo
- Publication number
- WO2015146691A1 WO2015146691A1 PCT/JP2015/057802 JP2015057802W WO2015146691A1 WO 2015146691 A1 WO2015146691 A1 WO 2015146691A1 JP 2015057802 W JP2015057802 W JP 2015057802W WO 2015146691 A1 WO2015146691 A1 WO 2015146691A1
- Authority
- WO
- WIPO (PCT)
- Prior art keywords
- ray
- energy
- detection element
- energy range
- imaging apparatus
- Prior art date
Links
- 238000003384 imaging method Methods 0.000 title claims abstract description 46
- 238000001514 detection method Methods 0.000 claims abstract description 127
- 238000012545 processing Methods 0.000 claims abstract description 91
- 238000012937 correction Methods 0.000 claims abstract description 87
- 238000004364 calculation method Methods 0.000 claims abstract description 43
- 238000000034 method Methods 0.000 claims description 62
- 230000005855 radiation Effects 0.000 abstract description 8
- 230000008569 process Effects 0.000 description 42
- 238000006243 chemical reaction Methods 0.000 description 10
- 230000014509 gene expression Effects 0.000 description 9
- 238000010586 diagram Methods 0.000 description 8
- 238000005259 measurement Methods 0.000 description 8
- 238000012986 modification Methods 0.000 description 7
- 230000004048 modification Effects 0.000 description 7
- 230000008859 change Effects 0.000 description 5
- 238000000691 measurement method Methods 0.000 description 4
- 238000007781 pre-processing Methods 0.000 description 4
- 238000004088 simulation Methods 0.000 description 4
- 238000001228 spectrum Methods 0.000 description 3
- 229910004613 CdTe Inorganic materials 0.000 description 2
- 238000010521 absorption reaction Methods 0.000 description 2
- 230000005540 biological transmission Effects 0.000 description 2
- 238000002600 positron emission tomography Methods 0.000 description 2
- 239000004065 semiconductor Substances 0.000 description 2
- 230000035945 sensitivity Effects 0.000 description 2
- 238000012935 Averaging Methods 0.000 description 1
- 229910004611 CdZnTe Inorganic materials 0.000 description 1
- 238000000342 Monte Carlo simulation Methods 0.000 description 1
- 238000002083 X-ray spectrum Methods 0.000 description 1
- 238000004458 analytical method Methods 0.000 description 1
- RPPBZEBXAAZZJH-UHFFFAOYSA-N cadmium telluride Chemical compound [Te]=[Cd] RPPBZEBXAAZZJH-UHFFFAOYSA-N 0.000 description 1
- CEKJAYFBQARQNG-UHFFFAOYSA-N cadmium zinc Chemical compound [Zn].[Cd] CEKJAYFBQARQNG-UHFFFAOYSA-N 0.000 description 1
- 238000004891 communication Methods 0.000 description 1
- 230000000593 degrading effect Effects 0.000 description 1
- 230000001066 destructive effect Effects 0.000 description 1
- 238000011161 development Methods 0.000 description 1
- 238000002059 diagnostic imaging Methods 0.000 description 1
- 230000009977 dual effect Effects 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- PCHJSUWPFVWCPO-UHFFFAOYSA-N gold Chemical compound [Au] PCHJSUWPFVWCPO-UHFFFAOYSA-N 0.000 description 1
- 229910052737 gold Inorganic materials 0.000 description 1
- 239000010931 gold Substances 0.000 description 1
- 238000007689 inspection Methods 0.000 description 1
- 230000003993 interaction Effects 0.000 description 1
- 230000001678 irradiating effect Effects 0.000 description 1
- 238000009607 mammography Methods 0.000 description 1
- 239000000463 material Substances 0.000 description 1
- 239000011159 matrix material Substances 0.000 description 1
- 238000010339 medical test Methods 0.000 description 1
- 239000002105 nanoparticle Substances 0.000 description 1
- 238000009659 non-destructive testing Methods 0.000 description 1
- 238000009206 nuclear medicine Methods 0.000 description 1
- 238000003672 processing method Methods 0.000 description 1
- 230000002250 progressing effect Effects 0.000 description 1
- 238000011002 quantification Methods 0.000 description 1
- 238000001959 radiotherapy Methods 0.000 description 1
- 238000012216 screening Methods 0.000 description 1
- 229910052710 silicon Inorganic materials 0.000 description 1
- 239000010703 silicon Substances 0.000 description 1
- 229910052714 tellurium Inorganic materials 0.000 description 1
- PORWMNRCUJJQNO-UHFFFAOYSA-N tellurium atom Chemical compound [Te] PORWMNRCUJJQNO-UHFFFAOYSA-N 0.000 description 1
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/42—Arrangements for detecting radiation specially adapted for radiation diagnosis
- A61B6/4208—Arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector
- A61B6/4241—Arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector using energy resolving detectors, e.g. photon counting
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
- A61B6/03—Computed tomography [CT]
- A61B6/032—Transmission computed tomography [CT]
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/48—Diagnostic techniques
- A61B6/482—Diagnostic techniques involving multiple energy imaging
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/52—Devices using data or image processing specially adapted for radiation diagnosis
- A61B6/5205—Devices using data or image processing specially adapted for radiation diagnosis involving processing of raw data to produce diagnostic data
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
- A61B6/58—Testing, adjusting or calibrating thereof
- A61B6/582—Calibration
- A61B6/585—Calibration of detector units
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
- G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
- G01T1/29—Measurement performed on radiation beams, e.g. position or section of the beam; Measurement of spatial distribution of radiation
- G01T1/2914—Measurement of spatial distribution of radiation
- G01T1/2985—In depth localisation, e.g. using positron emitters; Tomographic imaging (longitudinal and transverse section imaging; apparatus for radiation diagnosis sequentially in different planes, steroscopic radiation diagnosis)
Definitions
- the present invention relates to an imaging apparatus such as an X-ray CT apparatus, and more particularly to an X-ray imaging apparatus equipped with a photon counting X-ray detector.
- the X-ray CT apparatus calculates an X-ray absorption coefficient from an X-ray transmission image (hereinafter referred to as a projection image) of a subject taken from a plurality of directions, and obtains a tomographic image (hereinafter referred to as a reconstructed image) of the subject.
- a projection image an X-ray transmission image
- a reconstructed image a tomographic image
- the integral X-ray detector converts X-rays into light with a scintillator, converts the light into charges with a photodiode, converts the charges into a digital signal with a readout circuit, and outputs the digital signal.
- the readout circuit integrates the charge for each view to obtain a digital signal. A number of X-ray photons are incident between these views, and the amount of signal obtained is a signal amount corresponding to the total energy of the incident X-rays. Therefore, it is impossible to know the energy information of each incident X-ray photon.
- Non-Patent Document 1 the development of an X-ray CT apparatus equipped with a photon counting type X-ray detector has been progressing in recent years.
- This X-ray detector includes an X-ray detection element having a semiconductor detection layer such as CdTe, and a readout circuit that obtains a digital signal by sorting for each energy range according to the energy of incident X-ray photons.
- X-ray detection element having a semiconductor detection layer such as CdTe
- a readout circuit that obtains a digital signal by sorting for each energy range according to the energy of incident X-ray photons.
- charges corresponding to the energy of the X-ray photons are generated in the detection layer.
- the readout circuit reads out this charge so fast that it can be read out one by one by X-ray photons, and counts the number of X-ray photons by classifying into several energy ranges according to the energy of the incident X-rays. .
- the incident energy at this time is determined using the generated charge amount.
- this detection is similarly performed for each of a plurality of X-ray photons, the number of X-ray photons is counted in each energy range, and the count number is converted into a digital signal. By such measurement, a projection image is obtained for each energy range, and by using these, a reconstructed image can be obtained for each energy range.
- pixels may detect fluorescent X-rays generated when X-rays are detected on the detection layer. At this time, incident X-rays are counted off, detection is performed in different energy ranges, and X-ray photons that are not directly incident are counted.
- Such counting errors can be corrected by performing simultaneous measurement.
- This method is performed by, for example, a PET (positron emission tomography) apparatus, and when an X-ray photon is incident on the target element and a signal is also detected at the adjacent element, the signal of the adjacent element is incident on the target element.
- a PET positron emission tomography
- the incident rate X-ray dose incident per unit time
- the possibility of another X-ray photon entering the adjacent element at the same time increases, and errors are likely to occur.
- some of the X-rays that have entered the detection layer pass through the detection layer during the interaction with the detection layer. In this case, it will be mistaken if one X-ray photon having lower energy than the original X-ray is incident. Therefore, it may be counted as X-ray photons with different energy ranges.
- the X-ray imaging apparatus of the present invention uses the digital output value of each X-ray detection element of the X-ray detector as the movement rate of X-ray photons flowing in and out between the X-ray detection elements.
- the digital output value of each X-ray detection element of the X-ray detector Means for correcting is considered.
- the X-ray imaging apparatus of the present invention detects an X-ray photon, discriminates and measures an energy level into a plurality of energy ranges, and includes an X-ray detector comprising a plurality of X-ray detection elements of a photon counting method, A signal collection unit that collects the output of the line detection element to obtain a digital output value; and a data processing apparatus that corrects the digital output value of the X-ray detection element and creates projection data using the corrected digital output value;
- the data processing apparatus includes a correction unit that corrects each digital output value of the plurality of energy ranges for each X-ray detection element.
- the correction unit corrects the digital output value by using a parameter indicating the movement rate of the X-ray photon between the X-ray detection elements and a parameter indicating the energy shift ratio in the X-ray detection element, which are obtained in advance.
- the correction unit uses X-ray photons that are incident on other X-ray detection elements at an energy that is equal to or greater than the detection target energy range of the X-ray detection element in one X-ray detection element to be corrected.
- an inflow amount calculation unit that calculates a digital amount corresponding to the signal amount flowing into the X-ray detection element to be corrected, and removes the digital amount calculated by the inflow amount calculation unit from the digital output value (first One embodiment).
- the correction unit calculates the digital amount corresponding to the X-ray photon that has been energy shifted from the energy range higher than the detection target energy range to the detection target energy range in one X-ray detection element.
- a shift inflow amount calculation unit is provided, and the digital amount calculated by the energy shift inflow amount calculation unit is removed from the digital output value (second mode).
- the correction unit emits an energy shift that calculates a digital quantity corresponding to an X-ray photon incident on one X-ray detection element and shifted to an energy range lower than the detection target energy range.
- An amount calculation unit is provided, and the digital amount calculated by the energy shift outflow amount calculation unit is added to the digital output value (third mode).
- the present invention also includes an arbitrary combination of the first to third aspects described above.
- the present invention it is possible to prevent erroneous measurement of the number of incident X-ray photons for each energy range, and to obtain a correct projection image. In the reconstructed image created from these projection images, it is possible to prevent a decrease in the quantitative value of CT values and the occurrence of artifacts.
- FIG. 1 is a diagram showing an overall outline of an X-ray CT apparatus to which the present invention is applied.
- the X-ray CT apparatus shown in FIG. 1 includes an X-ray source 100, an X-ray collimator 102, an X-ray detector 104, a signal acquisition unit 108, a central processing unit 105, a display unit 106, an input unit 109, a control unit 107, and a gantry rotation.
- the unit 101 and the couch top 103 are configured.
- a plurality of X-ray detectors 104 are arranged in a circular arc shape with the X-ray source 100 as a substantial center, and are mounted on the gantry rotating unit 101 together with the X-ray source 100.
- the number of X-ray detectors 104 is shown as eight, but the number of X-ray detectors 104 is arbitrary, and in an actual apparatus, for example, about 40. It is.
- an X-ray grid (not shown in FIG. 1) is installed in front of the X-ray detector 104, and among the X-rays emitted from the X-ray source 100, the X-rays scattered by the subject 200 and the like. Is prevented from entering the X-ray detector 104.
- the X-ray detector 104 has a structure in which photon counting type X-ray detection elements are two-dimensionally arranged in the channel direction and the slice direction as shown in FIG. 2, for example.
- FIG. 2 shows a part of the X-ray detection element 110 arranged in the X-ray detector 104, in which four pieces in the channel direction and three pieces in the slice direction are cut out.
- the X-ray detection element 110 is arranged such that the channel direction and the rotation direction of the X-ray detector 104 are the same in the slice direction and the rotation axis direction.
- the X-ray detection element 110 is provided with positive and negative electrodes 112 and 113 so as to sandwich the detection layer 111, and a readout circuit 115 (signal collection unit 108) is provided on the electrodes. It has a connected structure.
- the detection layer 111 is made of, for example, a semiconductor material such as CdTe (cadmium tellurium), CdZnTe (cadmium zinc tellurium), Si (silicon), and detects incident X-ray photons and generates an amount of electric charge according to the energy.
- the readout circuit 115 reads out the electric charge generated in the detection layer 111, compares the electric signal generated by the electric charge with a preset energy level, and determines the energy range of the incident X-ray photon energy.
- the readout circuit 115 performs such discrimination for each incident X-ray photon, sorts it into a plurality of energy ranges between one view, and counts the number of each X-ray photon.
- the electrical signal corresponding to each count number output from the readout circuit 115 of each X-ray detection element 110 is output as a digital signal by the signal collection unit 108.
- (B) and (c) of FIG. 3 show, as an example, a state in which the energy range is divided into three and the number of X-ray photons is counted and a signal corresponding thereto.
- a digital signal (digital output value) corresponding to the number of X-ray photons can be obtained for each energy range.
- the number of energy ranges is not particularly limited as long as it is two or more, but in the following, a case where there are two energy ranges, a low energy range and a high energy range, will be described in order to simplify the description.
- the central processing unit 105 mainly processes the digital signal output from the signal collecting unit 108 and performs data processing such as correction and image reconstruction.
- FIG. 4 shows a functional block diagram of the central processing unit 105 that functions as a data processing unit.
- the central processing unit (data processing unit) 105 includes a correction unit 120, an image reconstruction unit 130, a parameter setting unit 140, and a main control unit 150 that controls the flow of data in each unit, for image creation. Performs various necessary calculations. Each calculation of the central processing unit is realized by executing a corresponding calculation program.
- the arithmetic program is stored in the central processing unit 105 in advance. Alternatively, it is uploaded to the central processing unit through a portable medium or communication and executed.
- the central processing unit 105 includes a storage device 160 that stores data and parameters 141 necessary for various calculations as an internal and / or external device.
- the correction unit 120 includes a pre-processing unit 121 and a count correction unit 125 that corrects the number of X-ray photons counted for each element of the X-ray detector 104.
- the pre-processing unit 110 performs processing for removing errors depending on the apparatus and removing signals other than the subject.
- the pre-processing unit 110 performs known processing such as LOG conversion and air correction on the data from the signal collecting unit 108. Process.
- the count correction unit 125 calculates a digital amount to be removed from an output value or a digital amount to be compensated for each energy range for each detection element constituting the detector 104.
- the count correction unit 125 corrects the digital output value of the X-ray detector 104 input from the signal collection unit 108 using the digital quantity calculated by each of the calculation units 122 to 124. The functions of these calculation units will be described in detail later.
- the image reconstruction unit 130 reconstructs a CT image by performing calculations such as a known filter-corrected back projection method and a successive approximation method based on the projection data for each energy range corrected by the correction unit 120.
- the parameter setting unit 140 sets parameters that are directly input from the input device 109, parameters that are determined based on input conditions, and the like, and passes them to the correction unit 120 and the image reconstruction unit 130.
- the display device 106 displays an image created by the image reconstruction unit 130, or displays a GUI for an operator to operate.
- the input device 109 can include a keyboard, a mouse, various operation buttons for instructing start / end of shooting, and the like.
- a photographing method (hereinafter referred to as actual photographing) for photographing a subject 200 to acquire a reconstructed image and a processing method will be described.
- X-rays are emitted from the X-ray source 100.
- the X-ray is irradiated by the X-ray collimator 102 and the irradiation field is limited toward the subject 200 placed on the bed top plate 103, and the X-ray transmitted through the subject 200 is detected by the X-ray detector 104.
- This imaging is repeated by rotating the gantry rotating unit 101 in the rotation direction while changing the X-ray irradiation angle with respect to the subject 200, and a digital signal for 360 degrees is acquired. Shooting is performed during a plurality of views, for example, every 0.4 degrees. Further, during this time, the control unit 107 controls the position of the X-ray focal point. The digital signal obtained in this way is collected by the signal collecting unit 108.
- the data collected by the signal collecting unit 108 is hereinafter referred to as raw data 143.
- the raw data 143 is sent to the central processing unit 105 for correction processing.
- FIG. 5 shows the procedure of the correction process in the central processing unit 105.
- the count correction is first performed on the raw data 143 received from the signal collection unit 108 (S501).
- the count correction corrects the counted number of X-ray photons for each digital signal in the low energy range and the high energy range.
- the parameter 141 stored in the storage device 160 is read out, and correction processing is performed.
- the LOG conversion is, for example, a conversion represented by the equation (1) where the value X before conversion and the value Y after conversion are used.
- a and b are constant coefficients.
- air correction is performed (S503).
- This correction is realized, for example, by subtracting the sensitivity / X-ray distribution data 142 for each energy, which has been created in advance and stored in the storage device 160, from the raw data after LOG conversion.
- Sensitivity / X-ray distribution data 142 is obtained by, for example, irradiating X-rays from the X-ray tube 100 without obtaining the subject 200 and acquiring raw data for each energy, and performing count correction S501 on these, and averaging processing for the view Create by performing LOG conversion.
- the reconstruction processing is performed (S504), and the reconstructed image 145 of the X-ray absorption coefficient distribution of the subject 200 is obtained, for example, for each of the low energy range and the high energy range. To create. Finally, the reconstructed image 145 is displayed on the display device 106 (S505).
- correction processing shown in FIG. 5 is an example, and does not limit the present invention.
- these correction orders may be different, other corrections may be applied, or air correction S503 may not be provided.
- a signal in the high energy range of the target element 11 is represented by a box 610, and a signal in the low energy range is represented by a box 620.
- the signal in the high energy range of the adjacent element 12 is represented by box 710, and the signal in the low energy range is represented by box 720.
- the count number includes X-ray photons (detection target photons) in the detection target energy region incident on the target element 11. ), (1) X-ray photons (inflow photons) that flowed in from the adjacent detection element 12 (arrows indicated by thin solid lines in FIG. 6), (2) higher than the detection target energy region incident on the detection element
- the inflow / outflow due to the energy shift is a one-way movement from the higher energy range to the lower energy range, X-ray photons in the low energy range do not flow into the high energy range of the same element or adjacent elements. However, X-ray photons in the same energy range may flow in and out between adjacent elements.
- the inflow side should be removed on the inflow side, but the outflow side (target element) Then, since it has already been counted, it is only necessary to consider the energy shift, and there is no need to compensate the count number.
- the count correction is performed in consideration of the behavior of X-ray photons (signal inflow / outflow) in such a photocount detector.
- X-ray photons signal inflow / outflow
- the present embodiment is characterized in that all three processes of removal of the inflow from other elements, removal of the energy shift inflow within the same element, and interpolation of unmeasured values within the same element are performed.
- the count correction according to the present embodiment will be described with reference to the flowchart of FIG.
- a parameter indicating the movement rate of X-ray photons between elements and a parameter indicating the energy shift ratio in the same element are obtained.
- the former parameter is a parameter ⁇ H_H indicating the ratio of X-ray photons measured in the high energy range of the target element 11 out of signals incident on the adjacent element 12 in the high energy range depending on the energy range
- Parameter ⁇ H_L indicating the proportion of X-ray photons measured in the low energy range of signals incident in the energy range
- measurement in the low energy range of target device 11 among signals incident on the adjacent device 12 in the low energy range There are three types of parameters ⁇ L_L that indicate the ratio of X-ray photons that are generated , and are determined for each element.
- the parameter indicating the rate of energy shift refers to the rate at which incident X-ray photons with energies in the high energy range are measured as X-ray photons in the low energy range for one element, and the rate of decrease in the high energy range.
- a parameter ⁇ H_L (x) which is a parameter ⁇ H_L (x) indicating a rate of increase in the low energy range.
- ⁇ H_L (x) and ⁇ H_L (x) generally match, but may be different. For example, when energy is lost in the high energy range, it remains in the high energy range, and the lost energy is measured in the low energy range.
- the first method is a method using simulation
- the second method is a method of actual measurement
- the third method is a method of actually measuring one or a few elements and estimating other elements. You may combine these suitably.
- a Monte Carlo simulation simulating the target element 11 and the adjacent element 12 is performed as in the arrangement of FIG.
- the number of X-ray photons flowing into the target element when X-rays are incident on the adjacent element is counted, and the parameters ⁇ H_H , ⁇ H_L , and ⁇ L_L can be obtained.
- X-rays are incident on the target element 11 in consideration of energy, and the parameters ⁇ H_L and ⁇ H_L can be obtained by comparing the count result of the number of X-ray photons and the spectrum of the input X-ray.
- the digital output values P H (x) and P L (x) in the actually measured high energy range and low energy range are measured.
- the X-rays are formed in a dotted or thin slit shape with pinholes or slits as shown in (a) or (b) of FIG. Squeeze and irradiate. From this result, the ratios ⁇ H_L (x) and ⁇ H_L (x) measured as X-ray photons in the low energy range are calculated.
- the count measured in the high energy range may be r H (x) (P H (x) + P L (x)). In some cases it is measured as P H (x). Therefore, the signal from the high energy range is reduced by r H (x) (P H (x) + P L (x)) ⁇ P H (x). On the other hand, expressed this amount at a rate beta H_L (x), since the ⁇ H_L (x) r H ( x) (P H (x) + P L (x)), ⁇ H_L (x) , the following It can be seen that it can be written as equation (2-1).
- the signal to the low energy range increases by r L (x) (P H (x) + P L (x))-P L (x)), and this amount is expressed as ⁇ H_L (x).
- ⁇ H_L (x) r L (x) (P H (x) + P L (x)) so ⁇ H_L (x) can be written as the following formula (2-2) I understand.
- the parameters ⁇ H_H , ⁇ H_L , ⁇ L_L of the target element 11 are calculated as being the same as the parameters of the adjacent element 12. By obtaining in this way, even when there are a plurality of adjacent elements 12 around the target element 11, the parameters can be obtained at a time. On the other hand, it goes without saying that X-rays may enter the adjacent element 12 and the amount of outflow to the target element 11 may be directly measured.
- the adjacent elements 12 are assumed to be elements adjacent in one direction (for example, the channel direction), but the detector aspect ratio and the element interval in the channel direction and the slice direction differ depending on the detector. Therefore, the above-described actual measurement may be performed in both directions to obtain respective parameters. Also in the actual measurement method, the ratios r H (x) and r L (x) of the high energy range and the low energy range may be calculated by obtaining the X-ray spectrum distribution by simulation.
- Equations (3-1) to (3-3) the digital output values P H (m) and P L (m) before correction of the adjacent element 12 are used, but the energy shift in the adjacent element 12 is By considering, the parameter can be determined with higher accuracy.
- the adjacent element 12 uses the previously measured ⁇ H_L , ⁇ H_L, and expressions (4-1) and (4-2) to be described later, the digital output value R excluding the influence of the energy shift. H (m) and R L (m) are calculated, and these are used in place of the digital output values P H (m) and P L (m), from Equations (3-1) to (3-3) Find the parameters.
- the third method is a method of reducing the burden of actually measuring all the elements.
- the parameters are determined by the above-described measurement method, and the values of the parameters are estimated by interpolation or simulation for the detection elements between them. This can reduce the burden of the actual measurement method.
- the parameters ⁇ H_H , ⁇ H_L , ⁇ L_L , ⁇ H_L (x), and ⁇ H_L (x) determined as described above are stored in the storage device 160 and used for the subsequent count correction calculation.
- Inflow removal processing is performed when one X-ray photon is incident on the adjacent element 12 of the target element 11, and when a part of the signal generated at that time is detected by the target element 11, the signal incident from the adjacent element 12 In this processing, the count number erroneously counted as the X-ray photon is removed from the X-ray photon count number of the target element 11 in consideration of the energy.
- the inflow amount calculation unit 122 calculates the number of counts measured by the target element 11, that is, the “photon inflow amount” of the above formula, using the X-ray photons incident on the adjacent elements 12.
- the digital output values in the high energy range and low energy range before the inflow removal processing in the target element 11 are P H (x) and P L (x), respectively, and the energy of the incident X-ray photons is accurately determined.
- the digital output values in the high energy range and the low energy range at the time of measurement are R H (x) and R L (x), respectively, and the digital output value before the inflow removal processing of the adjacent element 12 is P H (m),
- P L (m) and R H (m) and R L (m) be digital output values when the energy of the incident X-ray photon is accurately measured.
- X and m represent the position x of the X-ray detection element to be corrected and the position m of the adjacent element, and it goes without saying that the position x and m change if the position of the target X-ray detection element changes. .
- a count number proportional to the number of photons incident on the high energy range of the adjacent element 12 and a count number proportional to the number of photons incident on the low energy range of the adjacent element 12 are added. Is done.
- the signal 620 in the low energy range of the target element 11 a part (ratio: ⁇ H_L ) of the signal 710 in the high energy range of the adjacent element 12 and the signal in the low energy range of the adjacent element 12 Since a part of 720 (ratio: ⁇ L_L ) can be considered to flow in, the amount of inflow can be expressed as ⁇ H_L R H (m) + ⁇ L_L R L (m).
- ⁇ L_H 0
- the digital amount “inflow amount” to be corrected in the inflow amount removal processing is For high-energy X-ray photons, [R H (m) ⁇ ⁇ H_H ] For low-energy X-ray photons, [R H (m) x ⁇ H_L + R L (m) x ⁇ L_L ] It becomes.
- the counting correction unit 125 performs the inflow amount removal processing by the following equations (4-1) and (4-2) using the “inflow photon amount” calculated by the inflow amount calculation unit 122.
- the signal value when the energy of the incident X-ray photon is accurately measured can be calculated by subtracting the signal flowing from the adjacent element to the target element from the signal value before the inflow amount removal processing.
- the energy shift inflow amount calculation unit 123 removes the number of X-ray photons flowing from the high energy range to the low energy range out of the low energy range count, and then removes the low energy from the high energy range. Calculate the number of X-ray photons that flowed into the range.
- the ratio is ⁇ H_L (x)
- the inflow amount calculated by the energy shift inflow amount calculation unit 122 is ⁇ H_L (x) R H (x).
- the energy shift outflow amount compensation processing is processing for compensating the count number measured as the low energy range out of the count numbers in the high energy range, contrary to the energy shift inflow amount removal processing.
- This amount (energy shift outflow amount) is ⁇ H_L (x) R H (x) when considered in the same manner as in the energy shift inflow amount removal processing. Accordingly, as shown in Equation (6), this value is supplemented to the signal value before the inflow amount removal processing, thereby calculating the signal value when the energy of the incident X-ray photon is accurately measured.
- Equations (7-1) and (7-2) can be written as follows:
- Expressions (8-1) and (8-2) are expressions when the adjacent element 12 is regarded as the correction target element 11, that is, since these two elements are handled in this embodiment, the correction target element 11 and An equation in which the adjacent elements 12 are replaced is established, and can be solved using the simultaneous equations of these one set of equations.
- FIG. 9 shows the processing of the count correction S501 in consideration of such calculation order.
- the digital signal amount R 2 (x) in the high energy range and the digital signal amount R 1 (x) in the low energy range can be obtained (S5015).
- the process proceeds to the process of LOG conversion S502. The subsequent processing is as already described with reference to FIG.
- each energy is obtained by performing the count correction S501 for the count difference caused by the X-ray photons flowing from the adjacent elements and the count difference caused by the energy shift in the same element.
- the number of X-ray photons incident accurately in the range can be obtained, and a correct projection image can be obtained.
- the flow of a signal from the adjacent element prevents the image from being blurred and prevents the resolution from being lowered.
- the inflow removal (FIG. 7: S5012) can be omitted.
- the count correction S501 is performed using the equations (5) and (6) and the parameters ⁇ H_L (x) and ⁇ H_L (x).
- the present invention also includes count correction S501 for inflow amount removal, energy shift inflow amount removal, inflow amount removal and energy shift outflow amount compensation, energy shift inflow amount removal only, and energy shift outflow amount compensation only.
- the energy shift inflow removal processing By performing the energy shift inflow removal processing, it is possible to calculate the number of X-ray photons measured as a low energy range because only a part of the energy is detected even though higher energy X-ray photons are incident. Therefore, from the number of X-ray photons measured in a certain energy range, the number of X-ray photons in which X-ray photons in the higher energy range are mistakenly detected as the lower energy range can be removed by correction, and correct projection data can be obtained. Can do.
- X-ray photons in a certain energy range can be compensated by calculating the number of X-ray photons measured in a lower energy range because only part of the energy is detected. And correct projection data can be obtained.
- the corrected digital signal amount is calculated from a high energy range.
- the corrected low energy digital signal amount R L (x) is calculated in the corrected high energy digital signal amount R H (x), R H ( This is because of using m).
- the second term and the fourth term on the right side of the equation (7-1) having R H (x) mean inflow amount removal processing and energy shift inflow amount removal processing, respectively.
- the signal amount R H (x) is not required to obtain the signal amount R LL (x).
- the digital signal amount R H (x) in the high energy range when including at least one of the inflow removal processing and the energy shift inflow removal processing, it is desirable to obtain from the digital signal amount R H (x) in the high energy range, and when performing only the energy shift outflow compensation processing It may be determined from either the amount of digital signal in the high energy range or the low energy range.
- ⁇ Modification Example 2 of First Embodiment >>
- the case where parameters such as ⁇ H_H , ⁇ H_L , ⁇ L_L , ⁇ H_H (x), ⁇ H_L (x) are obtained in advance and used as fixed values has been described. Accordingly, the parameters can be changed automatically or manually.
- the X-ray CT apparatus of this embodiment is characterized in that it has a function of changing parameters automatically or manually.
- FIG. 10 An example of a functional block diagram of the control unit 107 and the central processing unit 105 of this embodiment is shown in FIG.
- the control unit 107 includes a shooting condition setting unit 170.
- the parameter setting unit 140 of the central processing unit 105 has a function as a parameter calculation unit in addition to the functions shown in FIG.
- the same elements as those in FIG. 4 are denoted by the same reference numerals, and description thereof is omitted.
- the count correction unit 125 includes at least one of the inflow amount calculation unit 122, the energy shift inflow amount calculation unit 123, and the energy shift outflow amount calculation unit 123 shown in FIG. Shall.
- imaging condition setting unit 170 imaging conditions such as the type of subject, the tube voltage to be irradiated, and the type of X-ray filter are set via the input device 109.
- the shooting condition setting unit 170 passes the set shooting condition information to the parameter setting unit 140 of the central processing unit 105.
- the parameter setting unit 140 determines the degree of energy hardening and softening based on the imaging conditions, and changes the parameters ⁇ H_H , ⁇ H_L , ⁇ L_L , ⁇ H_H (x), and ⁇ H_L (x).
- the parameter setting unit 140 changes the parameters ⁇ H_H , ⁇ H_L , ⁇ L_L , ⁇ H_L (x), and ⁇ H_L (x) according to the change in energy estimated from the imaging conditions.
- the braking distance until detection is increased, so ⁇ H_H , ⁇ H_L , ⁇ H_L (x), and ⁇ H_L (x) may be increased.
- the energy in the low energy range is cured, the braking distance until the energy is similarly detected becomes longer, so ⁇ L_L may be increased.
- the energy is softened due to an increase in scattered radiation or the like, the braking distance is shortened, so these parameters may be reduced.
- the parameter setting unit 140 determines the degree of energy hardening and softening based not only on the imaging condition information from the imaging condition setting unit 170 but also on the high energy range and low energy range counts obtained by the signal collection unit 108. You may judge. Accordingly , changing the parameters ⁇ H_H , ⁇ H_L , ⁇ L_L , ⁇ H_L (x), and ⁇ H_L (x) is the same as the case of judging from the imaging conditions.
- FIG. 10 shows a case where the parameter setting unit 140 automatically changes the parameter using the shooting condition from the shooting condition setting unit 170.
- the operator can change the parameter change factor via the input device 109. It is also possible to directly input the energy dependency of the conditions and parameters.
- the parameters ⁇ H_H , ⁇ H_L , ⁇ L_L , ⁇ H_L (x), and ⁇ H_L (x) may be changed by factors other than energy hardening and softening. For example, you may change according to the visibility of an image.
- Second Embodiment In the first embodiment, the case where a signal flows only from one adjacent element 12 has been described. However, in the present embodiment, the flow of signals from a plurality of adjacent elements 12 is considered.
- the adjacent element may or may not be in direct contact with the target element, and may be located at any position with respect to the target element. Furthermore, all X-ray detection elements of the X-ray detector 104 other than the target element may be targeted.
- FIG. 11 shows an example in which the range of the adjacent element 12 is expanded. In the figure, all elements connected by arrows are adjacent elements of the target element 11.
- the signal in the high energy range of the mth adjacent element (an integer from 1 to M other than x) is the signal in the high energy range of the target element.
- the ratio of flowing into the air is denoted as ⁇ H_H (m, x). That is, when there is one adjacent element, the ratio described as ⁇ H_H is expressed as ⁇ H_H (m, x) in order to define each of the plurality of adjacent elements.
- ⁇ H_L is denoted as ⁇ H_L (m, x)
- ⁇ L_L is denoted as ⁇ L_L (m, x).
- This embodiment is generalized by expanding the width of adjacent elements in the first embodiment, and similarly to the first embodiment, the number of X-ray photons incident accurately in each energy range can be obtained, A correct projection image can be obtained.
- Modification Examples 1 and 2 of the first embodiment can be similarly applied to this embodiment.
- the present embodiment is characterized in that the target is an X-ray detector with N energy ranges to be detected (N is an integer of 3 or more).
- a signal in the Nth energy range of the target element 11 is indicated by a box 610
- a signal in the nth energy range is indicated by a box 615
- a signal in the first energy range is indicated by a box 620.
- n is an integer from 2 to (N-1).
- a signal in the Nth energy range of the adjacent element 12 is indicated by a box 710
- a signal in the nth energy range is indicated by a box 715
- a signal in the Nth energy range is indicated by a box 720.
- the parameter ⁇ i_j (i, j: an integer from 1 to N satisfying i ⁇ j) is the same as in the first embodiment from the signal of the adjacent element 12 in the i-th energy range to the target element in the j-th energy range.
- the parameter ⁇ i_j (i, j: integer from 1 to N satisfying i> j) is the same element in the jth energy range from the signal of the target element 11 in the ith energy range.
- the ratio ⁇ i_j represents the ratio of flowing into the j-th energy range in the inflow / outflow of the eleventh signal
- the parameter ⁇ i_j represents the ratio of flowing into the jth energy range in the inflow / outflow. In FIG. 12, these ratios also show only exchanges between the Nth, nth, and first energy ranges, but in reality, the Nth, (N-1),... There are inflows and outflows in all energy ranges of 1.
- n is an integer not less than 2 and not more than (N ⁇ 1)
- the adjacent element 12 flows in from the nth (signal 715) to Nth (signal 710) energy range.
- the inflow from another energy range of the target element 11 is from the (n + 1) th to Nth (signal 610) energy range, and the outflow is from the first (signal 620) to the (n-1) th energy range.
- Pn (x) and Rn (x) in the signal 615 in the n-th energy range can be written as Equation (11).
- FIG. 13 shows the processing of the count correction unit 125 based on the above exchange of signals.
- the digital signal amount R N (x) in the Nth energy range after correction is used by using the digital signal amount P N (x) in the Nth energy range in the raw data 143. calculate.
- the inflow amount removal process and the energy shift outflow amount compensation process are performed.
- the expression (10) is described with respect to the target element 11, but it can be applied to all other elements.
- the digital signal amount R N-1 (x) in the corrected (N-1) energy range is calculated as the digital signal in the corrected Nth energy range obtained previously.
- the amount R N (x) and the digital signal amount P N-1 (x) in the (N ⁇ 1) th energy range in the raw data 143 are used for calculation.
- the inflow removal processing, the energy shift inflow compensation processing, and the energy shift outflow Quantity compensation processing is performed.
- the digital signal amount R i (x) (where i is an integer of 2 or more and (N ⁇ 2) or less) in the first (N ⁇ 1) to first energy range after correction is calculated. Therefore, the process is performed in the same manner as the process S532. That is, in the process S532, among the raw data 143, the digital signal amount P i (x) and the corrected digital signal amount R i + 1 (x) in the (i + 1) th to Nth energy ranges obtained previously, Using R i + 2 (x),..., R N (x) and the parameters ( ⁇ , ⁇ , ⁇ ) 141 stored in the storage device 160, the following equation (11) is calculated. Inflow removal processing, energy shift inflow compensation processing, and energy shift outflow compensation processing are performed. In these processes S532 and S533, similarly to the process S531, the corrected digital signal amount is obtained by solving the M simultaneous equations of Equation (11).
- the corrected digital signal amounts R 2 (x), R 3 (x),..., R N (x) in the second to Nth energy ranges obtained previously are stored in the storage device 160.
- the inflow amount removal processing and the energy shift inflow amount compensation processing are performed by calculating the equation (12).
- the corrected digital signal amount is obtained from M simultaneous equations obtained by using the equation (12) for all the X-ray detection elements 110.
- the digital signal amounts R 1 (x), R 3 (x),..., R N (x) in the first to Nth energy ranges after correction are calculated.
- the process proceeds to LOG conversion S502.
- the subsequent processing is the same as that described in the first embodiment (flow in FIG. 5).
- inflow amount removal processing energy shift inflow amount removal processing, and energy shift outflow amount compensation processing can be performed.
- the number of incident X-ray photons can be obtained.
- in the reconstructed image obtained by reconstructing this projection image it is possible to prevent the CT value from degrading and the occurrence of artifacts.
- Modification Examples 1 and 2 of the first embodiment can be applied to this embodiment as well.
- only one or two of the three processes included in the count correction, the inflow amount removal process, the energy shift inflow amount removal process, and the energy shift outflow amount compensation process may be performed. It may be changed automatically or manually.
- the range of adjacent elements can be expanded to a plurality of elements as shown in FIG. 11 as well as the element immediately adjacent in the channel direction or slice direction. It is.
- the adjacent element may or may not be in direct contact with the target element, and may be in any position with respect to the target element. Furthermore, all X-ray detection elements of the X-ray detector 104 other than the target element may be targeted.
- the present invention is not limited to this, and the number of photons obtained by classifying the radiation incident on the detection element for each energy. It can be applied to any device equipped with a photo-counting radiation detector that counts the number of photons.
- apparatuses to which the present invention can be applied include X-ray CT apparatus for non-destructive inspection, X-ray cone beam CT apparatus, dual energy CT apparatus, X-ray diagnostic imaging apparatus, X-ray imaging apparatus, X-ray fluoroscopic apparatus, mammography , Digital subtraction device, nuclear medicine screening device, radiotherapy device and the like.
- the light may have any wavelength such as visible light, infrared light, ultraviolet light, and gamma rays.
- the present invention is not limited to the above-described embodiment, and various modifications can be made without departing from the scope of the invention at the stage of implementation.
- the above-described embodiment includes various stages, and various embodiments can be obtained by appropriately combining a plurality of disclosed components. For example, some components may be deleted from all the components shown in the embodiment.
- the present invention in an X-ray imaging apparatus equipped with a photocounting radiation detector that separates and counts radiation incident on an X-ray detection element for each energy range, the number of X-ray photons in each energy range It is possible to correct a mistake and obtain a correct projection image. Furthermore, in a CT apparatus equipped with this radiation detector, it is possible to suppress a decrease in quantitativeness of CT values and occurrence of artifacts.
Landscapes
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- Engineering & Computer Science (AREA)
- Medical Informatics (AREA)
- High Energy & Nuclear Physics (AREA)
- Molecular Biology (AREA)
- Physics & Mathematics (AREA)
- Radiology & Medical Imaging (AREA)
- Veterinary Medicine (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Optics & Photonics (AREA)
- Pathology (AREA)
- Biophysics (AREA)
- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
- Public Health (AREA)
- Surgery (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Pulmonology (AREA)
- Theoretical Computer Science (AREA)
- Computer Vision & Pattern Recognition (AREA)
- General Physics & Mathematics (AREA)
- Spectroscopy & Molecular Physics (AREA)
- Measurement Of Radiation (AREA)
- Apparatus For Radiation Diagnosis (AREA)
Abstract
Description
本実施形態は、他の素子からの流入量の除去、同一素子内におけるエネルギーシフト流入量の除去、同一素子内における計測していない値の補間の3つの処理を全て行うことが特徴である。以下、本実施形態による計数補正を、図7のフローを参照して説明する。
補正処理に際し、まず、素子間のX線フォトンの移動割合を表すパラメータ、及び、同一素子内のエネルギーシフトの割合を表すパラメータを求める。前者のパラメータは、エネルギー範囲によって、隣接素子12に高エネルギー範囲で入射した信号のうち、対象素子11の高エネルギー範囲で計測されるX線フォトンの割合を示すパラメータαH_H、隣接素子12に高エネルギー範囲で入射した信号のうち、低エネルギー範囲で計測されるX線フォトンの割合を示すパラメータαH_L、隣接素子12に低エネルギー範囲で入射した信号のうち、対象素子11の低エネルギー範囲で計測されるX線フォトンの割合を示すパラメータαL_Lの3種類があり、素子毎に求める。
流入量除去処理は、1つのX線フォトンが対象素子11の隣接素子12に入射し、その際に生じた信号の一部が対象素子11で検出される場合、その隣接素子12から入射した信号によって誤ってX線フォトンとしてカウントされたカウント数を、そのエネルギーも考慮して対象素子11のX線フォトンのカウント数から除く処理である。
高エネルギーのX線フォトンついては、[RH(m)×αH_H]
低エネルギーのX線フォトンついては、[RH(m)×αH_L +RL(m)×αL_L]
となる。
エネルギーシフト流入量除去処理では、1つのX線フォトンが対象素子11に入射した際、生じた電荷の一部が、X線フォトンのエネルギーより低いエネルギー範囲のX線フォトンとして対象素子11で検出されて誤カウントされたカウント数を補正する。これは、検出されたX線フォトンの信号の一部が隣接素子12で検出される場合や、X線フォトンの一部のエネルギーが吸収されながらも対象素子11を透過した場合などに生じ得る。この現象は、高エネルギー範囲で計測されるX線フォトン数の一部が、低エネルギー範囲に移行しているように見なせるため、図6に示すように、高エネルギー範囲から低エネルギー範囲へカウント数が流入出すると見なすことができる。
次にエネルギーシフト流出量補填処理は、エネルギーシフト流入量除去処理とは反対に、高エネルギー範囲のカウント数のうち、低エネルギー範囲と計測されたカウント数を補填する処理である。この量(エネルギーシフト流出量)は、エネルギーシフト流入量除去処理の場合と同様に考えるとβH_L(x)RH(x)となる。従って、式(6)のように、この値を流入量除去処理前の信号値に補填することで、入射したX線フォトンのエネルギーを正確に計測した際の信号値を算出する。
その際、nの大きい方から(n=2のときから)式を解くことで、出力値RH(x)、RL(x)を算出できる。すなわち、まずn=2のときの式(8-2)を先に解くことで、式(8-1)の右辺の第3項のRH(x)が求められるので、式(8-2)と同様に解くことができる。
第一実施形態では、計数補正において、流入量除去、エネルギーシフト流入量除去、エネルギーシフト流出量補填の3つの処理を全て行ったが、検出器の特性等に応じて、これらの1または2の処理を省くことができる。
第一実施形態では、αH_H、αH_L、αL_L、βH_H(x)、γH_L(x)などのパラメータを予め求め、固定された値として用いた場合を記したが、撮影条件等に応じてパラメータは自動或いは手動で変更する構成とすることも可能である。本実施形態のX線CT装置は、パラメータを自動或いは手動で変更する機能を備えたことが特徴である。
図示するように、制御部107は、撮影条件設定部170を備える。中央処理装置105のパラメータ設定部140は、図4に示す機能に加えて、パラメータ算出部としての機能を備えている。なお図10において、図4と同じ要素については同じ符号で示し、説明を省略する。
また図10では図示を省略しているが、計数補正部125は図4に示す流入量算出部122、エネルギーシフト流入量算出部123、エネルギーシフト流出量算出部123の少なくとも一つを備えているものとする。
第一実施形態では、1つの隣接素子12からのみ信号が流入する場合を説明したが、本実施形態では、複数の隣接素子12から信号の流入を考慮した実施形態である。
本実施形態は、検出するエネルギー範囲がN個(Nは3以上の整数)のX線検出器を対象とする点が特徴である。
一方、対象素子11のほかのエネルギー範囲からの流入は第(n+1)から第N(信号610)のエネルギー範囲からあり、流出は第1(信号620)から第(n-1)のエネルギー範囲へ、ぞれぞれである。従って、第nのエネルギー範囲の信号615においてPn(x)とRn(x)は、式(11)のように書ける。
第三実施形態についても、第二実施形態と同様に、隣接素子の範囲をチャネル方向或いはスライス方向のすぐ隣の素子だけでなく、図11に示したように、複数の素子に広げることも可能である。
第三実施形態では、複数のエネルギー範囲について、それぞれ計数補正するために、式(10)~(12)のようなM次の連立方程式を用いることを説明したが、連立方程式ではなく、さまざまな近似により補正することも可能である。
Claims (14)
- X線フォトンを検出し、エネルギーレベルを複数のエネルギー範囲に弁別して計測するフォトンカウンティング方式の複数のX線検出素子から成るX線検出器と、
前記X線検出素子の出力を収集してデジタル出力値を得る信号収集部と、
前記X線検出素子のデジタル出力値を補正し、補正後のデジタル出力値を用いて投影データを作成するデータ処理装置と、を具備し、
前記データ処理装置は、各X線検出素子について前記複数のエネルギー範囲のそれぞれのデジタル出力値を補正する補正部を有し、当該補正部は、一つの補正対象のX線検出素子において、当該X線検出素子の検出対象エネルギー範囲以上のエネルギーで他のX線検出素子に入射したX線フォトンによって生じ、前記補正対象のX線検出素子に流入する信号量に相当するデジタル量を算出する流入量算出部を備え、前記デジタル出力値から前記流入量算出部が算出したデジタル量を除去することを特徴とするX線撮影装置。 - 請求項1に記載のX線撮影装置において、
前記流入量算出部は、補正対象のX線検出素子の第n(nは1からNまでの整数)番目のエネルギー範囲として計測されるデジタル信号のうち、前記補正対象のX線検出素子に隣接する隣接素子に入射した前記第n番目から第N番目のエネルギー範囲のX線フォトンによって生じた信号量を算出することを特徴とするX線撮影装置。 - 請求項1に記載のX線撮影装置において、
前記補正部は、各X線検出素子について前記複数のエネルギー範囲のそれぞれのデジタル出力値を補正するに際し、高いエネルギー範囲から低いエネルギー範囲の順に補正することを特徴とするX線撮影装置。 - X線フォトンを検出し、エネルギーレベルを複数のエネルギー範囲に弁別して計測するフォトンカウンティング方式の複数のX線検出素子から成るX線検出器と、
前記X線検出素子の出力を収集してデジタル出力値を得る信号収集部と、
前記X線検出素子のデジタル出力値を補正し、補正後のデジタル出力値を用いて投影データを作成するデータ処理装置と、を具備し、
前記データ処理装置は、各X線検出素子について前記複数のエネルギー範囲のそれぞれのデジタル出力値を補正する補正部を有し、
当該補正部は、一つのX線検出素子において検出対象エネルギー範囲よりも高いエネルギー範囲から前記検出対象エネルギー範囲にエネルギーシフトしたX線フォトンに相当するデジタル量を算出するエネルギーシフト流入量算出部と、
一つのX線検出素子に入射し、検出対象エネルギー範囲よりも低いエネルギー範囲にエネルギーシフトしたX線フォトンに相当するデジタル量を算出するエネルギーシフト流出量算出部の少なくとも一方を備え、前記デジタル出力値から前記エネルギーシフト流入量算出部が算出したデジタル量を除去する、または前記デジタル出力値に前記エネルギーシフト流出量算出部が算出したデジタル量を加算することを特徴とするX線撮影装置。 - 請求項4に記載のX線撮影装置において、
前記エネルギーシフト流入量算出部は、補正対象のX線検出素子の第n(nは1から(N-1)までの整数)番目のエネルギー範囲として計測されるデジタル信号のうち、補正対象X線検出素子に入射した第(n+1)番目から第N番目のエネルギー範囲のX線フォトンによって生じた信号量を算出することを特徴とするX線撮影装置。 - 請求項4に記載のX線撮影装置において、
前記補正部は、さらに、一つの補正対象のX線検出素子において、当該X線検出素子の検出対象エネルギー範囲以上のエネルギーで他のX線検出素子に入射したX線フォトンによって生じ、前記補正対象のX線検出素子に流入する信号量に相当するデジタル量を算出する流入量算出部を備え、前記デジタル出力値から前記流入量算出部が算出したデジタル量を除去することを特徴とするX線撮影装置。 - 請求項4に記載のX線撮影装置において、
前記エネルギーシフト流出量算出部は、補正対象のX線検出素子の第n(nは2からNまでの整数)番目のエネルギー範囲に入射したX線フォトンのうち、前記補正対象X線検出素子の第1番目から第(n-1)番目のエネルギー範囲の信号として計測された信号量を算出することを特徴とするX線撮影装置。 - 請求項4に記載のX線撮影装置において、
前記補正部は、各X線検出素子について前記複数のエネルギー範囲のそれぞれのデジタル出力値を補正するに際し、高いエネルギー範囲から低いエネルギー範囲の順に補正することを特徴とするX線撮影装置。 - X線フォトンを検出し、エネルギーレベルを複数のエネルギー範囲に弁別して計測するフォトンカウンティング方式の複数のX線検出素子から成るX線検出器と、
前記X線検出素子の出力を収集してデジタル出力値を得る信号収集部と、
前記X線検出素子のデジタル出力値を補正し、補正後のデジタル出力値を用いて投影データを作成するデータ処理装置と、を具備し、
前記データ処理装置は、各X線検出素子について前記複数のエネルギー範囲のそれぞれのデジタル出力値を補正する補正部を有し、当該補正部は、予め求めたX線検出素子間のX線フォトンの移動割合を示すパラメータとX線検出素子内のエネルギーシフトの割合を示すパラメータとを用いて、前記デジタル出力値を補正する計数補正部を備えたことを特徴とするX線撮影装置。 - 請求項9に記載のX線撮影装置において、
前記補正部は、前記X線検出素子の第n(nは1以上N以下の整数)番目のエネルギー範囲での投影データを算出する際、前記X線検出素子を第1番目から第M番目のM個とし、第x(xは1以上M以下の整数)番目の前記X線検出素子の補正前のデジタル出力値をPn(x)、前記投影データの出力値をRn(x)とし、第h(hは1以上N以下の整数)番目のエネルギー範囲の第a(aは1以上M以下の整数)番目の前記X線検出素子から第i(iは1以上N以下の整数)番目のエネルギー範囲の第b(bは1以上M以下の整数)番目の前記X線検出素子への信号移動割合量をαh_i(a、b)、前記X線検出素子において前記第j(jは1以上N以下の整数)番目のエネルギー範囲から前記第k(kは1以上N以下の整数)番目のエネルギー範囲への信号の流出入のうち、前記第j番目のエネルギー範囲からの流出の割合をβj_k(x)、前記第k番目のエネルギー範囲への流入の割合をγj_k(x)とするとき、式(1-1)~(1-3)に記される式を基に前記投影データの出力値Rn(x)を求めることを特徴とするX線撮影装置。
- 請求項9に記載されたX線撮影装置において、
さらに、各エネルギー範囲について設定した前記パラメータの少なくとも1つを変更するパラメータ変更部を具備することを特徴とするX線撮影装置。 - 請求項11に記載されたX線撮影装置において、
さらに操作者による入力を受け付ける入力装置を備え、
前記パラメータ変更部は、前記入力装置の入力により、前記パラメータの少なくとも1つを変更することを特徴とするX線撮影装置。 - 請求項11に記載されたX線撮影装置において、
さらに被写体の種類、照射する管電圧、X線フィルタの種類の少なくとも1つを決定する撮影条件決定部を備え、
前記パラメータ変更部は、前記撮影条件決定手段の決定結果に応じて前記パラメータの少なくとも1つを変更することを特徴とするX線撮影装置。 - 請求項9に記載のX線撮影装置において、
前記補正部は、各X線検出素子について前記複数のエネルギー範囲のそれぞれのデジタル出力値を補正するに際し、高いエネルギー範囲から低いエネルギー範囲の順に補正することを特徴とするX線撮影装置。
Priority Applications (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US15/122,981 US10292668B2 (en) | 2014-03-26 | 2015-03-17 | X-ray scanning apparatus |
JP2016510264A JP6518651B2 (ja) | 2014-03-26 | 2015-03-17 | X線撮影装置 |
CN201580010467.7A CN106028939B (zh) | 2014-03-26 | 2015-03-17 | X射线摄影装置 |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP2014-064549 | 2014-03-26 | ||
JP2014064549 | 2014-03-26 |
Publications (1)
Publication Number | Publication Date |
---|---|
WO2015146691A1 true WO2015146691A1 (ja) | 2015-10-01 |
Family
ID=54195214
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
PCT/JP2015/057802 WO2015146691A1 (ja) | 2014-03-26 | 2015-03-17 | X線撮影装置 |
Country Status (4)
Country | Link |
---|---|
US (1) | US10292668B2 (ja) |
JP (1) | JP6518651B2 (ja) |
CN (1) | CN106028939B (ja) |
WO (1) | WO2015146691A1 (ja) |
Families Citing this family (5)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP2871496B1 (en) * | 2013-11-12 | 2020-01-01 | Samsung Electronics Co., Ltd | Radiation detector and computed tomography apparatus using the same |
US10281596B2 (en) * | 2015-09-18 | 2019-05-07 | Koninklijke Philips N.V. | Correcting photon counts in a photon counting X-ray radiation detection system |
JP6885803B2 (ja) * | 2017-06-27 | 2021-06-16 | ゼネラル・エレクトリック・カンパニイ | 放射線撮影装置及び撮影方法 |
US11076823B2 (en) * | 2017-06-28 | 2021-08-03 | Canon Medical Systems Corporation | X-ray CT apparatus including a photon-counting detector and circuitry configured to set a control parameter corresponding to a position of each detecting element in the photon-counting detector |
EP3842839A1 (en) * | 2019-12-27 | 2021-06-30 | Koninklijke Philips N.V. | Compensation of polarization effects in photon counting detectors |
Citations (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JP2011085479A (ja) * | 2009-10-15 | 2011-04-28 | Tele Systems:Kk | 光子計数型放射線検出器のキャリブレーション装置及びそのキャリブレーション方法 |
JP2013019698A (ja) * | 2011-07-07 | 2013-01-31 | Toshiba Corp | 光子計数型画像検出器、x線診断装置、及びx線コンピュータ断層装置 |
WO2013048436A1 (en) * | 2011-09-30 | 2013-04-04 | Analogic Corporation | Photon count correction |
Family Cites Families (4)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
DE102010024626B4 (de) * | 2010-06-22 | 2018-12-13 | Siemens Healthcare Gmbh | Zählender Detektor und Computertomographiesystem |
JP5917157B2 (ja) * | 2012-01-13 | 2016-05-11 | 株式会社東芝 | X線ct装置 |
EP2664280A3 (en) * | 2012-05-14 | 2013-12-04 | Samsung Electronics Co., Ltd | X-ray imaging apparatus and control method therefor |
US8958524B2 (en) * | 2013-01-31 | 2015-02-17 | Analogic Corporation | Correction of projection data in radiation system |
-
2015
- 2015-03-17 WO PCT/JP2015/057802 patent/WO2015146691A1/ja active Application Filing
- 2015-03-17 US US15/122,981 patent/US10292668B2/en active Active
- 2015-03-17 JP JP2016510264A patent/JP6518651B2/ja active Active
- 2015-03-17 CN CN201580010467.7A patent/CN106028939B/zh not_active Expired - Fee Related
Patent Citations (3)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JP2011085479A (ja) * | 2009-10-15 | 2011-04-28 | Tele Systems:Kk | 光子計数型放射線検出器のキャリブレーション装置及びそのキャリブレーション方法 |
JP2013019698A (ja) * | 2011-07-07 | 2013-01-31 | Toshiba Corp | 光子計数型画像検出器、x線診断装置、及びx線コンピュータ断層装置 |
WO2013048436A1 (en) * | 2011-09-30 | 2013-04-04 | Analogic Corporation | Photon count correction |
Also Published As
Publication number | Publication date |
---|---|
CN106028939B (zh) | 2019-05-07 |
US10292668B2 (en) | 2019-05-21 |
CN106028939A (zh) | 2016-10-12 |
JP6518651B2 (ja) | 2019-05-22 |
US20170105688A1 (en) | 2017-04-20 |
JPWO2015146691A1 (ja) | 2017-04-13 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
JP6578289B2 (ja) | X線撮影装置 | |
EP2867701B1 (en) | Digital positron emission tomography (dpet) energy calibration method | |
KR20200024299A (ko) | x-선 영상화 시스템에서 기하학적 오정렬 관리 | |
US20080260094A1 (en) | Method and Apparatus for Spectral Computed Tomography | |
WO2012144589A1 (ja) | 光子計数型放射線検出器のキャリブレーション装置及びそのキャリブレーション方法 | |
US9075153B2 (en) | Method for correcting count rate drift in a quantum-counting detector, an X-ray system with a quantum-counting detector and a circuit arrangement for a quantum-counting detector | |
WO2015146691A1 (ja) | X線撮影装置 | |
US11179115B2 (en) | X-ray CT data processing device and X-ray CT device comprising same | |
WO2016147844A1 (ja) | X線ct装置及びマルチエネルギー像作成方法 | |
JP6031618B2 (ja) | X線撮像装置、x線撮像方法、及び、x線撮像装置のモニタリング方法 | |
US11045153B2 (en) | Device for acquiring pulse height spectrum, method for acquiring pulse height spectrum, program for acquiring pulse height spectrum, and radiation imaging apparatus | |
US20170202531A1 (en) | X-ray ct apparatus, information processing device and information processing method | |
JP2022111990A (ja) | 光子計数型x線ct装置及び方法 | |
JP2022113115A (ja) | ビームハードニング補正方法、x線ct装置及びビームハードニング補正プログラム | |
JPH02147883A (ja) | 多チャンネル放射線検出装置 | |
US11879856B2 (en) | Two-step material decomposition calibration method for a full size photon counting computed tomography system | |
JP5240029B2 (ja) | ポジトロンct装置 | |
US11782176B2 (en) | Bad detector calibration methods and workflow for a small pixelated photon counting CT system | |
JP6700737B2 (ja) | 放射線撮像システム、信号処理装置、及び、放射線画像の信号処理方法 | |
US11178346B2 (en) | Charge sharing calibration method and system | |
WO2018030055A1 (ja) | 画像処理装置、x線撮像装置及び画像処理方法 | |
JP4817071B2 (ja) | 核医学診断装置の散乱補正方法及びこれを備えた核医学診断装置 |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
121 | Ep: the epo has been informed by wipo that ep was designated in this application |
Ref document number: 15769771 Country of ref document: EP Kind code of ref document: A1 |
|
ENP | Entry into the national phase |
Ref document number: 2016510264 Country of ref document: JP Kind code of ref document: A |
|
WWE | Wipo information: entry into national phase |
Ref document number: 15122981 Country of ref document: US |
|
NENP | Non-entry into the national phase |
Ref country code: DE |
|
122 | Ep: pct application non-entry in european phase |
Ref document number: 15769771 Country of ref document: EP Kind code of ref document: A1 |