Patent Description:
In the X-ray CT apparatus, the gantry rotation axis or the sample rotation axis (hereinafter referred to as "CT rotation axis") deviates during measurement, thereby causing image degradation. This deviation is called tolerance error, and conventionally correction thereof has been attempted by various methods.

For example, a method of correcting the tolerance error by aligning images is known (See Patent Document <NUM>). In this method, the positional deviation confirmed by superimposing and outputting a two-dimensional projection image and a three-dimensional reconstructed image is corrected. As a result, it is possible to correct the center shift and the SOD (Source-to-Object Distance). In this case, it is possible to increase the accuracy by repeatedly reconstructing the image and using the alignment of the projection image and the projection image of the reconstructed image.

A method of correcting a tolerance error using a sensor is also known (see Patent Document <NUM> and Patent Document <NUM>). By this method, the deviation in the radial and thrust directions can be corrected using distance sensors. In Patent Document <NUM> a compensation mechanism in connection with a CT device is taught. This compensation mechanism is based on a comparison of projection images of a test specimen having a known shape with a real image of the test specimen. Further, Patent Documents <NUM> and <NUM> describe a correction technique that uses a correction phantom in which two spherical balls made of X-ray absorbing material are embedded in a square pillar. Still further, Patent Document <NUM> describes a CT system in which two different sets of image data of a sample are acquired in order to obtain the geometric centroid of the sample for medical CT calibration.

However, when a tolerance error is corrected by alignment of images, a reconstructed image is required, and it takes time to process the reconstruction. Further, in the case of using a sensor, although it does not take a long time for checking the error, the manufacturing cost is increased according to measurement accuracy required for the sensor itself and a way the sensor is installed.

The present invention has been made in view of such circumstances, and an object thereof is to provide a tolerance error estimating apparatus, a method, a program, a reconstruction apparatus and a control apparatus capable of estimating a deviation from a reference position of a drive axis with respect to driving time.

According to the present invention, by estimating the deviation of the rotation drive axis from the reference position with respect to the driving time, it is possible to reduce the burden on correction of the tolerance error.

Next, embodiments of the present invention are described with reference to the drawings. To facilitate understanding of the description, the same reference numerals are assigned to the same components in the respective drawings, and duplicate descriptions are omitted.

An X-ray CT apparatus irradiates a sample with a cone-shaped or parallel beam of X-rays from all angles and acquires a distribution of the absorption coefficient of the X-rays, that is, a projection image, by a detector. To irradiate X-rays from any angle, the X-ray CT apparatus is configured to rotate a sample stage with respect to the fixed X-ray source and the detector or to rotate the gantry integrated with the X-ray source and the detector. The rotation is relative, and a rotation angle refers to an angle that occurs between the gantry and the sample and is also referred to as a projection angle. Incidentally, the rotation angle is basically proportional to rotation driving time.

The X-ray CT apparatus is a type of X-ray analysis apparatus, comprises a CT rotation axis as a rotation driving axis, and acquires X-ray CT projection images as X-ray detection images. When estimating the tolerance error of the X-ray CT apparatus, a reference sample used for acquiring the X-ray detection images is a sphere of uniform density, a specific position used for calculating the amount of deviation is a centroid position of the absorption coefficient.

Thus, the projection is performed from various angles, and the distribution of the linear absorption coefficient of the sample can be estimated by shading of the obtained projection image of the sample. Then, it is called reconstruction that a three-dimensional line absorption coefficient distribution is obtained from two-dimensional projection images. Basically, back-projection of the projection images is performed.

In the X-ray CT apparatus as described above, the adjustment is performed so that the CT rotation axis is positioned at the reference position of the sample placed on the straight line connecting the center of the radiation source and the detector. If the CT rotation axis is rotated during measurement, the CT rotation axis may deviate from the reference position of the sample (tolerance error). <FIG> is a schematic diagram showing a configuration of an X-ray CT apparatus in which tolerance error has occurred. When the CT rotation axis is rotated by a rotation angle θ (gantry rotation angle), the X-ray source F0 and the detector D0 attached to the gantry move to the position of F1 and D1. At the time, the CT rotation axis (gantry rotation axis) coincides with the reference position of the sample at first at the position P0, but the position of the CT rotation axis deviates from P0 to P1 with the rotation of the CT rotation axis. This deviation is the tolerance error.

<FIG> are schematic diagrams of projection images obtained when each tolerance error has occurred. A rectangular frame indicates the region of the entire projection image detected by the detection plane. In the projection image, a direction parallel to the CT rotation axis is defined as v, and a direction orthogonal to v is defined as u. The external shape and centroid (u0, v0) of the projection image of the sample are shown when a sphere of uniform density is used as a reference sample. The projection image when the CT rotation axis is adjusted to be positioned at the reference position of the sample is shown by a broken line.

<FIG> is a graph showing the variation of the centroid position of the projection image in the u direction due to the tolerance error. The position of the centroid of the projection image moves with respect to the center position of the detector, and the direction and amount of movement varies with respect to the rotation driving time (t). Deviation in the direction parallel to the detector plane (u direction) and the deviation with respect to the SOD direction occurring in the CT rotation axis affect the projection image differently.

If the CT rotation axis deviates parallel to the detection surface (<FIG>), the outer shape of the projection image does not change, only the centroid position moves on the detector plane. In the case that there is also a deviation in the SOD direction (<FIG>), even if the movement amount of the centroid position is the same, since the magnification ratio varies when a deviation occurs in the SOD direction, the size of the outer shape of the projection image also changes accordingly. Therefore, when the amount of movement of the centroid position of the projection image is corrected as a tolerance error, since the deviation of the SOD direction remains, even if the reconstruction is performed using such a projection image there remains a blur due to the tolerance error in the reconstructed image. Therefore, when correcting the tolerance error, it is necessary to consider which direction and how much the CT rotation axis moves with respect to the rotation driving time.

In the present invention, when the position where the sample is installed is treated as a reference position, it is a feature to represent how much the center position of a CT rotation shaft deviates as the rotation drive axis from the reference position by a function of the rotation driving time (t). By determining the optimal parameters of the assumed functions, the amount of deviation (Δx, Δy, Δz) of the center position of the CT rotation shaft from the reference position at each rotation driving time can be estimated.

When optimizing the parameters of the function, CT measurement is performed with a sphere of uniform density as a reference sample, and the position of the centroid of the absorption coefficient is used in the projection image of the sphere projected on the acquired CT projection image. The sphere of uniform density is preferably a metal sphere, but more preferably a steel sphere. When the amount of deviation with respect to the driving time is reproducible, the amount of deviation with respect to the driving time can be reflected in the tolerance error correction of the experimental measurement by estimating the amount of deviation with respect to the driving time from reliable data. And, the centroid position can simply be calculated, if the contrast of the projection image is clear like a steel ball, and if a sample has isotropic shape.

<FIG> and <FIG> are projected views in the z direction showing the respective coordinate systems before and after the error occurs, respectively. <FIG> and <FIG> show the principles of estimating a deviation quantity in the X-ray CT apparatus. The reference coordinates are set at the position where the sample is placed, and the origin position is (<NUM>, <NUM>, <NUM>). When the coordinates with the center position of the CT rotation shaft as the origin are set, the reference position of the sample coincides with the center position of the CT rotation shaft at the initial time of the rotation drive. The center position of the detector also coincides with the centroid of the projection image on the projection image.

At the time of CT measurement, the center position of the CT rotation shaft (origin of the coordinates) is deviated by (-Δx (t), -Δy (t), -Δz) in the arrangement of the rotation angle (θ (t)) at a certain rotation driving time of the CT rotation axis. At this time, the deviation of the center position of the CT rotation shaft is represented by a vector β(t). Further, when the unit vector in the u direction parallel to the detection plane is represented as the relation (<NUM>), u0 (t) is as shown in the relation (<NUM>). <MAT> <MAT>.

The length v0 (t) in the v direction parallel to the detection plane coincides with the deviation in the z direction of the center position of the CT rotation shaft. These relationships are expressed by the following equations (Helgason-Ludwig condition). <MAT> <MAT>.

The factors of tolerance error differ depending on the assembly and material of the drive axis, etc. Therefore, the function is specified from the tendency of the direction and the amount of deviation. For example, when the deviation direction and the amount are constant in such cases that the member of the drive axis expands or contracts by an environment such as temperature or is affected by the stress applied in one direction, a simple functional form such as a linear function can be used. In the case of an X-ray CT apparatus, since it is expected that a certain amount or the same amount of deviation is repeated in a certain range around the axis of the CT rotation axis for each period of rotation, it is preferable to assume a periodic function.

When deviation Δx (t) and Δy (t) in a certain rotation driving time (t) are the periodic functions of the rotation angle (θ (t)) of a certain rotation driving time, they are expressed by the following equations by the Fourier series expansion. <MAT> <MAT>.

By defining the parameters {ai} and {bj} with respect to the values of Δx and Δy, it is possible to reproduce the variation in the amount of deviation over time in two directions that are perpendicular to each other. In addition, for larger parameters imax and jmax, the functions can contain higher order terms.

The parameters {ai} and {bj} of the function forms assumed above are optimized in order to calculate the Δx and Δy in each rotation driving time. The parameters {ai} and {bj} of the assumed functional form are optional constants, and these parameters are optimized so that the specific position of the X-ray detected image coincides with the specific position computed using the function representing Δx(t) and Δy(t). As an optimization index, an evaluation function representing the degree of coincidence of each specific position is preferably defined.

For example, in estimating the tolerance error of the X-ray CT apparatus, in the rotation driving time (tk) corresponding to the kth projection image, it is preferable to optimize the parameter {ai, bj} so as to satisfy the Helgason-Ludwig condition. Once the parameters are optimized, when the left side of the equation (<NUM>) is defined as the position of the centroid of the absorption coefficient of the CT projection image of the reference sample, the difference from the right side is minimized.

The sum of the residual squares of left-side and right-side for all projections (k) is used as the evaluation function. The evaluation function is expressed by the following equation. The parameters {ai, bj} are determined so as to minimize the evaluation function by the gradient method.

The optimized parameters {ai, bj} are substituted into Δx(t)(formula (<NUM>)) and Δy(t)(formula (<NUM>)) to determine the functions Δx(t), Δy(t), and SODa(t) for calculating Δx, Δy and SODa. Thus, Δx, Δy and SODa are able to be calculated for each rotation driving time t.

Further, the calculated values used for correction are preferable to be stored in a single table as t, θ (t), Δx (t), Δy (t), u0(t), v0 (t), and SODa (t). In this case, the storage is performed for each combination of t and θ(t). Thus, the correction amount to be used can be selected in accordance with the correction method.

By storing them as deviation amounts with respect to the rotation driving time t and the rotation angle θ, for example, the correction can be performed with incorporating the variation of the tolerance error when the scan time is varied. u0(t), v0(t) and SODa (t) are stored together with them.

Thus, since the position of the centroid of the absorption coefficient of the projection image of the reference sample used for the estimation of the deviation amount is stored, the values are possible to be directly referred at the time of correction of the reconstruction. As a result, it is possible for the reconstruction apparatus or the control apparatus to recalculate the position of the centroid of the absorption coefficient of the projection image of the reference sample or to eliminate the need to calculate the corrected SOD, i.e., SODa. In addition, the values are preferable to be stored as the inspection result at the time of the inspection of the device such as the shipping inspection and the maintenance of the device, or the periodic inspection result such as once a month, for example. From the stored data table, Δx and Δy over one rotation during CT measurement may be plotted to output a graph showing the trajectory.

The trajectory represents how much the rotation drive axis has moved in the x and y directions while the rotation drive axis rotates once with reference to the state where the reference position of the sample coincides with the center position of the CT rotation shaft of the sample. From the shape of the trajectory, the state of the X-ray analysis apparatus can be recognized at the time when the data used for the deviation amount calculation is obtained. Since the shape change of the trajectory is stored as device management information, for example, it is possible to determine whether there is deterioration or abnormality of the components related to the rotational drive such as wear of the bearing.

Since the estimated amount of deviation coincides with the amount of movement of the CT rotation axis in the control of the CT rotation axis of the measurement, the amount of deviation can be corrected by performing the movement control so as to cancel the deviation as the correction amount. Since data can be acquired while the amount of deviation being corrected at the time of measurement, correction in data processing is not necessary.

In addition, when the acquired data has an effect of the tolerance error, the data can be corrected by converting the amount of deviation into a correction amount. The coordinates are reset so that the center position of the detector prior to correction is moved by u0(t) and v0 (t). The transformation can be performed by the following formula: <MAT> <MAT>.

Since the deviation amount includes information of the moving direction and the movement amount of the CT rotation axis, it is possible to also calculate the deviation with respect to the SOD direction. SODa, which is the corrected SOD, can be calculated by the following formula.

By correcting the data referring to these values during reconstruction, it is possible to reduce the blur of the reconstructed image which is caused by the deviation with respect to the deviation of the CT rotation axis in the direction parallel to the detector plane (u direction, v direction) and the SOD direction.

<FIG> is a schematic diagram showing a configuration of a whole system <NUM> including an X-ray CT apparatus <NUM>, a processing apparatus <NUM>, an input device <NUM> and a display device <NUM>. Here, the X-ray CT apparatus <NUM> shown in <FIG> is configured to rotate the gantry in which the X-ray source <NUM> and the detector <NUM> are integrated with respect to the sample, however, the X-ray CT apparatus <NUM> is not limited thereto, and may be configured to rotate the sample.

The processing apparatus <NUM> (tolerance error estimating apparatus) is connected to the X-ray CT apparatus <NUM> to perform controlling the X-ray CT apparatus <NUM> and processing the acquired data. The processing apparatus <NUM> may be a PC terminal or a server on a cloud. The processing apparatus <NUM> estimates the tolerance error of the CT rotation axis in the X-ray CT data. The input device <NUM> is, for example, a keyboard or a mouse, and performs input to the processing apparatus <NUM>. The display device <NUM> is, for example, a display, and is used for showing a result of processing by the processing apparatus <NUM> to a user by screen display or the like.

As shown in <FIG>, the X-ray CT apparatus <NUM> includes a rotation controlling unit <NUM>, a sample position controlling unit <NUM>, a sample stage <NUM>, an X-ray source <NUM>, and a detector <NUM>. The X-ray source <NUM> and the detector <NUM> are installed on a gantry (not shown), and X-ray CT measurement is performed by rotating the gantry with respect to a sample fixed to the sample stage <NUM>. In addition, the sample stage <NUM> installed between the X-ray source <NUM> and the detector <NUM> may be rotated.

The X-ray CT apparatus <NUM> rotates the gantry at a timing instructed by the processing apparatus <NUM> and acquires a projection image of the sample. The measurement data is transmitted to the processing apparatus <NUM>. The X-ray CT apparatus <NUM> is suitable for use on precision industrial products such as semiconductor devices, however, can be applied to a device for animals as well as industrial products.

The X-ray source <NUM> emits X-rays toward the detector <NUM>. The detector <NUM> is a two-dimensional detector having a receiving surface for receiving X-rays and possible to measure the intensity distribution of X-rays transmitted through the sample by a number of pixels. The X-ray CT projection image is preferably acquired with a two-dimensional detector having detection elements with <NUM> or less width, e.g. pixels of <NUM>×<NUM> or less. For example, when the enlargement ratio is <NUM> times, the size of one pixel is <NUM>. When an image blur of micron order is caused by the tolerance error, the present invention is effective for an X-ray CT apparatus for industrial products in which analysis is carried out with accuracy of micron order especially, because the error occurs in recognizing the shape and measuring the dimension.

The rotation controlling unit <NUM> rotates the gantry at a speed set at the time of CT measurement. The sample position controlling unit <NUM> controls a sample position by adjusting a position of the sample stage <NUM> during the CT measurement. The sample position controlling unit <NUM> can adjust the sample position in accordance with Δx, Δy, and Δz at each rotational position according to an instruction from the processing apparatus <NUM>.

<FIG> is a block diagram showing a configuration of the processing apparatus <NUM> (a tolerance error estimating apparatus, a reconstruction apparatus, and a control apparatus). The processing apparatus <NUM> is configured by a computer formed by connecting a CPU (Central processing section), a ROM (Read Only Memory), a RAM (Random Access Memory) and a memory to a bus. The processing apparatus <NUM> is connected to the X-ray CT apparatus <NUM> and receives information. In the example shown in <FIG>, the processing apparatus <NUM> functions as each of a tolerance estimation apparatus, a reconstruction apparatus and a control apparatus. However, an independent processing apparatus may be used as each functional apparatus. In any case, the devices are connected to each other so that information can be transmitted and received.

The processing apparatus <NUM> includes a measurement data storing section <NUM>, an apparatus information storing section <NUM>, a specific position calculating section <NUM>, a deviation amount calculating section <NUM>, a display processing section <NUM>, a correction amount calculating section <NUM>, a table storing section <NUM>, and a designation receiving section <NUM>. Each section can transmit and receive information via a control bus L. The input device <NUM> and the display device <NUM> are connected to the CPU via an appropriate interface.

The measurement data storing section <NUM> stores measurement data acquired from the X-ray CT apparatus <NUM>. The measurement data includes a rotation driving time (including information corresponding to a rotation driving time such as rotation angle information) and a projection image corresponding thereto. The apparatus information storing section <NUM> stores apparatus information acquired from the X-ray CT apparatus <NUM>. The apparatus information includes geometry at the time of measurement, etc..

The specific position calculating section <NUM> obtains the centroid of the absorption coefficient from the X-ray CT projection image of the sphere of uniform density at each rotation driving time. Thus, it is possible to recognize the transition of the center of the sphere with respect to the passing of the rotation driving time in the projection image. The center of the sphere on the projection image represents the projections of the deviation of the center of the CT rotation axis from the reference position of the original sample. However, since Δx and Δy are not known directly from the projections of the deviation, they are necessary to be estimated.

The deviation amount calculating section <NUM>, based on the centroid position of the u direction, calculates the deviation Δx in the x direction and Δy in the y direction of the center position of the CT rotation shaft from the reference position of the sample at each rotation driving time when a direction parallel to the CT rotation axis is the z direction of the orthogonal coordinate system fixed to the sample. Thus, by calculating the deviation of the center position of the CT rotation shaft from the reference position of the sample using the projection image without performing reconstruction, it is possible to obtain high-quality data at low cost and at high speed. Details of the calculation of Δx and Δy are described below.

Specifically, it is preferable to assume respective functional forms of Δx and Δy with respect to each rotation driving time, to determine the functions Δx(t) used for calculating Δx and Δy(t) used for calculating Δy by optimizing the parameters of the assumed functions, and to calculate Δx and Δy at each rotation driving time using the determined Δx(t) and Δy(t). Thus, the amount of deviation caused by the tolerance error can be estimated, and the value that can be used for correction can be calculated. The parameters included in the assumed functional forms are preferably optimized so as to minimize the evaluation function representing the degree of coincidence between the specific position of the X-ray detection image and the specific position calculated using Δx and Δy. Thus, it is possible to estimate Δx and Δy varied by the rotation driving time with high accuracy.

Δx and Δy return to the same value in one cycle of the CT rotation. Using the fact, it is preferable to calculate Δx and Δy by assuming a periodic function having a period of the CT rotation. Thus, Δx and Δy can be easily estimated by assuming the periodic function. The deviation amount calculating section <NUM> further calculates Δz from the transition of the centroid position in the v direction with respect to the rotation driving time on the projection image.

The display processing section <NUM> displays Δx and Δy over one rotation calculated by the deviation amount calculating section <NUM> as a trajectory of tolerance error on the display device <NUM>. As a result, the user can recognize the state of the X-ray analysis apparatus at the time of acquiring the data used for the deviation amount calculation from the shape of the displayed trajectory.

The correction amount calculating section <NUM> calculates a value necessary for correction using the calculated deviation amounts Δx and Δy. For correction, it is preferable to use a stored table.

The table storing section <NUM> stores, as a table, the values calculated by the specific position calculating section <NUM>, the deviation amount calculating section <NUM>, and the correction amount calculating section <NUM>. In the table, the specific position, the amount of deviation, and the correction value of the X-ray image are specified for each combination of the rotation driving time and the rotation angle corresponding thereto.

The designation receiving section <NUM> receives a screen for designating a means for applying the deviation amounts in the x and y directions. The processing apparatus <NUM> starts the reconstruction function or the control function according to the received designation. Thus, the user can choose whether to correct the tolerance error on software or hardware.

The reconstruction apparatus <NUM> includes a reconstruction section <NUM>. The reconstruction apparatus <NUM> causes the reconstruction section <NUM> to reconstruct a three-dimensional image based on the corrected X-ray CT projection images of the sample. Thus, it is possible to generate a reconstructed image which does not require particularly adjustment of the optical system, etc., and which is corrected using the projection image including the tolerance error. The reconstruction section <NUM> reconstructs a three-dimensional image based on the X-ray CT projection images.

The control apparatus <NUM> includes a correction controlling section <NUM>, and the correction controlling section <NUM> controls the position of the sample for the correction at the time of CT test using the calculated Δx, Δy, and Δz. For correction, it is preferable to use the stored table. Thus, since it is possible to get the projection images while adjusting the relative position of the sample at the time of measurement, it is possible to generate a highly accurate reconstructed image without correction using the obtained projection images.

A tolerance error estimating method using the whole system <NUM> configured as described above is described. <FIG> is a flowchart showing a tolerance error estimating method. First, in step S1, a CT projection image is acquired using a steel ball as a reference sample which is a sphere of uniform density. Next, the centroid position u0(t) and v0 (t) of the absorptivity are calculated from the acquired CT projection image (step S2).

Next, a functional form of the deviation Δx and Δy at the rotation driving time is assumed (step S3). Since the factors of the tolerance error differ depending on the state of the components constituting the device, it is preferable to be able to select a functional form capable of reproducing the transition in the amount of deviation with respect to each rotation driving time. For example, a screen in which a user can select a function form such as a primary function or a periodic function may be displayed.

Next, an evaluation function is set for the parameter to be optimized (step S4). The evaluation function is set based on information on the specific position of the X-ray detection image, the specific position calculated using Δx and Δy, and the number of projections. The parameters are optimized by the gradient method (step S5). At the time, a graph plotting the specific position of the X-ray detection image and the specific position calculated using Δx and Δy with respect to the rotation angle at each rotation driving time or each rotation driving time may be output. Thus, the probability of the optimized parameters can be visually confirmed.

Next, functions Δx(t) and Δy(t) are determined using the optimized parameters (step S6). The deviation amounts (Δx, Δy) are calculated using the determined function (step S7). The corrected values (SODa) are calculated from the calculated deviation amounts (step S8). Then, the specific position of the calculated X-ray image, the deviation amount and the correction values are stored as a table (step S9). Thus, it is possible to estimate the tolerance error.

A reconstructed image can be generated by correcting the tolerance error estimated as described above. The correcting method includes two methods: a method using software and a method controlling an X-ray CT apparatus during measurement. It is preferable that the processing apparatus <NUM> displays a screen on which the user can select which means is used to perform the correction and whether the correction is applied or not, and the like.

When software is used, a desired sample is first CT measured. The obtained projection images are corrected using the tables of Δx, Δy and Δz. Specifically, the center shift and the SOD are corrected. The three-dimensional image is reconstructed using the corrected projection images. Thus, a reconstructed image whose tolerance error is easily corrected only by processing is obtained.

When the X-ray CT apparatus is controlled at the time of measurement, CT measurement is performed while controlling the sample position for the correction using the tables of Δx, Δy, and Δz at the time of CT measurement of a desired sample. In the projection image thus obtained, a tolerance error has been corrected. The three-dimensional image is reconstructed using the obtained projection image. Thus, a highly accurate reconstructed image with reduced error from the device can be obtained.

In this way, it is preferable that the estimated Δx, Δy and Δz be held as a table. <FIG> is a diagram showing an image of a table.

As shown in <FIG>, the rotation angle (θ1, θ2, θ3,. ), the centroid position of the absorption coefficient in the u direction (u01, u02, u03,. ), the centroid position of the absorption coefficient in the v direction (v01(Δz1), v02(Δz2), v03(Δz3),. ), the deviation amount in the X direction (Δx1, Δx2, Δx3,. ), the deviation amount in the Y direction (Δy1, Δy2, Δy3,. ), and the corrected SOD (SODa1, SODa2, SODa3,. ) are stored with respect to each driving time (t1, t2, t3,. ) in each constant step. As each rotation driving time for each constant step, for example, each rotation driving time for acquiring the projection image may be used.

Although the above embodiment is directed to the estimation and correction of tolerance error of an X-ray CT apparatus, the present invention can be applied to other X-ray analysis apparatuses. An X-ray diffractometer includes a rotation drive axis for rotating the detector about a reference position for placing the sample. Then, when a tolerance error occurs in the rotation drive axis, it may affect the data to be acquired. For example, if the camera length (sample-to-detector distance) changes due to a tolerance error, the capture angle changes. Even if the same diffraction beam is acquired, since the position where it is detected on the detector plane is changed, angular error occurs.

In the X-ray diffractometer, when a diffraction image is acquired using a reference sample as a powder sample having a known diffraction position, a Debye center (specific position) can be calculated from the observed Debye ring. The deviation amount can be calculated by applying the present invention as the Debye center (u O, v O), it is possible to correct the control or the data of the rotation drive.

A steel ball was subjected to CT measurement using an X-ray CT apparatus of gantry rotation type for testing. The centroid position was calculated from the obtained projection image of the steel ball and Δx and Δy were calculated from the centroid position of the u direction in the experimental measurement. The calculation of Δx and Δy was optimized using the Helgason-Ludwig condition. <FIG> is a graph showing the centroid position of the projection image of the steel ball in the u direction with respect to the rotation angle. As shown in <FIG>, it is confirmed that the measured values coincide with the calculated values for the centroid position in the u direction when the parameters {ai} and {bj} are optimized.

<FIG> is a graph showing Δx, Δy and the calculated centroid position (center shift) in the u-direction with respect to the rotation angle. <FIG> is a graph showing the trajectory of Δx and Δy over one rotation. The deviation amounts of Δx and Δy of the gantry rotation type X-ray CT apparatus for the test were confirmed. <FIG> is a graph showing a deviation Δz in the v direction with respect to the rotation angle. By plotting v0 calculated from the CT projection images, the deviation of Δz was confirmed.

SODa (t) was calculated using Δx and Δy obtained as described above. <FIG> is a graph showing the variation rate of SODa(t) with respect to the rotation angle. Thus, the correction amounts used for the correction of the reconstructed image were confirmed.

The difference between reconstructed images with and without correction was confirmed. First, the reconstructed image was generated using the projection images without correction for the steel balls used for the calculation of Δx, Δy, and Δz. Next, a reconstructed image was generated using the projection images corrected using the calculated Δx, Δy, and Δz. <FIG> are reconstructed images of steel balls with and without correction, respectively. It is confirmed that the steel ball is displayed in spherical shapes in <FIG>, whereas the steel ball is not displayed in spherical shapes due to blurring in <FIG>.

Claim 1:
A tolerance error estimating apparatus (<NUM>) for estimating a tolerance error of a rotation drive axis of an X-ray analysis apparatus, the tolerance error being the deviation of the rotation drive axis with respect to the centroid of a sample, the X-ray analysis apparatus rotating an X-ray source (<NUM>) and a detector (<NUM>) or the sample around the rotation drive axis to acquire an X-ray detection image as a projection image of the sample at each driving time of a rotation, comprising:
a specific position calculating section (<NUM>) configured to obtain the centroid position of the absorption coefficient in the X-ray detection image as a specific position of a reference sample at each driving time of a rotation from the X-ray detection images acquired by setting the reference sample formed as a sphere of uniform density at a reference position so that the centroid of the reference sample initially coincides with the center of a rotation drive shaft, and
a deviation amount calculating section (<NUM>) configured to calculate a deviation amount Δx in the x direction and Δy in the y direction of the center position of the rotation drive shaft as the rotation drive axis at each driving time of a rotation from the reference position based on the specific position, when the z direction of an orthogonal coordinate system fixed to a sample is set to the direction parallel to the rotation drive axis, wherein the driving time of a rotation is represented by a parameter t of the rotation angle θ(t).