WO2019210883A1 - 用于探测器的准直器及其应用 - Google Patents

用于探测器的准直器及其应用 Download PDF

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Publication number
WO2019210883A1
WO2019210883A1 PCT/CN2019/085728 CN2019085728W WO2019210883A1 WO 2019210883 A1 WO2019210883 A1 WO 2019210883A1 CN 2019085728 W CN2019085728 W CN 2019085728W WO 2019210883 A1 WO2019210883 A1 WO 2019210883A1
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Prior art keywords
hole
collimator
imaging
hole segment
top plate
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PCT/CN2019/085728
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English (en)
French (fr)
Inventor
刘亚强
王海鹏
侯岩松
江年铭
张琛
陈思
高丽蕾
田冬玲
许天鹏
齐畅
刘迈
Original Assignee
北京永新医疗设备有限公司
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Priority claimed from CN201810409873.6A external-priority patent/CN108685591B/zh
Priority claimed from CN201820647942.2U external-priority patent/CN209220307U/zh
Application filed by 北京永新医疗设备有限公司 filed Critical 北京永新医疗设备有限公司
Priority to JP2021510513A priority Critical patent/JP7102610B2/ja
Priority to KR1020207034751A priority patent/KR102565843B1/ko
Priority to EP19797148.4A priority patent/EP3811868A4/en
Priority to US17/052,305 priority patent/US11576633B2/en
Publication of WO2019210883A1 publication Critical patent/WO2019210883A1/zh

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/40—Arrangements for generating radiation specially adapted for radiation diagnosis
    • A61B6/405—Source units specially adapted to modify characteristics of the beam during the data acquisition process
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
    • A61B6/03—Computed tomography [CT]
    • A61B6/037—Emission tomography
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/06—Diaphragms
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/42—Arrangements for detecting radiation specially adapted for radiation diagnosis
    • A61B6/4291—Arrangements for detecting radiation specially adapted for radiation diagnosis the detector being combined with a grid or grating
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
    • G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
    • G01T1/16—Measuring radiation intensity
    • G01T1/161—Applications in the field of nuclear medicine, e.g. in vivo counting
    • G01T1/164—Scintigraphy
    • G01T1/1641—Static instruments for imaging the distribution of radioactivity in one or two dimensions using one or several scintillating elements; Radio-isotope cameras
    • G01T1/1642—Static instruments for imaging the distribution of radioactivity in one or two dimensions using one or several scintillating elements; Radio-isotope cameras using a scintillation crystal and position sensing photodetector arrays, e.g. ANGER cameras
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
    • G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
    • G01T1/29—Measurement performed on radiation beams, e.g. position or section of the beam; Measurement of spatial distribution of radiation
    • G01T1/2914—Measurement of spatial distribution of radiation
    • G01T1/2921—Static instruments for imaging the distribution of radioactivity in one or two dimensions; Radio-isotope cameras
    • G01T1/295—Static instruments for imaging the distribution of radioactivity in one or two dimensions; Radio-isotope cameras using coded aperture devices, e.g. Fresnel zone plates
    • G—PHYSICS
    • G02—OPTICS
    • G02B—OPTICAL ELEMENTS, SYSTEMS OR APPARATUS
    • G02B27/00—Optical systems or apparatus not provided for by any of the groups G02B1/00 - G02B26/00, G02B30/00
    • G02B27/30—Collimators
    • G—PHYSICS
    • G21—NUCLEAR PHYSICS; NUCLEAR ENGINEERING
    • G21K—TECHNIQUES FOR HANDLING PARTICLES OR IONISING RADIATION NOT OTHERWISE PROVIDED FOR; IRRADIATION DEVICES; GAMMA RAY OR X-RAY MICROSCOPES
    • G21K1/00—Arrangements for handling particles or ionising radiation, e.g. focusing or moderating
    • G21K1/02—Arrangements for handling particles or ionising radiation, e.g. focusing or moderating using diaphragms, collimators
    • G21K1/025—Arrangements for handling particles or ionising radiation, e.g. focusing or moderating using diaphragms, collimators using multiple collimators, e.g. Bucky screens; other devices for eliminating undesired or dispersed radiation

Definitions

  • the present disclosure relates to the field of nuclear medicine imaging technology, and in particular to collimators for detectors and their applications, and more particularly to collimators and detectors for detectors.
  • Emission tomography is a non-invasive nuclear medicine imaging method.
  • Single photon Emission Computed Tomography is a kind of emission tomography, which has been widely used in preclinical drug research and Clinical disease diagnosis.
  • Spatial resolution and detection efficiency are two important technical indicators for measuring SPECT imaging performance.
  • SPECT imaging requires collimation of the rays, and conventional clinical SPECTs are equipped with parallel-hole collimators. With the development of nuclear medicine, the spatial resolution and detection efficiency of parallel-hole collimator SPECT are difficult to meet higher clinical requirements.
  • the multi-pinhole collimator can achieve better detection efficiency and better spatial resolution by reducing the imaging field of view and designing appropriate pinhole magnification and pinhole arrangement. Therefore, the multi-pinhole SPECT imaging system is an important development direction of current emission tomography.
  • the application of multi-pinhole collimators to the clinic still needs to overcome some difficulties: although the target field of view of the multi-pinhole collimator is a small human body, radioactive rays from other parts of the body may pass through the pinhole on the detector. Producing a projection, if this part of the projection overlaps with the projection of the small organ, it will reduce the reconstruction spatial resolution or it is difficult to reconstruct a reasonable image; in order to obtain higher detection efficiency, the pinhole aperture of the multi-pinhole collimator needs to be designed.
  • the present disclosure is intended to address at least one of the technical problems existing in the prior art. To this end, it is an object of the present disclosure to provide a collimator for a detector that selectively occludes radioactive rays passing through the imaging through-hole through the top plate, thereby effectively reducing the overlap between different pinhole projections. Moreover, the detection efficiency and spatial resolution of the detector are significantly improved, and the reconstructed image quality is better.
  • the present disclosure provides a collimator for a detector.
  • the collimator includes: a bottom plate on which an imaging through hole distributed in an array is disposed, the imaging through hole includes a first hole segment and a second hole segment, and the first The lateral dimension of the hole segment gradually decreases along the free end toward the second hole segment, and the transverse dimension of the second hole segment gradually decreases along the free end toward the first hole segment; the shielding ring, the a shielding ring formed on the bottom plate; and a top plate disposed in the shielding ring and closing at least part of the opening of the shielding ring, wherein the top plate is provided with a shielding through hole arranged in an array, And the imaging through hole and the shielding through hole are arranged in one-to-one correspondence.
  • the radioactive rays passing through the imaging through holes are secondarily blocked by the top plate, effectively reducing the overlap between different pinhole projections, and passing the distance between the conditional top plate and the bottom plate
  • the parameters of the imaging through hole and the shielding through hole can change the ratio of the light blocking rate.
  • the detection efficiency and spatial resolution of the detector are significantly improved, and the reconstructed image quality is better.
  • the collimator has a low processing cost and is easy to popularize and apply.
  • collimator according to the above embodiment of the present disclosure may also have the following additional technical features:
  • the first hole segment and the second hole segment are symmetrically disposed in the up and down direction.
  • the first hole segment and the second hole segment are independently a circular table or a polygonal plate.
  • the shield through hole is a straight hole or a slant hole.
  • a lower edge of the shield through hole coincides with an intersection of an extended face of the annulus where the inner wall of the first hole segment is located and a lower surface of the top plate.
  • the collimator has a light blocking ratio of not more than 10%, wherein the light blocking ratio is determined based on the following formula,
  • S 1 represents a projected area of the penumbra of the collimator
  • S 2 represents a projected area of the umbral area of the collimator
  • H represents a distance from a center of the imaging through hole to the surface of the detector
  • ⁇ represents the angle of the diagonal of the imaging through hole
  • D represents the maximum aperture of the imaging through hole
  • T represents the distance from the bottom surface of the bottom plate to the top surface of the top plate.
  • the thickness of the top plate and the bottom plate are each not less than 3.5 mm.
  • the bottom plate has a thickness of 10-14 mm and the top plate has a thickness of 2-6 mm.
  • the through hole of the shield has a hole diameter of 3-6 mm. According to a preferred embodiment of the present disclosure, the through hole of the shield has a hole diameter of 4.5 mm.
  • the present disclosure further proposes a detector.
  • the detector includes the aforementioned collimator.
  • the detector has high detection efficiency and spatial resolution, and the reconstructed image quality is good.
  • the collimator has all the technical features and technical effects of the foregoing collimator, and details are not described herein again.
  • the detector is a variable angle dual probe SPECT.
  • FIG. 1 shows a partial structural schematic view of a collimator according to an embodiment of the present disclosure
  • FIG. 2 shows a schematic structural view of a bottom plate according to an embodiment of the present disclosure
  • FIG. 3 is a schematic structural view of a longitudinal section of a bottom plate according to an embodiment of the present disclosure
  • FIG. 4 shows a schematic structural view of a top plate according to an embodiment of the present disclosure
  • Figure 5 is a schematic view showing the principle of shading of the existing collimator
  • FIG. 6 shows a schematic diagram of results of shading rates in accordance with an embodiment of the present disclosure
  • FIG. 7 shows a schematic structural view of a longitudinal section of a top plate according to an embodiment of the present disclosure
  • FIG. 8 shows a schematic diagram of a shading principle of a collimator according to an embodiment of the present disclosure
  • FIG. 9 is a schematic view showing a result of shading of a collimator according to an embodiment of the present disclosure.
  • FIG. 10 is a schematic view showing a result of shading of a collimator according to an embodiment of the present disclosure.
  • Figure 11 shows a schematic diagram of dual probe SPECT imaging in accordance with one embodiment of the present disclosure.
  • first and second are used for descriptive purposes only, and are not to be construed as indicating or implying a relative importance or implicitly indicating the number of technical features indicated. Thus, features defining “first” and “second” may include one or more of the features either explicitly or implicitly. Further, in the description of the present disclosure, "a plurality of” means two or more unless otherwise stated.
  • the present disclosure provides a collimator for a detector.
  • the radioactive rays passing through the imaging through holes are secondarily blocked by the top plate, the overlap between the different pinhole projections is effectively reduced, and by adjusting the distance between the top plate and the bottom plate And the parameters of the imaging through hole and the shielding through hole can change the ratio of the light blocking rate.
  • the detection efficiency and spatial resolution of the imaging system of the detector are significantly improved, and the reconstructed image quality is better.
  • the collimator has a low processing cost and is easy to popularize and apply.
  • FIGS. 1-9 may include a bottom plate 100, a shield ring 200, and a top plate 300.
  • the components of the collimator are specifically described below:
  • the bottom plate 100 as shown in FIGS. 2 and 3, according to an embodiment of the present disclosure, the bottom plate 100 is provided with an imaging through hole 110 distributed in an array, the imaging through hole 110 includes a first hole segment 111 and a second hole segment 112, And the lateral dimension of the first hole segment 111 gradually decreases along the free end toward the second hole segment, and the lateral dimension of the second hole segment 112 gradually decreases along the free end toward the first hole segment 111. In other words, the first hole segment 111 and the second hole segment 112 are gradually reduced in the lateral direction from the free end toward the center of the bottom plate.
  • the inventors have discovered that the use of two through-hole segments in the imaging vias 110 of the embodiments of the present disclosure can increase the thickness of the material at the smallest lateral dimension, reducing the intensity of penetration of radiation from the portion, as compared to the use of one through-hole segment.
  • the properties of the first hole segment 111 and the second hole segment 112 may be symmetrical or asymmetric. That is to say, the parameters such as the shape, height and lateral dimension of the first hole segment 111 and the second hole segment 112 may be the same or different. According to a preferred embodiment of the present disclosure, the first hole segment 111 and the second hole segment 112 are symmetrically disposed in the up and down direction.
  • the orientations of the different imaging through holes 110 point in different directions, all of which converge at the center of the imaging field of view.
  • the first hole segment 111 and the second hole segment 112 may independently be a circular table or a polygonal plate. That is, the first hole segment 111 and the second hole segment 112 may be arbitrarily a truncated cone or a multi-ribbed table. Wherein, the upper and lower surfaces of the truncated cone may be circular, elliptical, or other irregular circular shapes.
  • Shield Ring 200 The shield ring 200 is formed on the base plate 100 in accordance with an embodiment of the present disclosure. Thereby, the shielding ring blocks the light that is incident on the collimator from the external environment.
  • Top plate 300 Referring to FIG. 4, according to an embodiment of the present disclosure, the top plate 300 is disposed in the shielding ring 200 and encloses at least a portion of the opening of the shielding ring 200, and the top plate 300 is provided with shielding through holes 310 distributed in an array.
  • the imaging through hole 310 and the shielding through hole 110 are disposed in one-to-one correspondence. That is, the top plate 300 is disposed opposite the bottom plate 100 and the periphery is located within the shield ring 200.
  • the secondary occlusion of the radioactive rays passing through the imaging through hole by the top plate effectively reduces the overlap between the projections of the different pinholes, and by adjusting the distance between the top plate and the bottom plate and the imaging through hole and the shielding through
  • the parameters of the hole can change the ratio of the shading rate. Furthermore, the detection efficiency and spatial resolution of the detector are significantly improved, and the reconstructed image quality is better.
  • the bottom plate 100 and the top plate 300 are disposed in parallel. Thereby, the structural design can be simplified and assembly is facilitated.
  • the target field of view is in the area covered by the pinhole opening angle , but the angle at which the incident radioactive ray is actually incident is ⁇ .
  • ⁇ the angle at which the incident radioactive ray is actually incident
  • ⁇ represents an angle between a midpoint of the connecting face of the first hole segment and the second hole segment to a free end of the first hole segment
  • ⁇ represents the angle between the diagonals of the imaging through hole 110;
  • D represents the maximum radial dimension of the joint faces of the first bore section and the second bore section
  • the projection range of the shadow area and the penumbra area is as shown in Fig. 5.
  • the shadow area is also the projection area covered by the opening angle in Fig. 5.
  • the penumbra area is also the area covered by the ⁇ angle in Fig. 5 minus the area.
  • the detector 600 has both a projection of the umbra and a projection of the penumbra on the plane, and the shape of the projection is circular.
  • the projected area of the shadow area is represented by S 2
  • S 1 represents the projected area of the penumbra of the collimator, that is, the area covered by the ⁇ angle in FIG. 5 minus the area of the remaining area of the umbra;
  • S 2 represents the projected area of the umbral area of the collimator, that is, the area of the projection area covered by the opening angle in FIG. 5;
  • H represents the distance from the center of the imaging through hole 110 to the surface of the detector
  • ⁇ represents the angle between the midpoint of the connecting face of the first hole segment 111 and the second hole segment 112 to the free end of the first hole segment 111;
  • D represents the maximum aperture of the imaging via 110
  • T represents the distance from the bottom surface of the bottom plate 100 to the top surface of the top plate 300.
  • the light blocking ratio is the ratio of the projected area S 1 of the penumbra and the projected area of the shadow area by S 2 , and the relationship between the light blocking rate and the thickness of the collimator is as shown in FIG. 6 .
  • the thickness of the collimator is at least about 80 mm.
  • the materials used to make the collimator are relatively expensive, and some materials (such as tungsten) are difficult to process, and it is impractical to use a thick collimator.
  • the visor 400 of FIG. 5, thereby, can significantly reduce the thickness of the bottom plate 100 and the top plate 300, and the thickness of the bottom plate 100 and the top plate 300, the distance between the bottom plate 100 and the top plate 300, and the imaging of different shapes and sizes.
  • the hole 110 and the shield through hole 310 can meet different design requirements and have great flexibility.
  • the top plate 300 has twelve elliptical shield through holes 310 that correspond one-to-one with the imaging through holes 110 on the bottom plate.
  • the shield via 310 is a straight hole (as shown in FIG. 7A) or a slant hole (as shown in FIG. 7B) according to an embodiment of the present disclosure. Changing the inclined hole to the straight hole makes the processing more convenient, and the influence on the shielding effect can be neglected, and those skilled in the art can select according to the processing difficulty.
  • the size of the elliptical hole is designed to block as much as possible the shadow of the penumbra of the imaging pinhole without affecting the projection of the umbra, and the occlusion effect is as shown in FIGS. 8, 9, and 10.
  • the penumbra on the imaging detector is small and hardly overlaps with adjacent umbral areas.
  • the inventors have found that when the lower edge of the shield through hole 310 coincides with the intersection of the extended surface of the annulus where the inner wall of the first hole segment 111 is located and the lower surface of the top plate 300, that is, the inner wall of the first hole segment 111 is located.
  • the pattern formed by the extension of the face intersecting the lower surface of the top plate 300 also constitutes the lower edge of the shield through hole 310. At this time, the light blocking rate is small, and the area of the penumbra S 1 is close to zero.
  • the distance between the bottom plate 100 and the top plate 300, as well as the imaging through holes 110 and the shielding through holes 310 of different shapes and sizes, can be adjusted according to different design requirements, and have great flexibility.
  • the ray from the non-target organ can be selectively subjected to additional occlusion of some angles to shield the unwanted or affecting image quality, so that the detection efficiency and spatial resolution of the detector are significantly improved. , reconstructed image quality is better.
  • the equivalent thickness of the collimator of the embodiment of the present disclosure is the distance from the bottom surface of the bottom plate 100 to the top surface of the top plate 300, that is, equivalent to the thickness of the bottom plate 100,
  • the thickness of the top plate 300 and the distance between the bottom plate 100 and the top plate 300 are the sum of the three.
  • the distance between the two plates can be determined by subtracting the thickness of the first plate and the thickness of the second plate by D.
  • the bottom plate 100, the top plate 300, and the shield 200 may be formed of at least one of gold, ruthenium, platinum, tungsten, and lead.
  • the bottom plate 100, the top plate 300, and the shield 200 may be formed of the same material.
  • the thickness of the bottom plate 100 and the top plate 300 need to be ensured not to be penetrated by rays. If the ray energy is 140 keV, the flat material is tungsten, and the plate is set to block at least 99.999% of the rays, the minimum thickness T of the plate. Can be found by the following formula,
  • the thickness of the top plate 300 and the bottom plate 100 are each not less than 3.5 mm. Therefore, it is possible to effectively block the radiation and prevent the radiation from being penetrated.
  • the thickness of the bottom plate should not be too thin.
  • the bottom plate 100 has a thickness of 10-14 mm and the top plate 300 has a thickness of 2-6 mm. Therefore, the thickness of the bottom and the top is suitable, and the ray of the imaging through hole can only reach a corresponding shielding through hole, the light blocking rate is lower, the detection efficiency and spatial resolution of the detector are remarkably improved, and the reconstructed image quality is better. .
  • the through hole 310 has a hole diameter of 3-6 mm. According to a preferred embodiment of the present disclosure, the through hole 310 has a hole diameter of 4.5 mm. Therefore, the aperture of the shielding through hole is suitable, and the radiation of the imaging through hole can only reach a corresponding shielding through hole, and the light blocking rate is lower.
  • the collimator further includes a support member 500 disposed between the top plate 300 and the bottom plate 100 for supporting the fixed top plate 300 and the bottom plate 100.
  • the support member 500 may also be formed of at least one of tungsten, lead, gold, platinum, and rhodium. Further, the support member 500 can also be formed of the same material as the top plate 300 and the bottom plate 100.
  • the present disclosure further proposes a detector.
  • the detector includes the aforementioned collimator.
  • the detector has high detection efficiency and spatial resolution, and the reconstructed image quality is good.
  • the dual-probe SPECT in which the aforementioned collimator is mounted can perform tomographic imaging and dynamic tomography of a small human body without rotation. It should be noted that the collimator has all the technical features and technical effects of the foregoing collimator, and details are not described herein again.
  • the detector of the embodiment of the present disclosure is particularly suitable for imaging a small organ of the human body for the heart, the thyroid or the brain, but the use of the detector is not limited to performing tomographic imaging and dynamic tomography on small organs of the human body. It is also possible to perform tomographic imaging and dynamic tomography of some organs and organs of an animal, and other objects that can be imaged by the detector of the embodiment of the present disclosure are applicable to the detector of the embodiment of the present disclosure.
  • the detector is a variable angle dual probe SPECT.
  • FIG. 11 it is a schematic diagram of imaging a small organ of a human body by dual-probe SPECT.
  • the multi-pinhole SPECT imaging apparatus having the collimator 10 described above, the two detectors are placed at an angle, and the imaging field of view is located between the angles of the two detectors, and all the pinholes can cover a sphere sufficient to contain the heart region. Vision.
  • the SPECT imaging device can achieve high sensitivity, for example, rapid tomographic imaging of the heart without rotation, and in particular, the device can also achieve dynamic imaging of the heart.

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Abstract

一种用于探测器(600)的准直器(10)，准直器(10)包括：底板(100)，底板(100)上设置有呈阵列分布的成像通孔(110)，成像通孔(110)包含第一孔段(111)和第二孔段(112)，且第一孔段(111)的横向尺寸沿自由端向第二孔段(112)的方向逐渐减小，第二孔段(112)的横向尺寸沿自由端向第一孔段(111)的方向逐渐减小；屏蔽圈(200)，屏蔽圈(200)形成在底板(100)上；以及顶板(300)，顶板(300)设置在屏蔽圈(200)内，并封闭屏蔽圈(200)的至少部分开口，且顶板(300)上设置有呈阵列分布的屏蔽通孔(310)，且成像通孔(110)和屏蔽通孔(310)一一对应设置。

Description

用于探测器的准直器及其应用
优先权信息
本公开请求于2018年05月02日向中国国家知识产权局提交的、专利申请号为201810409873.6、申请名称为“用于探测器的准直器及其应用”以及专利申请号为201820647942.2、申请名称为“用于探测器的准直器及含有准直器的探测器”的中国专利申请的优先权，并且其全部内容通过引用结合在本公开中。
技术领域
本公开涉及核医学成像技术领域，具体地，涉及用于探测器的准直器及其应用，更具体地，涉及用于探测器的准直器和探测器。
背景技术
发射断层成像技术是一种非侵入式的核医学成像方法，单光子发射计算机断层成像(SPECT，Single Photon Emission Computed Tomography)是发射断层成像的一种，目前已广泛应用于预临床的药物研究和临床疾病诊断。空间分辨率和探测效率是衡量SPECT成像性能的两个重要技术指标。SPECT成像需要对射线进行准直，传统的临床SPECT均配有平行孔准直器。随着核医学的发展，平行孔准直器SPECT的空间分辨率和探测效率难以满足更高的临床需求，针对小器官成像，如心脏、甲状腺、脑等，如果给传统SPECT的探测器配备专用的多针孔准直器，可以通过缩小成像视野，设计合适的针孔放大倍数和针孔排布方式，获得更高的探测效率和更好的空间分辨率。因此多针孔SPECT成像系统是当前发射断层成像技术的一个重要发展方向。
然而，将多针孔准直器应用到临床仍需要克服一些难题：虽然多针孔准直器的目标视野是人体小器官，但来自人体其他部位的放射性射线也可能通过针孔在探测器上产生投影，这部分投影如果和小器官的投影发生交叠，会降低重建空间分辨率或难以重建出合理图像；为了获得更高的探测效率，多针孔准直器的针孔孔径需要设计的比较大，这时由于针孔投影半影区的影响会导致投影交叠更加严重；通过增加准直器板的厚度可以一定程度减小半影区，但过厚的准直器使得材料成本高昂且加工难度大，在实际中无法应用。
由此，一种可以有效消除多针孔准直器中不同针孔投影的交叠，兼顾探测效率、空间分辨率和重建图像质量的准直器有待研究。
公开内容
本公开旨在至少解决现有技术中存在的技术问题之一。为此，本公开的一个目的在于提出一种用于探测器的准直器，通过顶板对穿过成像通孔的放射性射线进行二次遮挡，有 效减小不同针孔投影之间的交叠，并且使探测器的探测效率和空间分辨率显著提高，重建图像质量更好。
根据本公开的一个方面，本公开提供了一种用于探测器的准直器。根据本公开的实施例，该准直器包括：底板，所述底板上设置有呈阵列分布的成像通孔，所述成像通孔包含第一孔段和第二孔段，且所述第一孔段的横向尺寸沿自由端向所述第二孔段的方向逐渐减小，所述第二孔段的横向尺寸沿自由端向所述第一孔段的方向逐渐减小；屏蔽圈，所述屏蔽圈形成在所述底板上；以及顶板，所述顶板设置在所述屏蔽圈内，并封闭所述屏蔽圈的至少部分开口，且所述顶板上设置有呈阵列分布的屏蔽通孔，且所述成像通孔和所述屏蔽通孔一一对应设置。
根据本公开实施例的准直器，通过顶板对穿过成像通孔的放射性射线进行二次遮挡，有效减小不同针孔投影之间的交叠，并且，通过条件顶板和底板之间的距离以及成像通孔和屏蔽通孔的参数，可以改变遮光率的比例。进而，使探测器的探测效率和空间分辨率显著提高，重建图像质量更好。此外，该准直器的加工成本低，易于推广应用。
另外，根据本公开上述实施例的准直器还可以具有如下附加的技术特征：
根据本公开的实施例，所述第一孔段和所述第二孔段在上下方向上对称设置。
根据本公开的实施例，所述第一孔段和所述第二孔段独立地为圆台或多棱台。
根据本公开的实施例，所述屏蔽通孔为直孔或斜孔。
根据本公开的实施例，所述屏蔽通孔的下边沿与所述第一孔段的内壁所在环面的延长面与所述顶板的下表面的交线重合。
根据本公开的实施例，所述准直器的遮光率不大于10％，其中，所述遮光率是基于下列公式确定的，
Figure PCTCN2019085728-appb-000001
其中，S 1代表所述准直器的半影区投影面积；S 2代表所述准直器的本影区投影面积；H代表所述成像通孔的中心到所述探测器表面的距离；α代表所述成像通孔对角线的夹角；D代表所述成像通孔的最大孔径；T代表所述底板的底面到所述顶板的顶面的距离。
根据本公开的实施例，所述顶板和所述底板的厚度均不小于3.5毫米。根据本公开的优选实施例，所述底板的厚度为10-14毫米，所述顶板的厚度为2-6毫米。
根据本公开的实施例，所述屏蔽通孔的孔径为3-6毫米。根据本公开的优选实施例，所述屏蔽通孔的孔径为4.5毫米。
在此基础上，本公开进一步提出了探测器。根据本公开的实施例，该探测器包括前述的准直器。由此，该探测器的探测效率和空间分辨率高，重建图像质量好。其中，需要说明的是，该准直器具有前述准直器的全部技术特征和技术效果，在此不再一一赘述。
根据本公开的实施例，所述探测器为可变角双探头SPECT。
本公开的附加方面和优点将在下面的描述中部分给出，部分将从下面的描述中变得明显，或通过本公开的实践了解到。
附图说明
本公开的上述和/或附加的方面和优点从结合下面附图对实施例的描述中将变得明显和容易理解，其中：
图1显示了根据本公开一个实施例的准直器的局部结构示意图；
图2显示了根据本公开一个实施例的底板的结构示意图；
图3显示了根据本公开一个实施例的底板纵截面的结构示意图；
图4显示了根据本公开一个实施例的顶板的结构示意图；
图5显示了现有准直器遮光原理的示意图；
图6显示了根据本公开一个实施例的遮光率的结果示意图；
图7显示了根据本公开一个实施例的顶板的纵截面的结构示意图；
图8显示了根据本公开一个实施例的准直器的遮光原理的示意图；
图9显示了根据本公开一个实施例的准直器的遮光结果的示意图；
图10显示了根据本公开一个实施例的准直器的遮光结果的示意图；
图11显示了根据本公开一个实施例的双探头SPECT成像的示意图。
公开详细描述
下面详细描述本公开的实施例，所述实施例的示例在附图中示出，其中自始至终相同或类似的标号表示相同或类似的元件或具有相同或类似功能的元件。下面通过参考附图描述的实施例是示例性的，仅用于解释本公开，而不能理解为对本公开的限制。
在本公开的描述中，术语“纵向”、“横向”、“上”、“下”、“前”、“后”、“左”、“右”、“竖直”、“水平”、“顶”、“底”等指示的方位或位置关系为基于附图所示的方位或位置关系，仅是为了便于描述本公开而不是要求本公开必须以特定的方位构造和操作，因此不能理解为对本公开的限制。
需要说明的是，术语“第一”、“第二”仅用于描述目的，而不能理解为指示或暗示相对重要性或者隐含指明所指示的技术特征的数量。由此，限定有“第一”、“第二”的特征可以明示或者隐含地包括一个或者更多个该特征。进一步地，在本公开的描述中，除非另有说明，“多个”的含义是两个或两个以上。
准直器
根据本公开的一个方面，本公开提供了一种用于探测器的准直器。根据本公开实施例的准直器，通过顶板对穿过成像通孔的放射性射线进行二次遮挡，有效减小不同针孔投影之间的交叠，并且，通过调节顶板和底板之间的距离以及成像通孔和屏蔽通孔的参数，可以改变遮光率的比例。进而，使探测器的成像系统的探测效率和空间分辨率显著提高，重 建图像质量更好。此外，该准直器的加工成本低，易于推广应用。
为了便于理解该准直器，参考图1-9对本公开实施例的准直器进行解释说明，该准直器根可以包括：底板100、屏蔽圈200和顶板300。下面对该准直器的各组件进行具体说明：
底板100：如图2和3所示，根据本公开的实施例，底板100上设置有呈阵列分布的成像通孔110，该成像通孔110包含第一孔段111和第二孔段112，且第一孔段111的横向尺寸沿自由端向所述第二孔段的方向逐渐减小，第二孔段112的横向尺寸沿自由端向第一孔段111的方向逐渐减小。换句话说，第一孔段111和第二孔段112由自由端向底板的中心方向，横向尺寸逐渐减小。发明人发现，与采用一个通孔段相比，本公开实施例的成像通孔110采用两个通孔段可以增加横向尺寸最小处材料的厚度，降低射线从该部分穿透的强度。
其中，第一孔段111和第二孔段112的性质可以是对称的，也可以是不对称的。也就是说，第一孔段111和第二孔段112的形状，高度和横向尺寸等参数可以相同，也可以不同。根据本公开的优选实施例，第一孔段111和第二孔段112在上下方向上对称设置。
根据本公开的实施例，不同成像通孔110的朝向(即圆锥轴线方向)指向不同的方向，所有朝向汇聚在成像视野的中心。由此，实现不同成像通孔对同一成像视野的成像，可同时获得待成像物体在不同角度上的投影并用于重建。
根据本公开的实施例，第一孔段111和第二孔段112可以独立地为圆台或多棱台。也就是说，第一孔段111和第二孔段112可以任意的为圆台或多棱台。其中，圆台的上下表面可以是圆形、椭圆形，也可以是其它不规则的圆形。
屏蔽圈200：根据本公开的实施例，该屏蔽圈200形成在底板100上。由此，屏蔽圈遮挡住从外界环境射入准直器的光线。
顶板300：参考图4，根据本公开的实施例，该顶板300设置在屏蔽圈200内，并封闭屏蔽圈200的至少部分开口，且该顶板300上设置有呈阵列分布的屏蔽通孔310，且该成像通孔310和屏蔽通孔110一一对应设置。也就是说，顶板300相对设置在底板100的上方，并且周边位于屏蔽圈200内。由此，通过顶板对穿过成像通孔的放射性射线进行二次遮挡，有效减小不同针孔投影之间的交叠，并且，通过调节顶板和底板之间的距离以及成像通孔和屏蔽通孔的参数，可以改变遮光率的比例。进而，使探测器的探测效率和空间分辨率显著提高，重建图像质量更好。
根据本公开的实施例，底板100和顶板300平行设置。由此，可简化结构设计并方便组装。
在此，进一步对准直器的遮光原理进行解释说明，如图3所示，通常来说，目标视野在针孔张角ɑ所覆盖的区域内，但实际可接受放射性射线入射的角度为β，其中，当针孔朝向和第一平板垂直时，ɑ、β之间有如下关系：
Figure PCTCN2019085728-appb-000002
其中，
α代表所述第一孔段和所述第二孔段的连接面的中点到所述第一孔段自由端的夹角；
β代表成像通孔110对角线的夹角；
T 0代表底板100的厚度，也就是T 0＝T 1+T 2；
D代表所述第一孔段和所述第二孔段的连接面的最大径向尺寸；
本影区和半影区的投影范围如5所示，本影区也就是图5中ɑ张角所覆盖的投影区域，半影区也就是图5中β张角所覆盖的区域减去本影区的剩余区域。在此种情况下，探测器600平面上既有本影区的投影又有半影区的投影，投影的形状均为圆形。将本影区投影面积用S 2表示，半影区投影面积用S 1表示，在T 1＝0的情况下，二者的比值满足如下关系：
Figure PCTCN2019085728-appb-000003
其中，
S 1代表准直器的半影区投影面积，也就是图5中β张角所覆盖的区域减去本影区的剩余区域的面积；
S 2代表准直器的本影区投影面积，也就是图5中ɑ张角所覆盖的投影区域的面积；
H代表成像通孔110的中心到探测器表面的距离；
α代表第一孔段111和第二孔段112的连接面的中点到第一孔段111自由端的夹角；
D代表成像通孔110的最大孔径；
T代表底板100的底面到顶板300的顶面的距离。
其中，遮光率为半影区投影面积S 1和本影区投影面积用S 2的比值，遮光率随着准直器厚度的变化关系如图6所示。由图6可知，为了使半影区面积降低到本影区面积的10％左右，也就是遮光率为10％，准直器的厚度至少要达到约80mm。通常制作准直器的材料都比较昂贵，且部分材料(如钨)加工难度大，采用厚的准直器不切实际。发明人在研究中发现，通过设置顶板300进行二次遮挡，也就是由底板100和顶板300共同实现图5中遮光板400的作用，即底板100、顶板300和二者之间的部分共同构成图5中的遮光板400，从而，可以显著减小底板100和顶板300的厚度，并且，底板100和顶板300的厚度，底板100和顶板300之间的距离，以及不同形状和尺寸的成像通孔110和屏蔽通孔310，可以满足不同的设计需求，具有很大的灵活性。
在本公开的一个实施例中，如图4所示，顶板300上有12个椭圆形的屏蔽通孔310，和底板上的成像通孔110一一对应。
如图7所示，根据本公开的实施例，根据本公开的实施例，屏蔽通孔310为直孔(如图7A所示)或斜孔(如图7B所示)。将斜孔改为直孔会更方便进行加工，对遮挡效果的影响可以忽略，本领域技术人员可依据加工难易度自行选取。
进一步地，椭圆形孔的大小设计成尽可能多地遮挡掉成像针孔的半影区投影又不影响本影区的投影，遮挡效果如图8、图9和图10所示。在图10中，成像探测器上的半影区 很小，几乎不会和相邻本影区发生交叠。发明人研究发现，当屏蔽通孔310的下边沿与第一孔段111的内壁所在环面的延长面与顶板300的下表面的交线重合时，也就是第一孔段111的内壁所在环面的延长面与顶板300的下表面相交所述形成的图形也就构成了屏蔽通孔310的下边沿，此时，遮光率小，半影区S 1的面积接近于零。
此外，需要说明的是，底板100和顶板300之间的距离，以及不同形状和尺寸的成像通孔110和屏蔽通孔310，可以根据不同的设计需求进行调整，具有很大的灵活性。从而，可选择性地对来自非目标器官的射线进行额外某些角度的投影进行额外遮挡，以屏蔽掉不想要或对图像质量有影响的数据，使探测器的探测效率和空间分辨率显著提高，重建图像质量更好。
如前所述，相对于现有的准直器，本公开实施例的准直器的等效厚度为底板100的底面到顶板300的顶面的距离，也就是等价于底板100的厚度、顶板300的厚度和底板100和顶板300之间的距离三者之和。根据公式(2)和所设定的遮光率S 1/S 2值求出D之后，两块平板之间的距离可以通过D减去第一平板的厚度和第二平板的厚度来确定。
在本公开的实施例中，底板100、顶板300和屏蔽件200可以由金、钽、铂、钨和铅中的至少一种形成的。
进一步，在本公开的优选实施例中，底板100、顶板300和屏蔽件200可以由相同的材料的形成。
在此，需要说明的是，底板100和顶板300的厚度需要保证不被射线穿透，如果射线能量为140keV，平板材料为钨，设定平板至少遮挡99.999％的射线，则平板的最低厚度T可以用如下公式求出，
Figure PCTCN2019085728-appb-000004
其中μ＝3.268mm -1，是材料钨对能量140keV光子的线性衰减系数。
相应地，根据本公开的实施例，顶板300和底板100的厚度均不小于3.5毫米。由此，能够有效地遮挡射线，防止被射线射穿。
同时，为了保证透过一个成像通孔110的射线只能到达一个对应的屏蔽通孔310，底板的厚度不能太薄。根据本公开的优选实施例，底板100的厚度为10-14毫米，顶板300的厚度为2-6毫米。由此，底部和顶部的厚度适宜，成像通孔的射线只能到达与之相对应的一个屏蔽通孔，遮光率更低，探测器的探测效率和空间分辨率显著提高，重建图像质量更好。
具体地，根据本公开的优选实施例，屏蔽通孔310的孔径为3-6毫米。根据本公开的优选实施例，屏蔽通孔310的孔径为4.5毫米。由此，屏蔽通孔的孔径适宜，成像通孔的射线只能到达与之相对应的一个屏蔽通孔，遮光率更低。
根据本公开的实施例，该准直器进一步包括支撑件500，该支撑件500设置在顶板300和底板100之间，用于支撑固定顶板300和底板100。
根据本公开的实施例，该支撑件500也可以由钨、铅、金、铂和钽的至少一种形成的。 进一步地，该支撑件500还可以与顶板300和底板100采用同种材料形成的。
探测器
在此基础上，本公开进一步提出了探测器。根据本公开的实施例，该探测器包括前述的准直器。由此，该探测器的探测效率和空间分辨率高，重建图像质量好。根据本公开的实施例，安装前述准直器的双探头SPECT可以无须旋转即对人体小器官进行断层成像和动态断层成像。其中，需要说明的是，该准直器具有前述准直器的全部技术特征和技术效果，在此不再一一赘述。
此外，需要说明的是，本公开实施例的探测器尤其适于对人体小器官为心脏、甲状腺或脑进行成像，但该探测器的用途不限于可以对人体小器官进行断层成像和动态断层成像，还可以对动物的一些器官和脏器进行断层成像和动态断层成像，以及其他可以用本公开实施例的探测器进行成像的目标物均可适用于本公开实施例的探测器。
根据本公开的实施例，探测器为可变角双探头SPECT。如图11所示，即为双探头SPECT对人体小器官进行成像的示意图。具有前述的准直器10的多针孔SPECT成像装置，两个探测器呈一定夹角放置，成像视野位于两个探测器的夹角之间，所有针孔可以覆盖一个足够包含心脏区域的球形视野。由此，该SPECT成像装置可以达到很高的灵敏度，例如，无需旋转即可对心脏实现快速断层成像，特别地，该装置还可以实现对心脏的动态成像。
在本说明书的描述中，参考术语“一个实施例”、“一些实施例”、“示例”、“具体示例”、或“一些示例”等的描述意指结合该实施例或示例描述的具体特征、结构、材料或者特点包含于本公开的至少一个实施例或示例中。在本说明书中，对上述术语的示意性表述不一定指的是相同的实施例或示例。而且，描述的具体特征、结构、材料或者特点可以在任何的一个或多个实施例或示例中以合适的方式结合。
尽管已经示出和描述了本公开的实施例，本领域的普通技术人员可以理解：在不脱离本公开的原理和宗旨的情况下可以对这些实施例进行多种变化、修改、替换和变型，本公开的范围由权利要求及其等同物限定。

Claims (12)

  1. 一种用于探测器的准直器，其中，包括：
    底板，所述底板上设置有呈阵列分布的成像通孔，所述成像通孔包含第一孔段和第二孔段，且所述第一孔段的横向尺寸沿自由端向所述第二孔段的方向逐渐减小，所述第二孔段的横向尺寸沿自由端向所述第一孔段的方向逐渐减小；
    屏蔽圈，所述屏蔽圈形成在所述底板上；以及
    顶板，所述顶板设置在所述屏蔽圈内，并封闭所述屏蔽圈的至少部分开口，且所述顶板上设置有呈阵列分布的屏蔽通孔，且所述成像通孔和所述屏蔽通孔一一对应设置。
  2. 根据权利要求1所述的准直器，其中，所述第一孔段和所述第二孔段在上下方向上对称设置。
  3. 根据权利要求1或2所述的准直器，其中，所述第一孔段和所述第二孔段独立地为圆台或多棱台。
  4. 根据权利要求1-3中任一项所述的准直器，其中，所述屏蔽通孔为直孔或斜孔。
  5. 根据权利要求1-4中任一项所述的准直器，其中，所述屏蔽通孔的下边沿与所述第一孔段的内壁所在环面的延长面与所述顶板的下表面的交线重合。
  6. 根据权利要求1-5中任一项所述的准直器，其中，所述准直器的遮光率不大于10％，其中，所述遮光率是基于下列公式确定的，
    Figure PCTCN2019085728-appb-100001
    其中，
    S 1代表所述准直器的半影区投影面积；
    S 2代表所述准直器的本影区投影面积；
    H代表所述成像通孔的中心到所述探测器表面的距离；
    α代表所述第一孔段和所述第二孔段的连接面的中点到所述第一孔段自由端的夹角；
    D代表所述成像通孔的最大孔径；
    T代表所述底板的底面到所述顶板的顶面的距离。
  7. 根据权利要求1-6中任一项所述的准直器，其中，所述顶板和所述底板的厚度均不小于3.5毫米。
  8. 根据权利要求1-6中任一项所述的准直器，其中，所述底板的厚度为10-14毫米，所述顶板的厚度为2-6毫米。
  9. 根据权利要求1-8中任一项所述的准直器，其中，所述屏蔽通孔的孔径为3-6毫米。
  10. 根据权利要求1-9中任一项所述的准直器，其中，所述屏蔽通孔的孔径为4.5毫米。
  11. 一种探测器，其中，包括权利要求1-10任一项所述的准直器。
  12. 根据权利要求11所述的探测器，其中，所述探测器为可变角双探头单光子发射计算机断层成像装置。
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