Main specifications of XII system.
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Open access peer-reviewed chapter
By Akio Yoneyama, Shigehito Yamada and Tohoru Takeda
Submitted: November 9th 2010Reviewed: April 17th 2011Published: August 23rd 2011
X-ray imaging is widely used for non-destructive observations of the inner structures of samples in many fields, such as biological, clinical, and industrial ones. The transparency of X-rays is much higher than that of visible light, and therefore the spatial distribution of X-ray intensity passing through a sample (radiography) can visualize the mass-density distribution inside the sample. However, X-ray intensity barely changes when passing through samples consisting of a light element, such as carbon, oxygen, or nitrogen, because of theextremely high transmittanceof X-rays. Therefore, the sensitivity of absorption-contrast X-ray imaging is not sufficient for carrying out fine observations of samples such as biological soft tissues and organic materials. Contrast agents, including heavy elements such as iodine, and long exposure to X-rays are ordinarily used to improve sensitivity. However, these supplementary methods may cause allergic reactions and expose subjects to extremely high X-ray dosages.
A fundamental solution to this problem is use of the phase information of X-rays. X-rays are electromagnetic waves having very short wavelength and are mainly characterized by their amplitude and phase. When they pass through samples, their amplitude is decreased and the phase is shifted. In the hard X-ray region, the cross-section of phase shift for light elements is about 1000 times larger than that of absorption ( Momose & Fukuda, 1995 ). Therefore, phase-contrast X-ray imaging, which uses phase shift caused by the sample as image contrast, provides a way of conducting fine observations of biomedical samples without the need for contrast agents or excessive X-ray dosages.
For phase-shift detection, it is essential to convert the phase shift into the change in X-ray intensity because we can only detect the intensity of X-rays by using current-detecting devices. Many conversion methods, such as interferometry with an X-ray crystal interferometer ( Momose & Fukuda, 1995 ; Momose, 1995 ; Takeda et al., 1995), diffractometry with a perfect analyzer crystal (Davis et al., 1995; Ingal and Beliaevskaya, 1995; Chapman et al., 1997), a propagation-based method with a Fresnel pattern (Snigirev et al., 1995; Wilkins et al., 1996), and Talbot interferometry with a Talbot grating interferometer (Momose et al., 2003; Weitkamp et al., 2005), have been developed recently. The principle difference between these methods is in the detection of physical values; that is, interferometry detects the phase shift directly, while the other methods detect the first or second spatial derivation of the phase shift. Therefore, interferometry has the highest sensitivity and is suitable for radiographic and three-dimensional (3D) observation of samples requiring high density resolution, such as biomedical soft tissues. On the other hand, the other methods have a large dynamic range of density and are suitable for observation of samples including regions with large differences in density, such as bone and soft tissues (Yoneyama et al., 2008).
Among these methods, interferometry and diffractometry are two major techniques for biomedical imaging, and 2D and 3D observations of various biomedical samples have been performed using synchrotron radiation. Note that Talbot interferometry using a conventional X-ray source has been studied actively for clinical userecently (Momose, 2009; Donath et al., 2010), because it has theadvantage of cone-beam and/or polychromatic X-rays being useable.
Early X-ray interferometric imaging (XII) was achieved by using a monolithic crystal X-ray interferometer having three wafers cut from one silicon ingot (Bonse & Hart, 1965). Radiographic observations of rat cerebella ( Momose & Fukuda, 1995 ), metastatic liver tumors in humans (Takeda et al., 1995), and cancerous breast tissues (Takeda et al., 2004b) were conducted.The high sensitivity of XII enablesdifferences in biological soft tissues such as cancers and normal tissues to be visualized. Phase-contrast X-ray computed tomography was also achieved in combination with general computed tomography ( Momose et al., 1995 ). Non-destructive 3D observations of small columnar samples of various biological soft tissues were made (Momose et al., 1996; Takeda et al., 2000). To broaden the scope of interferometry to biomedical applications such as in vivo observations, imaging systems fitted with a two-crystal X-ray interferometer (Becker & Bonse, 1974) have been developed(Yoneyama et al., 1999, 2002, 2004a). The latest version of the system has a 60 × 40-mm field of view at an X-ray energy of 17.8 keV (Yoneyama et al., 2004a), and it enables 3D observations with a density resolution of less than 1 mg/mm3.By using this system, in vivo radiographic observation of blood flow in a rat liver (Takeda et al., 2004a), in vivo 3D observation of a tumor implanted in nude mice (Takeda et al., 2004b; Yoneyama et al., 2006), and quantitative analysis of β-amyloid plaques in brains extracted from Alzheimer’s disease model mice (Noda-Saita et al., 2006) were successfully performed.
Diffractometry was expanded and termed diffraction-enhanced imaging (DEI) for fine biomedical observations (Chapman et al., 1997). With this method, observations of breast cancer tissues (Pisano et al., 2000), articular cartilage (Mollenhauer et al., 2002; Ando et al., 2004), and amyloid plaques in the brain of a mouse model of Alzheimer's disease (Connor et al., 2009) were performed. The results showed that DEI had a higher sensitivity than that of conventional radiography and computed tomography. In addition, many developments in DEI (recently known by the more generic name of analyzer-based imaging (ABI)) have also been actively studied, and three images of a sample depicting refraction, ultra-small-angle scatter, and absorption have been obtained recently (Oltulu et al., 2003; Wernick et al., 2003; Rigon et al., 2007). To shorten the measurement time and lower the X-ray dose, a new derivative method using two diffraction beams (forward and normal) was also developed, and a fine tomographic image of breast cancer was obtained (Sunaguchi et al., 2010). In addition, high-energy DEI was developed to extend the dynamic range of density, and an obtained image of an electrical cable showed clearly not only the core and ground wire made of copper but also the isolator and outer jacket made of polymer (Yoneyama et al., 2009).
In this chapter, we will describe the principle of phase-contrast X-ray imaging, two major methods for detecting X-ray phase-shift (XII and DEI), imaging systems for XII and DEI, and examples of fine2D and 3D images of pathological soft tissues and mice embryos.
When X-rays pass through a sample, their amplitude is decreased by absorption and their phase is shifted as shown in Fig. 1 (a). In the hard X-ray region, the refractive index n of the sample is written as
where r e is the classical electron radius, λ is the wavelength of the X-ray, N i is the atomic density of element i, Z i is the atomic number of element i, and f’ i and f’’ i are the real and imaginary parts respectively of the anomalous scattering factor of element i. By using these constituents of the refractive index, the X-ray intensity change ln(I/I o), caused by amplitude decrease in a uniform-density sample, is given by
and the phase-shift dθ is given by
where t is the thickness of the sample. Conventional absorption-contrast X-ray imaging uses ln(I/I o) as image contrast while phase-contrast X-ray imaging uses dθ. Therefore, the sensitivity ratio between absorption- and phase-contrast imaging is given by the ratio of β to δ.
The calculated sensitivity ratios (δ/β) to atomic number for various X-ray energies are plotted in Fig. 1(b). The results show that the ratio of light elements, such as hydrogen, oxygen, nitrogen, and carbon, runs to about 1000 times. Thus, the sensitivity of phase-contrast X-ray
imaging for light elements is about 1000 times higher than that of absorption-contrast X-ray imaging in principle. The high sensitivity of phase-contrast X-ray imaging provides many advantages for biomedical observations. First, fine observations of samples consisting of light elements, such as biological soft tissues and organic materials, can be performed in a short measurement time. Second, the usage of contrast agents is not required, and therefore the density distribution in a sample can be measured independently without considering reactions to contrast agents. Third, δ is almost proportional to the electron density of samples and the square of X-ray energy while β changes abruptly near the energy of the absorption edges; density distribution in a sample can be measured without considering the influenceof the difference of the X-ray energy.
Conventional X-ray computed tomography (CT) uses intensity change ln(I/I o) in samples as input data for reconstruction calculations. When X-rays pass through samples having different density and element regions, ln(I/I o) is written as
where the integration is carried out along the direction of the X-rays. On the other hand, phase-shift dθ caused by the sample is written as
The difference between the two equations above is only in δ andβ, which are the same as in the radiographic observations. Therefore, CT using phase-shift information can be carried out using the same algorithm of reconstruction as conventional X-ray CT. The sensitivity of phase-contrast CT is about 1000 times higher than that of conventional CT for the same reason as previously mentioned forradiographic observation. In addition, dθ is proportional to the sample electron density; the obtained tomograms then provide the electron density distribution of the sample.
A schematic view of a monolithic triple Laue-case X-ray interferometer (Bonse & Hart, 1965) used in early X-ray interferometric imaging is shown in Fig. 2(a). This interferometer is made of silicon crystal and is monolithically cut from one silicon ingot to have three thin crystal wafers. The incident X-ray is divided into two beams (object and reference beams) at the first wafer (S), and these beams are reflected at the second wafer (M) by Laue-case X-ray diffraction. The reflected beams are then superposed at the third wafer (A), and they generate two interference beams by similar X-ray diffraction. Thus, this interferometer acts as a Mach-Zehnder interferometer in the visible light region. The intensity of the interference beams, I i , is given by
where I o is the intensity of the object beam, I r is that of the reference beam, vis the absolute value of the complex degree of coherence, and dθ is the phase shift caused by the sample placed in the path of the object beam. Therefore, dθ can be detected by measuring the interference intensity changes.
To obtain a quantitative phase map showing the spatial distribution of dθ, a sub-fringe method, such as Fourier transfer (FT) (Takeda et al., 1982) and fringe scanning (FS) (Bruning et al., 1974), is required. The former method is traditionally used in in vivo observations as it is used to detect phase shifts from only one interference pattern. The latter method, which requires multiple interference images to calculate phase shift, has a wide dynamic range of density and high spatial resolution compared to that of FT. Therefore, this method is normally used for fine observations of static samples such as formalin-fixed biomedical soft tissues.
To broaden the scope of X-ray interferometric imaging in biomedical applications such as in vivo observations, a large-area field of view and suppression of the thermal disturbance caused by a sample's heat are indispensable. However, the monolithic X-ray interferometer cannot cope with these requirements because the field of view is limited by the size of the silicon ingot from which the interferometer was cut, and the sample cannot be set apart from the optical components of the interferometer due to the geometrical limitations. To overcome these limitations, a two-crystal X-ray interferometer consisting of two silicon-crystal blocks eachhaving two crystal wafers has been developed (Fig. 2 (b))(Becker & Bonse, 1974). By dividing the crystal block of the interferometer into two blocks, the field of view can be extended by four times or more. In addition, the distance between the crystal blocks and the sample can be kept long; the thermal influence, such as deformation of the crystal wafers caused by the sample's heat, is negligible and can be applied for the observation of living samples. On the other hand, a relative rotation between the blocks changes the X-ray phase very sensitively, and therefore rotational stabilization of the subnano-radian order is necessary for performingfine observations.
When X-rays pass through a sample, their optical paths (propagation direction) diverge slightly due to refraction by the sample as shown in Fig. 3(a). This refraction angle, ds, is given by
where dθ/dx is the spatial differential of the phase shift. Therefore, phase shift dθ can be obtained by calculating the integral of ds. The ds canbe detected using the X-ray diffraction of the perfect crystal placed downstream of the sample for analyzing. The intensity of the diffracted X-ray changes depending on the incidence angle to the crystal around the Bragg angle,θB, as shown in Fig. 3(b). This curve is called a rockingcurve, and its full width at halfmaximum (FWHM) is a few arcseconds for a perfect silicon crystal. In addition, the slopes near the angles θL or θH, wherethe diffracted intensity is half the maximum, are very steep. Therefore, the intensity of the diffracted X-ray can be made almost proportionalto ds by adjusting theanalyzer crystal to θL or θH. Namely, the crystal functions as an angular analyzer of the ds, and the ds can be very sensitively detected as changes in the intensity of the diffracted X-ray.
To obtain a correct phase map without the effect of the X-ray absorption by the sample, measurement methods using multiple diffraction images taken at different crystal angles are required. One measurement method is diffraction-enhanced imaging using two (i.e., “T”) images (DEIT) (Chapman et al., 1997). The ds is calculated as
where R(θ) is the reflectivity of the analyzer crystal and I is the intensity of the diffracted X-ray. Only two images are needed, so this method is suitable for quick measurements such as in vivo observations. However, if the ds is larger than the FWHM of the rocking curve, the intensity of the diffracted X-ray shows an incorrect value because the angular point on the rocking curve is far from the peak, where the ds is not proportional to the diffracted intensity. Therefore, the dynamic range of density of DEIT is not as wide as that of the method obtained by scanning the analyzer crystal throughout the rocking curve, i.e., diffraction-enhanced imaging using many (i.e., “M”) images (DEIM) (Koyama et al., 2004). The dsin DEIM is calculated as
where θ k is the angle of the analyzer crystal and I k is the intensity of the diffractedX-ray at θ k . The scanning angular range depends on the spatial density changes in the sample. For samples with large spatial density changes, a large range is required to obtain correct images. A long measurement time is required to obtain the images, but the dynamic range is not limited by the angular width of the total reflection of the analyzer crystal.
A schematic view of an XII system (Yoneyama et al., 2004a; Yoneyama et al., 2005) fitted with a skew-symmetric two-crystal X-ray interferometer (STXI) is shown in Fig. 4. The system consists of an asymmetric crystal, an STXI, positioning tables for the STXI, a sample positioner, and a phase shifter. The imaging system has been set up at beamlineBL-14C2(at the Photon Factory in Tsukuba, Japan) to use the X-ray synchrotron radiation emitted from a vertical wiggler. The X-ray is monochromatized by a Si (220) double-crystal monochromator (not shown), enlarged horizontally by the Si (220) asymmetric crystal, and irradiated onto the first block of the STXI. One interference image generated by the STXI is taken with the charge-coupled device (CCD)-based low-noise X-ray imager for detecting the phase map of the sample. The other image is used in the feedback system stabilizing the X-ray phase fluctuation.The main specifications of the imaging system are shown in Table 1.
To attain subnano-radianmechanical stability of the STXI for fine observation, the positioning tables of the STXI are simplified as much aspossible, made robust against vibration, and driven by laminated piezoelectric translator (PZT) actuators. In addition, the drift rotation is suppressed by the feedback system, which controls the PZT's expansion so as to cancel the movement of the X-ray interference pattern caused by the drift rotationbetween the crystal blocks of the STXI (Yoneyama et al., 2004b). Due to these features, mechanical stability (standard deviation) within 0.04 nradwas achieved, enabling fine observations of biomedical samples to be obtained.
|X-ray energy||17–52 keV|
|Field of view||60×30 mm at 17 keV; 25×30 mm at 35 keV|
|Spatial resolution||Approx. 50 μm|
|Density resolution||Approx. 1 mg/cm3 for 3D measurement for 2 hours|
The X-ray imager consists of a scintillator that converts X-rays into visible light, a relay-lens system that transfers the light from the scintillator to a camera, and a full-frame-type CCD camera (Momose et al., 2001). The field of view of this imager is 36×36 mm, composed of 2048 × 2048 pixels of 18-μm square, and the image-transfer period is about 3 s for a full image. Gd2O2S (GOS) was used to fabricatethescintillator. The GOSthickness is 30 μm, and its absorption ratio is 78 and 20% for 17.8- and 35-keV X-rays, respectively. The CCD camerais cooled with water instead of anair fan to avoid any mechanical vibration.
A sample isplaced in theobject beam path using a sample positioner composed of vertical and horizontal linear tables and a rotational table with the horizontal axis. Each table is driven by stepping motors operated by remote control. A plastic wedge used as a phase-shifter is also positioned by another positioner with the same structure as the sample positioner. Each positioner is attached to rails installed on the frame and can move perpendicular to the interfering beam so that it can be roughly adjusted and the samples can be exchanged. The frame standsindependently of the STXI table so as to prevent vibration caused by the motion of the positioner from disturbing the interference.
Interference images for the FS method are taken by scanning the wedge vertically at even intervals. For 3D observation, the sample isrotated perpendicularly to the beam pathfor 180 degrees by using the rotational table of the sample positioner. The phase-contrast tomogramsare obtained as follows.
Calculate the phase map from the obtained interference images by the FS method.
Unwrap the phase map and then generate a sinogram from it.
Calculate the tomograms using a filter-back projection with a Shepp-Logan filter (Shepp & Logan, 1974).
A schematic view of a DEI system (Yoneyama et al., 2008) is shown in Fig. 5. The system consists of an asymmetric crystal, an analyzer crystal, and an X-ray imager. The X-ray synchrotron radiation emitted from the storage ring is monochromatized and enlarged horizontally by the Si (220) symmetric crystal in the same way as in the XII system, and it irradiates the sample directly. The X-ray beam that has passed through the sample is diffracted by the Si (220) analyzer crystal placed downstream of the sample and is detected by the same X-ray imager used in the XII system. The main specifications of the DEI system are shown in Table 2.
|X-ray energy||17–70 keV|
|Field of view||60×30 mm at 17 keV; 8×30 mm at 70 keV|
|Spatial resolution||Approx. 50 μm|
|Density resolution||More than a few mg/cm3 for 3D measurement for 2 hours|
The asymmetric and analyzer crystals are mounted on a precise rotational mechanism consisting of a vertical rotational table and a tilt table. Each table is driven by a stepping motor remotely, and the rotational resolutions are 0.05 and 8 μradfor horizontal and tilt rotation, respectively. By using these precise tables, the drift rotation of the analyzer crystal can be made negligible. The sample ispositioned by a sample positioner composed of vertical linear tables and a rotational table with the vertical axis. For 3D observation, the sample is rotated vertically for 180 degrees by using the rotational table. The tomogramsare obtained as follows.
Calculate the tomograms using a filter-back projection with a Shepp-Logan filter.
Generate a sinogram from the phase map.
Calculate the phase map by using
Figure 6 shows the phase mapsof a formalin-fixed rat liver obtained using (a) XII, (b) DEIT, (c) DEIM, and (d) conventional radiography (absorptioncontrast). Each image was 24-mm wide and 25-mm high. The X-ray energy was set to 17.8 keV, and the total X-ray dose for obtaining the images was adjusted to remain at the same level by changing the exposure time. The sample was put in a sample cell filled with formalin to prevent rapid phase shifts caused by a large density difference between the sample and its surrounding environment. The fringe number for FS in XIIwas set at 3, and 11 diffraction images were used for DEIM. Large blood vessels with a diameter of ~1 mm can be clearly seen in phase maps (a) to (c), but not in (d), because the phase shift of saline solution injected in blood vessels is different from that of the surrounding liver tissues (Takeda et al., 2002). Blood vessels with a diameter of less than 100 μm can be seen in (a), but not in (b) and (c). In addition, phase maps (b) and (c) include many horizontal noise lines caused by the integral calculation of ds along the x-axis (horizontal direction in the figures). As shown here, the radiographic image quality of XII is better than that of DEIM and DEIT because DEI has no sensitivity in the vertical direction.
Figure 7 shows 3D images and tomograms of a formalin-fixed rat kidney obtained using (a) XII, (b) DEIT, and (c) DEIM. The X-ray energy was set at 35 keV, and the X-ray dose was adjusted to remain at the same level in the same way as in radiographic imaging. The sample was rotated in the sample cell filled with formalin to decrease artifacts caused by a large density difference between the sample and its surroundingenvironment. The image quality of (a) is better than that of (b) and (c); soft tissues such as blood vessels, medullas, and cortexes are clearly visiblein (a), while thedetails of tissues cannot be distinguished in (b) and (c).
The density resolutions of XII, DEIT, and DEIM for X-ray intensities at the sample position are shown in Fig. 8. The density resolutions were calculated from the standard deviation of the relative refractive index in the background regions in each obtained tomogram. The X-ray energy was set at 35 keV, and typical total exposure times to obtain one data set for one projection were 1.5, 3, 7.5, 15, and 30 s. To conduct the comparison correctly, the samephantom consisting of polyethylene tubes filled with saline solution was used with each imaging system. As expected from the observations of the kidney, this result shows that the sensitivity of XII was the highest among these methods. In addition, the sensitivity of DEIM is about one fifth that of DEIT because all the images (including those obtained at the angles far from the Bragg condition) were used to calculate the ds for a wider dynamic range of density. Note that images obtained by DEIT and DEIM include many horizontal noise lines as shown in Fig. 6, and therefore it is thought that the relative difference of the density resolution between XII and DEIs is larger in 3D observations.
A3D image of a formalin-fixed rat tail obtained using DEIM with a 35-keV X-ray beam is shown in Fig. 9. The bone, disc, and hair are clearly visible. The density between the disc and the muscle was very different; therefore, the phaseshift caused by the tail was too large and could not be detected correctly using either XII or DEIT. DEIM has lower sensitivity than the other methods, but it has a wide dynamic range of density and enables observation of a sample having regions with large differences in density.
Current biomedical research commonly uses various imaging techniques, such as X-ray CT, magnetic resonance imaging (MRI), positron emission tomography (PET), optical imaging, and supersonic imaging, to visualize the inner structures of objects(Wu & Tseng, 2004; Weissleder, 2006; Grenier et al., 2009; Hoffman & Grambhir, 2007). Micro-imaging techniques require highspatial resolution of the micrometer order and high contrast resolution,especially for basic biomedical research with small animals. For example, micro-X-ray CT with a conventional X-ray tube has spatial resolution of a few micrometers, but the contrast resolution is significantly low (Ritman, 2002).
X-ray interferometric imaging clearly depicts minute density differences within biological objects composed of low atomic number elements. Thus, this imaging technique was applied to observe biomedical objects, and detailed images that cannot be visualized by conventional X-ray imaging techniques was obtained. Here, we describe ex-vivo and in-vivo biomedical imagesobtained using XII.
A conventional X-ray mammogram is obtained as a projection image, and a lower X-ray energy of 18 keV is used to detect micro-calcification of more than 0.2 mm and soft tissue mass lesions of more than 2–3 mm. The phase-contrast X-ray imaging technique has high sensitivity to detect soft tissue lesions and enables the X-ray exposure for the patient to be decreased.The diagnosis of breast cancer is one of the most important targets of this technique.
An absorption-contrast X-ray image, phase map, and histological picture stained with hematoxylin-eosin of an invasive ductal breast cancer specimen are shown in Fig. 10. Breast tissue and its cancer, which is composed of fat, soft tissue, and micro-calcification, have a wide density difference. Therefore, to increasethe dynamic range of density,a high X-ray energy of 51 keV was used in interferometric imaging of breast tissuespecimens.In the phase map, the mosaic-like structure of breast cancer is clearly depicted, resembling the histological picture, whereas in the absorption-contrast image, the cancer and surrounding breast soft tissue are shown ashomogeneous (Takeda et al., 2004c). The signal to noise ratio of thephase map at 51 keV on soft tissue against surrounding water was approximately 478-folds higher than that of theabsorption X-ray image at 17.7 keV.
The phase map at 51 keV also had an excellent ability to enable differentiationof minute changes in the soft tissue density and detectionof micro-calcifications of 0.036 mm that were undetected by the absorption-contrast X-ray technique. The phase map of the inner breast cancer structures matched well with pathological pictures. Therefore, XII might detect an extremely early stage of breast cancer, and thus it could improve the prognosis for the patient. In addition, the use of 51-keV X-ray energy markedly reducesthe X-ray exposure of the patient. For example, to image a 50-mm-thick object, a 51-keV X-ray dose by XII would be less than 1/80 of the dose in conventional X-ray mammography.
Imaging of cancer is very important for diagnosis and determining a treatment strategy. In a conventional X-ray CT image, the absorption differences among cancer, fibrosis, necrosis, and normal tissues are difficult to detect because the differences in the linear attenuation coefficients of these tissues are very small. As mentioned earlier, XII enables visualizationof the inner structures of human cancer specimens (Takeda et al., 2000) and animal cancer specimens (Momose et al., 1996; Takeda et al., 2004d), the brain (Beckmann et al., 1997), and the kidney (Wu et al., 2009) without contrast agents composed of heavy atomic elements. Here, we describe the images of cancer specimens obtainedusing XIIat 35-keV X-ray energy.
The formalin-fixed specimens, approximately 12mm in diameter, were of colon cancer that had been implanted in nude mice with a subsequent ethanol injection performed to examine the therapeutic effectof ethanol. Obtained sectional images clearly depicted the detailed inner structures of the subcutaneous implanted colon cancer mass, including cancer lesions, necrosis, mixed changes, surrounding tumor vessels, the subcutaneous thin muscle layer, subcutaneous tissue, and skin (Fig.11). Cancer cells underwent necrosis in the central portion of the cancer mass due to the ethanol injection. In addition, the bulging of cancer from the thin muscle layer was well demonstrated. The pathological picture well resembled the phase-contrast sectional image. Thus, pathological information generated by the difference in density could be detected clearly.This indicates that quantitative evaluation could be easily performed using XII for new therapeutic applications.
Alzheimer's disease (AD) is the most common cause of dementia, and it is pathologically characterized by the deposition of amyloid plaques. Amyloid plaques, composed of densely aggregated β-amyloid (Aβ) peptides, are believed to play a key role in the pathogenesis of AD. Therefore, visualization of amyloid plaques is believed important for diagnosing AD. In this study, the brains from 12 PSAPP mice, an excellent AD model mouse for studying amyloid deposition, were imaged by XII at 17.8keV X-ray energy.
Numerous bright white spots having highdensity were typically observed in the brains of 3PSAPP mice at the age of 12 months, whereas no spots were depicted in anage-matched control mouse without the use of contrast agents. An exampleis shown in Fig. 12 (Noda-Saita et al., 2006). To confirm the identity of these bright spots, histological studies were performed after the observation.The bright spots were found to be identical to amyloid plaques. Finally, we performed quantitative analysis of Aβ spots in the brains of 3 PSAPP mice each at 4, 6, 9, and 12 months of age. The results showed that the quantity of Aβ spots clearly increased with age as shown in Fig. 13.
In-vivo observation of a small animal disease model is very important for establishing a new diagnostic and/or treatment method in basic clinical research. With the benefit of a two-crystal interferometer, in-vivo imaging of a mouse implanted with colon cancer was achieved using the XII system (Takeda et al., 2004d). Furthermore, sequential observation was performed to examine the treatment effect of paclitaxelas a cancer drug (Yoneyama et al., 2006).
A series of horizontal slice images obtained from a tumor following injection of paclitaxel is shown in Fig. 13. The tumor size did not change significantly, but the low density area (necrosis) near the center became larger gradually. A typical 3D image observed during the second day after cancer drug therapystarted is shown in Fig. 14. The tumor was 10mm in diameter and ~6mmthick. The blue area indicates a low-density region and the green area indicates a high-density region.
These results showed that the phase-contrast X-ray CT enables us to perform detailedobservation with high spatial resolution without harming the target, and thereforeex-and in-vivo visualization of biomedical objects is believed very useful for biomedical research.
Embryos undergo complicated morphogenetic changes during the course of development. Classically, drawings and solid reconstruction were used to demonstrate the 3D changes of embryonic structures. The wax plate technique of reconstruction was used for embryology, and based on the reconstructed models, numerous accurate drawings of embryos were produced by hand (seeYamada et al., 2006). During the past 20 years, computer-assisted reconstruction of biological structures has become available, which has enabled the reconstruction of various 3D structures from serial sectional images. Non-destructive imaging technologies such as X-ray CT and magnetic resonance (MR) imaging, which were originally developed as non-invasive diagnostic tools in clinical medicine, have also been applied to the imaging and 3D reconstruction of tiny biological structures such as embryos. The MR microscopic technology has been widely used to scan and visualize relatively small samples, including mammalian embryos (Smith et al., 1996; Smith, 1999; Haishi et al., 2001; Yamada et al., 2010), but MR microscopy does not yield resolution or contrast high enough for millimetre-sized embryos. Conventional X-ray CT was also developed for microscopic observation of small structures, but it is not appropriate for soft tissues such as embryos.
Sequential images during mouse embryo development obtained by the DEI system are shown in Fig. 15. By using formalin-fixed mouse embryos, detailed observation of the internal organs can be made throughout the early to late stages of mouse embryonic development by tomographs, as well as of the external appearance by surface reconstruction. The developing bone structures do not affect the phase-contrast images (see E15.5 and E17.5 in Fig. 15).
Embryo images obtained by the XII and DEI systems are shown in Fig. 16. Both systems can provide fine surface reconstruction and images of the internal structure. Images by the XII system seem to be better than those of the DEI systemfor the same embryo, although the scan time of DEI (1hr) is much shorter than that of XII (4–5hrs). The image sharpness can be affected by the direction of the rotation of the samples. Some precioussamples were not glued directly on the stage but were embedded in agar, which was then fixed on the stage by an adhesive agent. Therefore, small deformation of the agar by gravity may affect the images by the XII system.
These images show that the phase-contrast X-ray CT has a wide enough field and high enough resolution for observation and analyses of morphological changes during embryo development.
Phase-contrast X-ray imaging is a novel imaging method using the X-ray phase shift caused by a sample as image contrast. The sensitivity of the method is much higher than that of the conventional method using X-ray absorption by the sample. To detect X-ray phase shift, many detection methods such as X-ray interferometric imaging (XII) and diffraction-enhanced imaging (DEI) have been developed. XII has the highest sensitivity (density resolution) and therefore is suitable for observations requiring highdensity resolution, such as visualization ofβ-amyloid plaques. DEI has a wide dynamic range of density and is thus suitable for observation of samples including regions with large differences in density, such as bone and soft tissues. Many fine observations of pathological soft tissues and mice embryoswere performedby selecting the most suitable imaging method. The results show that phase-contrast X-ray imaging enables us to perform fine observation of biomedical and organic samples without extreme X-ray exposure or any supplemental agents.
We thank Dr. Y. Hirai of Saga Light Source, Dr. Y. Shitaka, Dr. K. Noda-Saita, Dr. N. Amino, Dr. M. Mori, and Dr. M. Kudoof of Astellas Pharma Inc. for experimental help and advice. We also thank Dr. K. Hyodo of the Photon Factory for his technical assistance at the beam line. The observations were carried out under Proposal Nos. 2002S2-001, 2005S2-001,and 2009S2-006 approved by the High Energy Accelerator Research Organization.
The experiment was approved by the Ethics Committee of the University of Tsukuba for the human sample, and the Medical Committee for the Use of Animals in Research of the University of Tsukuba and the Animal Ethical Committee of Astellas Pharma Inc. It conformed to the guidelines of the American Physiological Society for animal experiments.
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