Radiographic image generating device

Abstract

A device that uses a grating to carry out high sensitivity radiographic image shooting using the wave nature of x-rays or the like can shoot a sample that moves relative to a device. A pixel value computation section determines, using a plurality of intensity distribution images of a sample that moves in a direction that traverses the path of radiation, whether or not a point (p, q) on the sample belongs in a region (Ak) on each intensity distribution image. Further, the pixel value computation section obtains a sum pixel value (Jk) for each region (Ak) by summing pixel values on the each intensity distribution image for point (p, q) that belongs to each region (Ak). An image computation section creates a required radiographic image using the sum pixel values (Jk) of the region (Ak).

Claims

1. A radiographic image generating device, for generating an radiographic image for a sample, using an intensity distribution image for radiation that has passed through the sample and a grating group that have been arranged on a path from a source section to a detection section, comprising: a pixel value computation section; and an image computation section, wherein the pixel value computation section determines, using a plurality of intensity distribution images for the sample that is moved in a direction that traverses the path, whether or not point (p, q) on the sample falls in a region (Ak) on each intensity distribution image, and obtains a sum pixel value (Jk) for each region (Ak) by summing up pixel values, on each intensity distribution image, of the point (p, q) that falls in each region (Ak), and wherein the image computation section creates a necessary radiographic image using the sum pixel values (Jk) of the regions (Ak).

2. The radiographic image generating device of claim 1, further comprising a region specifying section, wherein; the region specifying section comprises an initial image computation section, an initial image determination section, and a range computation section, the initial image computation section, in a state where there is no sample, computes at least a differential phase image (.sub.0) using a plurality of intensity distribution images that have been acquired while at least partially changing a positional relationship between the radiation source section, the grating group, and the detection section, the initial image determination section determines whether or not pixel values of the differential phase image are distributed continuously in a value region of to +, in the movement direction of the sample, and the range computation section determines the region (Ak) such that the pixel values of the differential phase image constitute a set of pixels in a specified range.

3. The radiographic image generating device of claim 2, wherein the region specifying section further comprises a pixel number computation section, and wherein the pixel number computation section respectively computes a number of pixels that fall on a locus of the point (p, q), in each region (Ak).

4. The radiographic image generating device of claim 1, used in medical applications.

5. The radiographic image generating device of claim 1, used in examination applications for foodstuff, industrial parts and industrial products.

6. A radioscopic inspection apparatus comprising the radiographic image generating device of claim 1, including the radiation source section, the grating group, and a detection section, wherein the detection section acquires an intensity distribution image for radiation that has passed through a sample and the grating group that have been arranged on a path from the radiation source section to the detection section.

7. The radioscopic inspection apparatus of claim 6, used in medical applications.

8. The radioscopic inspection apparatus of claim 6, used in examination applications for foodstuff, industrial parts and industrial products.

9. A radiographic image generating method, for generating a radiographic image for a sample, using an intensity distribution image for radiation that has passed through the sample and a grating group that have been arranged on a path from a radiation source section to a detection section, comprising: determining, using a plurality of intensity distribution images for the sample that is moved in a direction that traverses the path, whether or not point (p, q) on the sample falls in a region (Ak) on each intensity distribution image, obtaining a sum pixel value (Jk) for each region (Ak) by summing up pixel values, on each intensity distribution image, of the point (p, q) that falls in each region (Ak), and creating a necessary radiographic image using the sum pixel values (Jk) of the regions (Ak).

10. The radiographic image generating method of claim 9, used in medical applications.

11. The radiographic image generating method of claim 9, used in examination applications for foodstuff, industrial parts and industrial products.

12. A non-transitory computer-readable medium having a computer program stored thereon, wherein execution of the computer program by a computer causes the computer to: determine, using a plurality of intensity distribution images for the sample that is moved in a direction that traverses the path, whether or not point (p, q) on the sample falls in a region (Ak) on each intensity distribution image, obtain a sum pixel value (Jk) for each region (Ak) by summing up pixel values, on each intensity distribution image, of the point (p, q) that falls in each region (Ak), and create a necessary radiographic image using the sum pixel values (Jk) of the regions (Ak).

Description

BRIEF DESCRIPTION OF THE SEVERAL VIEWS OF THE DRAWINGS

(1) FIG. 1 is an explanatory drawing showing the schematic structure of a radioscopic inspection apparatus that uses the radiographic image generating device of one embodiment of the present disclosure.

(2) FIG. 2 is a block diagram for explaining an image generating section used in the device of FIG. 1.

(3) FIG. 3 is a block diagram for explaining a region specifying section used in the device of FIG. 1.

(4) FIG. 4 is a flowchart showing an outline of an image generating method using the device of FIG. 1.

(5) FIG. 5 is one example of a moir fringe image attributable to grating distortion. FIG. 5(a) to FIG. 5(e) show moir fringe images that change in accordance with position of a grating in the fringe scanning method.

(6) FIG. 6 is an image showing one example of a differential phase image calculated from the images of FIG. 5.

(7) FIG. 7 is an image showing one example of region division calculated from the differential phase image of FIG. 7.

(8) FIG. 8 is a flowchart showing an outline of an image generating method using the device of FIG. 1.

(9) FIG. 9 is images that has been taken in accordance with movement of a sample. FIG. 9(a) to FIG. 9(i) show moving images that have been taken in accordance with movement of a sample.

(10) FIG. 10 shows images that have been generated using sum pixel values generated from the moving images of FIG. 9.

(11) FIG. 11 shows an absorption image that has been generated from FIG. 10.

(12) FIG. 12 shows a refractive image that has been generated from FIG. 10.

(13) FIG. 13 shows a scattering image that has been generated from FIG. 10.

(14) FIG. 14 is an explanatory drawing for describing a sample used in specific practical examples.

(15) FIG. 15 shows radiographic images that have been acquired in a modified example, with FIG. 15a showing an absorption image, FIG. 15b showing a refractive image, and FIG. 15c showing a scattering image.

(16) FIG. 16 shows radiographic images that have been acquired in a modified example, after correction, with FIG. 16a showing an absorption image, FIG. 16b showing a refractive image, and FIG. 16c showing a scattering image.

DETAILED DESCRIPTION

(17) In the following, an example of a radioscopic inspection apparatus that uses the radiographic image generating device of the present disclosure will be described.

(18) (Radioscopic Inspection Apparatus of this Embodiment)

(19) In the following, the structure of a radioscopic inspection apparatus of this embodiment will be described with reference to the drawings. This radioscopic inspection apparatus targets either an organism or object other than an organism as a sample 10. Also, this device can be used in medical applications or non-medical applications. As an application in non-medical fields, it is possible to exemplify the examination of foodstuffs, industrial parts, or industrial products, but these are not limiting.

(20) (Overall Structure of Radioscopic Inspection Apparatus)

(21) The radioscopic inspection apparatus of this embodiment (refer to FIG. 1) comprises a radiation source section 1, a grating group 2, a detection section 3, a conveyor section 4, and an image generating section 5. Further, this device is additional provided with a control section 6 and an output section 7.

(22) (Radiation Source Section)

(23) The radiation source section 1 is configured to radiate radiation that has transmissivity with respect to the sample 10, towards the grating group 2. Specifically, with this embodiment, an X-ray source that generates X-rays is used as the radiation source 1. As the radiation source 1, it is possible to use, for example, an X-ray source that generates X-rays (namely, radiation) as a result of irradiation of an electron beam to a target. Specific structure of the radiation source 1 can be made the same as an already known X-ray source, and so more detailed description in this regard is omitted.

(24) (Grating Group)

(25) The grating group 2 is provided with a plurality of gratings that are capable of transmitting radiation that has been irradiated towards this grating group 2. The grating group 2 satisfies conditions for mechanical structure and geometric configuration necessary to construct a Talbot interferometer (including the cases of a Talbot-Lau interferometer and a Lau interferometer). However, for this embodiment, conditions for constructing a Talbot interferometer are not required to satisfy conditions in the strict mathematical sense of the word, as long as they are met an extent to sufficient to make required examination possible.

(26) Specifically, the grating group 2 of this embodiment is constituted by three gratings, namely grating G0, grating G1, and grating G2. Grating G0 is a grating for constituting a Talbot-Lau interferometer, which is one type of Talbot interferometer, and uses an absorption type grating. A micro-light source array (i.e., a Talbot interferometer if considered as a single light source), which is a structural element of a Talbot-Lau interferometer, is realized by the grating G0. As grating G1, a phase type grating is normally used, but it is also possible to use an absorption type grating. An absorption type grating is used as grating G2. It should be noted that a structure from which arrangement of G2 is omitted is also possible (Lau interferometer). Refer to patent laid open number 2012-16370.

(27) With the grating group 2 of this example, there is some distortion in either of the gratings. The distortion here is what is known as offset or dispersion of the grating from an ideal state, such as some kind Moir fringe (refer to FIG. 5 which will be described later) attributable to distortion arising. This type of distortion is not specially intended and occurs naturally with normal manufacturing methods. It is obviously possible to manufacture a grating so as to intentionally impart distortion.

(28) In points other than described above, the structures of the gratings G0-G2 can be the same as for a conventional Talbot interferometer (including the cases for a Talbot-Lau interferometer and a Lau interferometer), and so more detailed description will be omitted.

(29) (Detection Section)

(30) The detection section 3 of this embodiment is configured to be able to acquire an intensity distribution image of radiation that has passed through the sample 10 and the grating group 2, both of which have been arranged on a path from the radiation source section 1 to the detection section 3.

(31) In more detail, the detection section 3 has a structure where pixels are arranged in a two dimensional array (i.e., horizontally and vertically), and is configured to detect radiation that reaches the pixels through the plurality of gratings G0-G2, for every pixel.

(32) (Conveyor Section)

(33) The conveyor section 4 is configured to move the sample 10 in a direction that traverses the radiation direction of the radiation (right direction within the drawing in the example of FIG. 1), with respect to the grating group 2. Specifically, the conveyor section 4 of this embodiment is constructed using a belt conveyor that moves the sample 10 in a lateral direction. Also, with this embodiment, the conveyor section 4 conveys the sample 10 so that the sample can pass through a portion of radiation passing through a space between the grating G0 and the grating G1. It should be noted that the conveyor section 4 may cause the sample 10 to pass between the grating G1 and the grating G2. It should be noted that when constructing a Lau interferometer (refer to Japanese patent laid open No. 2012-16370), the sample 10 is made to pass between the grating G1 and the detection section 3.

(34) As a belt used in a belt conveyor, as the conveyor section 4, it is preferable to select one having high transmissivity for the radiation that is used. It should be noted that the conveyor section 4 is not limited to being a belt conveyor, and can have an appropriate structure as long as it can convey the sample 10 in a desired direction. It is also possible to have a configuration in which the sample 10 is fixed, and all of the radiation source, grating group and detection section are made to move relative to the sample 10 (including polar coordinate system movement).

(35) (Image Generating Section)

(36) The image generating section 5 (refer to FIG. 2) is provided with a pixel value computation section 51 and an image computation section 52. Further, the image generating section 5 of this embodiment is additionally provided with a region specifying section 53.

(37) The pixel value computation section 51, using a plurality of intensity distribution images for the sample 10 that is moved in a direction that traverses an x-ray path from the radiation source section 1 to the detection section 3 (the right direction in the drawing, in the example of FIG. 1), determines whether or not a coordinate point (p, q) (described later) fixed on the sample 10 belongs in a region Ak (described later) on each intensity distribution image. Further, the pixel value computation section 51 obtains a sum pixel value Jk for point (p, q) corresponding to each region Ak, by summing pixel values on each intensity distribution image when point (p, q) is in each region Ak.

(38) The image computation section 52 is configured to create a necessary radiographic image using the sum pixel values (Jk) corresponding to the regions (Ak).

(39) The region specifying section 53 (refer to FIG. 3) is provided with an initial image computation section 531, an initial image determination section 532, a range computation section 533, and a pixel number computation section 534.

(40) The initial image computation section 531 is configured to compute at least a wrapped differential phase image (.sub.0), using a plurality of intensity distribution images that have been acquired while at least partially changing a positional relationship between the radiation source section 1, the grating group 2 and the detection section 3 in a state where there is no sample 10. A wrapped differential phase image is an image in which a range resulting from arc tangent computation becomes from to +. Specifically, for example, a pixel value that has an original value of 1.5 is expressed as 0.5.

(41) The initial image determination section 532 is configured to determine whether or not pixel values of a wrapped differential phase image are distributed continuously in a range of from to , in the movement direction of the sample 10.

(42) The range computation section 533 is configured to determine regions (Ak) that are sets of pixels having pixel values of a wrapped differential phase image that are within a specified range.

(43) The pixel number computation section 534 is configured to compute a number of pixels belonging to each region (Ak).

(44) More detailed structure of the image generating section 5 will be additionally described as description of an operation method.

(45) (Control Section)

(46) The control section 6 is configured to send drive signals to the conveyor section 4, and send information on the movement velocity of the sample 10 (command value or detection value) to the image generating section 5.

(47) (Output Section)

(48) The output section 7 is configured to be able to output images that have been generated by the image generating section 5. As the output section 7, it is possible to use a display that can present images to the user, memory means that can temporarily or permanently store images, or another appropriate device. The output section 7 may also be configured to transmit image data to another device via a network.

(49) (Operation of the Radioscopic Inspection Apparatus of this Embodiment)

(50) An image generating method that uses the radioscopic inspection apparatus of this embodiment will be described in the following. This method is roughly divided into region specifying stage (FIG. 4) and image generating stage (FIG. 8). Description will first be given of the region specifying stage of FIG. 4.

(51) (Region Specifying Stage)

(52) (Step SA-1 of FIG. 4)

(53) First, the conveyor section 4 is stopped and a state where the sample 10 is not used is entered (no-sample state). In this state, a conventional fringe scanning method is carried out. Specifically, if a grating period is made T, shooting using X-rays is carried out while moving the grating sequentially by a distance Tx1/M (M is a natural number of 3 or greater), and a plurality of intensity distribution images are acquired by the detection section 3. This image corresponds to one example of a plurality of intensity distribution images that have been acquired while at least partially changing a positional relationship between the radiation source section 1, the grating group 2 and the detection section 3. Examples of intensity distribution images that have been acquired in this way are shown in FIG. 5(a) to FIG. 5(e). With this example, M=5. Also, with the example of FIG. 5, a moir fringe resulting from grating distortion is generated.

(54) (Step SA-2 of FIG. 4)

(55) Next, the initial image computation section 531 of the region specifying section 53 computes at least a wrapped differential phase image .sub.0 (x, y), as an initial image, using the plurality of intensity distribution images that have been acquired (refer to FIG. 6). Here, (x, y) represents coordinates in the field of view of the detection section 3 or in an image acquisition range. The initial image computation section 531 of this example further computes an absorption image A.sub.0 (x, y) and a visibility image V.sub.0 (x, y).

(56) (Step SA-3 of FIG. 4)

(57) Next, the initial image determination section 532 of the region specifying section 53 determines, for each y of coordinates (x, y), whether or not values of a wrapped differential phase image .sub.0 (x, y) are continuously distributed in a range of ( to +) in the movement direction of the sample 10 (with the example of FIG. 1, in the right direction in the drawing). Specifically, it is determined whether or not there is continuous phase change spanning to +. Since a sample 10 is not actually used at this stage, the movement direction means a direction in which the sample 10 should be moved.

(58) If the determination in this step is No, processing advances to the step SA-4, which will be described later, while if the determination is Yes processing advances to step SA-5, which will be described later.

(59) (Step SA-4 in FIG. 4)

(60) In the event that, for each y of coordinates (x, y), values of a wrapped differential phase image .sub.0 (x, y) are not continuously distributed in a range of to +, in the movement direction of the sample 10, grating alignment is carried out. Alignment of the grating means changing some relative arrangement conditions of the grating, including, for example, grating inclination, distance between gratings, grating curvature, etc. The alignment operation itself can be carried out manually by an operator, and can be carried out automatically using some sort of automated means. After that, previously described step SA-1 is returned to, and the subsequent steps are repeated.

(61) (Step SA-5 in FIG. 4)

(62) If the determination in step SA-4 was YES, then the range computation section 533 determines a range (Ak) based on values of the wrapped differential phase image .sub.0 (x, y).

(63) More specifically, if a field of view region is divided into n (where n is an integer of 3 or more), regions Ak can be defined from the following rules. It should be noted that k=1, 2, . . . , n.
A.sub.k(x,y), if +2(k1)/n<.sub.0(x,y)<+2k/n

(64) An example of regions that have been divided in this way is shown in FIG. 7. With this example, n=6. With this example, one region Ak means a portion where each of the divided regions have been interleaved. Also, the whole of the field of view region is covered by regions Ak, without overlapping.

(65) As a result of the above processing, it is possible to specify regions Ak that the intensity distribution image should be divided into.

(66) (Step SA-6 of FIG. 4)

(67) Next, the pixel number computation section 534 is configured to respectively compute, for each region (Ak), a number of pixels that belong to a locus of point (p, q) of coordinates that lie on the sample 10 (that is, a locus that intersects each region accompanying movement of the sample). The locus of point (p, q) can be a locus at the time that any point on the sample intersects the field of view, and with the example of FIG. 7 it is possible to recognize a straight line from top to bottom, for example.

(68) More specifically, the pixel number computation section 534 of this example creates, for each y, group g(y) for a number of pixels that belong in a region Ak, counted along the x axis direction, where
g(y)=(N.sub.1(y),N.sub.2(y), . . . ,N.sub.n(y)).

(69) (Actual Image Generating Stage)

(70) Next, the image generating stage shown in FIG. 8 will be described.

(71) (Step SB-1 in FIG. 8)

(72) First, a sample 10 that moves so as to intersect the field of view of the detection section 3 is photographed. Specifically, the detection section 3 acquires a plurality of intensity distribution images for the sample 10 that moves in a direction that intersects a path from the radiation source section 1 to the detection section 3. An example of the plurality of intensity distribution images that have been acquired in this way is shown in FIG. 9(a) to 9(i). x in the drawing shows movement direction of the sample 10. FIG. 9(a) to 9(i) shows appearance when the sample 10 is moving in the x direction within the field of view of the detection section 3.

(73) It should be noted that actual photographing interval (sampling period) is shorter, and FIG. 9 shows images that have been extracted from a moir moving image every 100 frames. Also, the intensity distribution images may be identified using I(x, y, t) in the above description. Here, x, y is a coordinate within the field of view, and t is acquisition time of the frame in question. Accordingly it is possible to express a moving image using change in t, within I(x, y, t).

(74) This makes it possible to show fixed coordinates on the sample as shown below.
p=x+vt,
q=y

(75) v here is speed of the sample 10 in the x axis direction.

(76) (Step SB-2 in FIG. 8)

(77) Next, the pixel value computation section 51 can obtain sum pixel value (Jk), for a plurality of intensity distribution images of the sample 10 that moves in a direction that traverses a path from the radiation source section 1 to the detection section 3 (refer to FIG. 9), by summing pixel values for the case where point (p, q) on the sample 10 belongs to region (Ak).

(78) This processing can specifically be executed as follows. That is, when a point (p, q) is in a particular region AK, I(pvt, y, t)/Nk(y) is added to stack Jk(p, q). This is carried out for all moving image frames (that is, frames corresponding to each t). Here, dividing by Nk(y) is in order to normalize (namely, average) values of pixel values I in accordance with number of pixels. Accordingly, the sum pixel value Jk in this embodiment has been normalized using number of pixels Nk.

(79) More specifically, the procedure can be described as shown below.
when (p,q)Ak,Jk(p,q)+=I(pvt,y,t)/Nk(y)

(80) An example of images corresponding to this stack Jk (namely images resulting from adding all frames) is shown in FIG. 10. With this example, in J.sub.k(p,q)(k=1, 2, . . . , n) described below, n=20.

(81) (Step SB-3 in FIG. 8)

(82) The image computation section 52 creates a necessary radiographic image using the sum pixel values (Jk).

(83) More specifically, with this embodiment, using J.sub.k (p,q)(k=1, 2, . . . , n) that has been acquired, an absorption image A.sub.bs, a refraction image , and a scattering image V.sub.is can be respectively computed as:

(84) $A_{\mathrm{bs}}\left(p,q\right)=\underset{k=1}{\overset{n}{.Math.}}{J}_k\left(p,q\right)$$\left(p,q\right)=\arg \left[\underset{k=1}{\overset{n}{.Math.}}{J}_k\left(p,q\right)\exp \left(i2\frac{k}{n}\right)\right]$$V_{\mathrm{is}}\left(p,q\right)=\frac{2.Math.\underset{k=1}{\overset{n}{.Math.}}{J}_k\left(p,q\right)\exp \left(i2\frac{k}{n}\right).Math.}{A_{\mathrm{bs}}\left(p,q\right)}$

(85) Examples of the acquired images are shown in FIG. 11 to FIG. 13. It should be noted that these are only one example of radiographic images generated as required, and it is not necessary to generate all of these. Generating other types of images is also possible.

(86) According to this embodiment, at the image creation stage it is possible to create a required radiographic image without using a fringe scanning method (method of moving a grating intermittently) as with the prior art. As a result, with this embodiment it is possible to generate a radiographic image at high speed, even in a case where the sample and the device move relatively (normally the sample side moves), and it is possible to make relative movement velocity between the sample and the device faster.

(87) Also, according to this embodiment, since it is possible to generate a radiographic image of good precision even if a grating shape and arrangement conditions are not perfect, it is possible to keep device manufacturing cost and maintenance costs low.

Modified Example

(88) An image generating device of a modified example will be described in the following.

(89) With the previously described embodiment, when a point (p, q) is in a particular region Ak, Jk is generated by adding I(pvt, y, t)/Nk(y) to stack Jk(p, q). Here, if it can not be assumed that X-ray intensity and image sharpness are even, an error can arise within an image.

(90) With this modified example, therefore, in computation of J.sub.k a coefficient for reducing the effect of this error is introduced. Specifically, for coordinate (p, q) fixed on the sample (here, p=x+vt, q=y), by computing
when (p,q)Ak,Jk(p,q)+=I(pvt,y,t)/Nk(y)/A.sub.0(pvt,y)

(91) for all I(x,y,t) it is possible to acquire Jk. That is, with this modified example intensity correction is intended as a result of dividing I by coefficient A.sub.0 (pvt,y). It should be noted that this coefficient A.sub.0 is the same as the previously described absorption image data, and so the same reference numeral is used.

(92) Other structure and operation of the modified example are the same as the previously described embodiment, and so more detailed description is omitted.

Practical Example

(93) A practical example that uses the procedure of the previously described embodiment will be described based on FIG. 14 to FIG. 16.

(94) With this practical example, the sample 10 shown in FIG. 14 is used. This sample 10 has a polyethylene sphere 101 containing an air portion inside (shown by the small circle in the drawing), a polypropylene sphere 102 containing an air portion inside, a PMMA sphere 103, and a POM sphere 104 containing an air portion inside. These spheres 101 to 104 all have the same diameter (7.9 mm), and are arranged in a one-dimensional direction (the lateral direction in FIG. 14).

(95) First, radiographic images that have been acquired with the method of this embodiment are shown in FIG. 15A to FIG. 15c. As will be understood from these images, while it is possible to acquire a radiographic image with high precision, unnecessary contrast is observed. It should be noted that the scanning direction of the sample in this practical example is the horizontal direction in the drawing.

(96) Next, radiographic images that have been acquired with the method of the modified example are shown in FIG. 16a to FIG. 16c. As will be understood from these images it is possible to acquire radiographic images in which errors have been reduced.

(97) It should be noted that descriptions for each of the embodiments and the practical example are merely simple examples, and do not show the essential structure of the present disclosure. The structure of each part is not limited to the above description as long as it falls within the scope of the present disclosure.

(98) For example, with the previously described embodiment an x-ray source has been used as the radiation source section, but it is also possible to use another radiation source that has transmissivity with respect to the sample, for example, a neutron source. Obviously, in this case, the detection section is capable of detecting the radiation source that is used.

DESCRIPTION OF THE NUMERALS

(99) A.sub.k region G.sub.0 to G.sub.2 grating J.sub.k sum pixel value N.sub.k number of pixels 1 radiation source section 2 grating group 3 detection section 4 conveyer section 5 image creation section 51 pixel value computation section 52 image computation section 53 region specifying section 531 initial image computation section 532 initial image determination section 533 range computation section 534 pixel number computation section 6 control section 7 output section 10 sample

(100) The various embodiments and aspects described above can be combined to provide further embodiments. All of the U.S. patents, U.S. patent application publications, U.S. patent applications, foreign patents, foreign patent applications and non-patent publications referred to in this specification and/or listed in the Application Data Sheet are incorporated herein by reference, in their entirety. Aspects of the embodiments can be modified, if necessary to employ concepts of the various patents, applications and publications to provide yet further embodiments.

(101) These and other changes can be made to the embodiments in light of the above-detailed description. In general, in the following claims, the terms used should not be construed to limit the claims to the specific embodiments disclosed in the specification and the claims, but should be construed to include all possible embodiments along with the full scope of equivalents to which such claims are entitled. Accordingly, the claims are not limited by the disclosure.