WO2022104684A1 - 一种多模态成像装置及其方法和多模态成像系统 - Google Patents

一种多模态成像装置及其方法和多模态成像系统 Download PDF

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Publication number
WO2022104684A1
WO2022104684A1 PCT/CN2020/130398 CN2020130398W WO2022104684A1 WO 2022104684 A1 WO2022104684 A1 WO 2022104684A1 CN 2020130398 W CN2020130398 W CN 2020130398W WO 2022104684 A1 WO2022104684 A1 WO 2022104684A1
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array
piezoelectric
layer
imaging device
ultrasonic transducer
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French (fr)
Inventor
马腾
张琪
柳正
杨永峰
黄继卿
李永川
邝忠华
郑海荣
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Shenzhen Institute of Advanced Technology of CAS
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Shenzhen Institute of Advanced Technology of CAS
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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
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves

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  • the present invention relates to the field of imaging technology, and more particularly, to a multimodal imaging device, a method thereof, and a multimodal imaging system.
  • positron emission tomography PET
  • CT Computed Tomography
  • MR Magnetic Resonance
  • US Ultrasonography
  • CT images, MR images and US images can provide morphological and structural information of the imaging site; PET images can provide metabolic and functional information of the imaging site.
  • Any existing modal imaging method has its own defects. Therefore, the fusion of medical image information from different modalities can achieve information complementation, poor verification, and effectively achieve early and accurate diagnosis.
  • the present invention provides a multi-modal imaging device, a method thereof, and a multi-modal imaging system, which effectively solve the technical problems existing in the prior art, and align the PET detector and the two-dimensional area array ultrasonic transducer. It is integrated in a multimodal imaging device to realize fusion imaging of multimodal images, thereby providing more imaging information.
  • a multimodal imaging device comprising: a PET detector and a two-dimensional area array ultrasonic transducer arranged in alignment;
  • the PET detector includes: a scintillation crystal array and a photodetector array coupled to the scintillation crystal array;
  • the two-dimensional area array ultrasonic transducer includes: a backing layer, a flexible circuit board, a piezoelectric array element array layer and a matching layer stacked in sequence; wherein, the flexible circuit board includes a pad part and at least one extension The pad part includes a plurality of connection pads arranged in an array, the extension part includes external leads connected to the connection pads in a one-to-one correspondence; the piezoelectric array element array layer includes an array of A plurality of piezoelectric array elements, the pad portion is located between the backing layer and the piezoelectric array element array layer, and the piezoelectric array elements are connected to the connection pads in a one-to-one correspondence.
  • the scintillation crystals of the scintillation crystal array are yttrium lutetium silicate scintillation crystals, lutetium fine silicate scintillation crystals, cerium-doped gadolinium gallium aluminum garnet scintillation crystals or bismuth germanate scintillation crystals.
  • the scintillation crystals of the scintillation crystal array are cuboid scintillation crystals.
  • the photodetectors of the photodetector array are position-sensitive photomultiplier tubes, avalanche photodiodes, silicon photomultiplier tubes or photomultiplier tubes.
  • the pad portion further includes an alignment structure, and the alignment structure is used for aligning the pad portion with the piezoelectric array element array layer.
  • the PET detector and/or the two-dimensional area array ultrasonic transducer further includes an alignment structure, and the alignment structure is used for the PET detector and the two-dimensional area array ultrasonic transducer. Counterpoint.
  • the alignment structure is a positioning hole and/or a positioning post.
  • the pad portion includes a plurality of sub-flexible layers stacked in sequence along the direction from the backing layer to the piezoelectric array element array layer.
  • the present invention also provides a multi-modal imaging method, using the above-mentioned multi-modal imaging device, the multi-modal imaging method includes:
  • PET detector to collect the first modal image of the object to be measured, and use the two-dimensional area array ultrasonic transducer to collect the second modal image of the object to be measured;
  • the first modal image and the second modal image are fused to form a multi-modal image.
  • the present invention also provides a multimodal imaging system, including the above multimodal imaging device.
  • the technical solution provided by the present invention has at least the following advantages:
  • the present invention provides a multimodal imaging device, a method thereof, and a multimodal imaging system, comprising: a PET detector and a two-dimensional area array ultrasonic transducer arranged in alignment;
  • the PET detector comprises: a scintillation crystal array and a photodetector array coupled to the scintillation crystal array;
  • the two-dimensional area array ultrasonic transducer includes: a backing layer, a flexible circuit board, a piezoelectric array element array layer and a matching layer stacked in sequence;
  • the flexible circuit board includes a pad portion and at least one extension portion, the pad portion includes a plurality of connection pads arranged in an array, and the extension portion includes an external connection connected to the connection pads in a one-to-one correspondence.
  • the PET detector and the two-dimensional area array ultrasonic transducer are aligned and integrated into a multi-modal imaging device, and based on the same spatial position and the same time point of the object to be measured, the PET detector collects the The modal image and the modal image collected by the two-dimensional area array ultrasonic transducer are fused to realize the fusion imaging of multi-modal images, thereby providing more imaging information.
  • FIG. 1 is a schematic structural diagram of a multimodal imaging device according to an embodiment of the present invention
  • FIG. 2 is a schematic structural diagram of a flexible circuit board provided by an embodiment of the present invention.
  • FIG. 3 is a schematic structural diagram of a PET detector provided by an embodiment of the present invention.
  • FIG. 4 is a schematic structural diagram of a two-dimensional area array ultrasonic transducer provided by an embodiment of the present invention.
  • FIG. 5 is a flowchart of a multimodal imaging method provided by an embodiment of the present invention.
  • positron emission tomography Positron Emission Tomography
  • PET Computed Tomography
  • CT Computed Tomography
  • MR Magnetic Resonance
  • US Ultrasonography
  • CT images, MR images and US images can provide morphological and structural information of the imaging site; PET images can provide metabolic and functional information of the imaging site.
  • Any existing modal imaging method has its own shortcomings. Therefore, the fusion of medical image information from different modalities can achieve information complementation, poor verification, and effectively achieve early and accurate diagnosis.
  • the embodiments of the present invention provide a multi-modal imaging device, a method thereof, and a multi-modal imaging system, which effectively solve the technical problems existing in the prior art. It is integrated into a multimodal imaging device to realize fusion imaging of multimodal images, thereby providing more imaging information.
  • FIG. 1 is a schematic structural diagram of a multi-modal imaging device provided by an embodiment of the present invention
  • FIG. 2 is a schematic structural schematic diagram of a flexible circuit board provided by an embodiment of the present invention.
  • the multimodal imaging device includes: a PET detector 100 and a two-dimensional area array ultrasonic transducer 200 arranged in alignment.
  • the PET detector 100 includes a scintillation crystal array 110 and a photodetector array 120 coupled to the scintillation crystal array 110 .
  • the two-dimensional area array ultrasonic transducer 200 includes: a backing layer 210, a flexible circuit board 220, a piezoelectric array element array layer 230 and a matching layer 240 stacked in sequence; wherein, the flexible circuit board 220 includes a welding The pad portion 221 and at least one extension portion 222, the pad portion 221 includes a plurality of connection pads 2211 arranged in an array, and the extension portion 222 includes external leads 2221 ( It should be noted that only part of the external lead is shown in FIG.
  • the piezoelectric array element array layer 230 includes a plurality of piezoelectric array elements arranged in an array, and the pad portion 221 is located on the backing layer 210 and the piezoelectric array element array layer 230, and the piezoelectric array elements are connected to the connection pads in a one-to-one correspondence.
  • the multimodal imaging device provided by the embodiment of the present invention further includes a package casing 300, and the package casing 300 is packaged and integrated with the PET detector 100 and the two-dimensional area array ultrasonic transducer 200 arranged in alignment.
  • the technical solution provided by the embodiment of the present invention integrates the PET detector and the two-dimensional area array ultrasonic transducer into the multi-modal imaging device, and based on the same spatial position and the same time point of the object to be measured, The modal images collected by the PET detector and the modal images collected by the two-dimensional area array ultrasonic transducer are fused to realize the fusion imaging of multi-modal images, thereby providing more imaging information.
  • the present invention does not specifically limit the alignment and placement relationship between the PET detector and the two-dimensional area array ultrasonic transducer included in the multimodal imaging device, wherein the PET detector and the two-dimensional area array
  • the ultrasonic transducer can be superimposed and aligned in the direction toward the object to be measured, or the PET detector and the two-dimensional area array ultrasonic transducer can be aligned side by side in the direction perpendicular to the object to be measured, or the PET detector can be positioned side by side.
  • the detector can be a ring detector, and the two-dimensional area array ultrasonic transducer is arranged in the hollow in the middle of the ring detector and nested, which needs to be specifically designed according to the actual application.
  • FIG. 3 it is a schematic structural diagram of a PET detector provided by an embodiment of the present invention, wherein the PET detector provided by the present invention includes a scintillation crystal array 110 , wherein an appropriate segmented scintillation crystal array is used, and the PET detector is detected according to the PET detector. Scanning requirements of the detector to achieve high-resolution PET detectors.
  • the shapes of the scintillation crystals of the scintillation crystal array provided by the embodiment of the present invention are not specifically limited; optionally, the scintillation crystals of the scintillation crystal array provided by the embodiment of the present invention are cuboid scintillation crystals, wherein The side length of the section can be 0.8mm-2mm and the length can be 10mm-30mm; specifically, the scintillation crystal provided by the embodiment of the present invention can be 1.01*1.01*10mm3 in size, wherein the scintillation crystal array can be a multi-row*multi-column array Arrangement, specifically 23 rows*23 columns.
  • the scintillation crystal provided by the embodiment of the present invention may adopt a material with high density, good time performance and high light output; wherein the scintillation crystal of the scintillation crystal array provided by the present invention may be a yttrium lutetium silicate scintillation crystal, which can The energy reception of high energy gamma photons is converted into multiple visible photons output.
  • the scintillation crystals of the scintillation crystal array provided by the embodiments of the present invention may be lutetium fine silicate scintillation crystals, cerium-doped gadolinium gallium aluminum garnet scintillation crystals or bismuth germanate scintillation crystals, which are not specifically limited in the present invention.
  • a photodetector array 120 is coupled to one end of the scintillation crystal array 110 .
  • the size of the photodetector of the photodetector array provided by the embodiment of the present invention may be 3*3 mm2, which is not specifically limited by the present invention, and other sizes may also be used, which need to be specifically designed according to factors such as resolution in practical applications.
  • the photodetector array provided by the embodiment of the present invention may be an array combination of multiple rows and multiple columns, specifically, 8 rows and 8 columns, and the detection effective area may reach 25.6*25.6 mm2.
  • the photodetector array provides the position information, energy information and time information of the detected gamma photons, and at the same time, the number of readout channels is reduced by adopting the method of scintillation crystal array light sharing and photodetector array readout signal encoding.
  • the discrete positioning method or the charge distribution method can be used to encode the multi-channel signal into fewer channels for acquisition.
  • the multi-channel signal can be encoded as 2* 2 of 4-channel signals;
  • the discrete positioning method provided in the embodiment of the present invention may be a resistance network readout method, and the charge distribution method may be a row-column addition readout method, which is not specifically limited by the present invention.
  • a resistance network readout method can be used to read out the photodetector array, wherein by optimizing the resistor combination and the channel connection of the photodetector array, the four signal paths of A1, B1, C1, and D1 are realized. Read out, where the calculation method for judging the position of the scintillation crystal satisfies:
  • X1 is to judge the position of the scintillation crystal in the x-axis direction
  • Y1 is to judge the position of the scintillation crystal in the y-axis direction
  • the total energy of the PET detector is:
  • E 1 A 1 +B 1 +C 1 +D 1
  • the photodetectors of the photodetector array provided by the present invention are position-sensitive photomultiplier tubes, avalanche photodiodes, silicon photomultiplier tubes or photomultiplier tubes.
  • FIG. 4 it is a schematic structural diagram of a two-dimensional area array ultrasonic transducer provided by an embodiment of the present invention, wherein the two-dimensional area array ultrasonic transducer provided by an embodiment of the present invention includes: backings stacked in sequence layer 210 , flexible circuit board 220 , piezoelectric array element array layer 230 and matching layer 240 .
  • the piezoelectric array element array layer 230 provided in the embodiment of the present invention may be arranged in a multi-row*multi-column array, and may specifically be a piezoelectric array element array layer with 22 rows*22 columns.
  • the area of the piezoelectric array element provided by the embodiment of the present invention can be consistent with the cross-sectional size of the scintillation crystal, thereby realizing more convenient alignment of the PET detector and the two-dimensional area array ultrasonic transducer in terms of spatial size. .
  • the material of the backing layer provided by the embodiment of the present invention may include epoxy resin, and may also include tungsten powder, alumina powder and other powders and epoxy resin to form a mixed material.
  • the piezoelectric array element array layer provided by the present invention may be a piezoelectric ceramic, a piezoelectric ceramic composite material, a pressure point single crystal material or a piezoelectric single crystal composite material.
  • the matching layer provided by the embodiment of the present invention is used to match the acoustic impedance matching between the two-dimensional area array ultrasonic transducer and the object to be measured, wherein the matching layer may be a single-layer structure, or the matching layer may also be a plurality of laminated structures .
  • the two-dimensional area array ultrasonic transducer also includes an acoustic metasurface located between the matching layer and the piezoelectric array element array layer or located on the side of the matching layer away from the backing layer, and the acoustic metasurface can also change the transmission characteristics of acoustic waves, Such as reflection focusing at any point, perfect low-frequency sound absorption, self-bending sound beam, spiral sound wave and asymmetric transmission of sound energy, etc., to further improve the detection performance of the two-dimensional area array ultrasonic transducer.
  • an acoustic metasurface located between the matching layer and the piezoelectric array element array layer or located on the side of the matching layer away from the backing layer, and the acoustic metasurface can also change the transmission characteristics of acoustic waves, Such as reflection focusing at any point, perfect low-frequency sound absorption, self-bending sound beam, spiral sound wave and asymmetric transmission of sound energy, etc., to further improve the detection performance of the two-dimensional area array ultrasonic transducer.
  • the pad portion provided by the embodiment of the present invention further includes an alignment structure, and the alignment structure is used for aligning the pad portion with the piezoelectric array element array layer, Furthermore, the precise alignment between the piezoelectric array elements and the connection pads is achieved through the alignment structure.
  • the alignment structure provided in the embodiment of the present invention may be an alignment line, and the present invention does not specifically limit the number and shape of the alignment line, for example, it may be four alignment lines.
  • the PET detector and/or the two-dimensional area array ultrasonic transducer provided by the embodiment of the present invention further includes an alignment structure, and the alignment structure is used for the PET detector and the two-dimensional area array ultrasonic transducer The transducer is aligned, and then the precise alignment between the PET detector and the two-dimensional area array ultrasonic transducer is achieved through the alignment structure, and a multimodal imaging device is obtained.
  • the alignment structure provided in the embodiment of the present invention is a positioning hole and/or a positioning post.
  • the alignment hole may be provided on the pad portion of the flexible circuit board, which is not specifically limited by the present invention.
  • the piezoelectric array element array layer provided by the present invention includes a large number of piezoelectric array elements, so more connection pads need to be arranged on the flexible circuit board.
  • the pad part includes a plurality of sub-flexible layers superimposed in sequence along the direction from the backing layer to the piezoelectric array element array layer, and through the arrangement of the plurality of sub-flexible layers, the design of more connection pads can be realized; as implemented in the present invention
  • the piezoelectric array element provided in the example is arranged in a 22-row*22-column array
  • the pad part includes connection pads arranged in a 22-row*22-column array
  • the pad part can include 8 sub-flexible layers to achieve
  • the setting of the 484 connection pads is not specifically limited in the present invention.
  • the number of extension parts provided by the embodiment of the present invention can be multiple, so as to avoid the problems of manufacturing difficulty and high circuit density caused by the concentration of external leads in one extension part; for example, the number of extension parts can be 4, and the extension part They are arranged in the four directions of the pad portion opposite each other, which is not specifically limited in the present invention.
  • the embodiment of the present invention also provides a multimodal imaging method.
  • FIG. 5 it is a flowchart of a multimodal imaging method provided by an embodiment of the present invention, wherein the multimodal imaging method adopts the multimodal imaging device provided in any of the foregoing embodiments, and the multimodal imaging method includes: :
  • the first modal image and the second modal image are fused to form a multi-modal image.
  • the multimodal images provided by the embodiments of the present invention are based on the same spatial position and the same time point of the object to be measured; that is, the first and second modal images are related to the same space of the object to be measured.
  • the image at the position and the image at the same time point are fused to ensure the consistency of the collection position and collection time of the object to be measured in the multimodal image.
  • the PET detector provided by the embodiment of the present invention injects a radioisotope-labeled compound into the organism as a tracer, then measures the radioactivity distribution information in the organism from different angles in vitro, and uses the processing device to complete the image reconstruction of the metabolite distribution.
  • Three-dimensional imaging; PET detectors are based on molecular level detection, which can effectively detect the spatiotemporal distribution of radioactive tracer atomic drugs injected into the organism, determine the nature and degree of deterioration of lesions, and provide functional and metabolic information.
  • the two-dimensional area array ultrasonic transducer uses the acoustic beam to scan the living body, and obtains the image of the living body structure through the reception and processing of the reflected signal, which accurately reflects the changes in the shape and structure of the diseased tissue.
  • a multi-modal image is obtained by fusing the first modal image collected by the PET detector with the second modal image collected by the two-dimensional area array ultrasonic transducer, so that the multi-modal image can reflect the shape of the living tissue.
  • structural changes can also reflect functional and metabolic information, thereby providing more diagnostic information.
  • an embodiment of the present invention further provides a multimodal imaging system, including the multimodal imaging device provided by any one of the above embodiments.
  • Embodiments of the present invention provide a multimodal imaging device, a method thereof, and a multimodal imaging system, including: a PET detector and a two-dimensional area array ultrasonic transducer arranged in alignment; the PET detector includes: a scintillation A crystal array and a photodetector array coupled to the scintillation crystal array; and the two-dimensional area array ultrasonic transducer includes: a backing layer, a flexible circuit board, a piezoelectric array element array layer and a matching layer stacked in sequence wherein the flexible circuit board includes a pad part and at least one extension part, the pad part includes a plurality of connection pads arranged in an array, and the extension part includes a one-to-one connection with the connection pads
  • the piezoelectric array element array layer includes a plurality of piezoelectric array elements arranged in an array, the pad portion is located between the backing layer and the piezoelectric array element array layer, and the The piezoelectric array elements are
  • the PET detector and the two-dimensional area array ultrasonic transducer are aligned and integrated into the multimodal imaging device, and based on the same spatial position and the same time point of the object to be measured, the PET detector is The acquired modal image and the modal image acquired by the two-dimensional area array ultrasonic transducer are fused to realize the fusion imaging of multi-modal images, thereby providing more imaging information.

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Abstract

一种多模态成像装置及其方法和多模态成像系统，包括PET探测器(100)和二维面阵超声换能器(200)；PET探测器(100)包括闪烁晶体阵列(110)和耦合于闪烁晶体阵列(110)上的光电探测器阵列(120)；二维面阵超声换能器(200)包括依次叠加的背衬层(210)、柔性线路板(220)、压电阵元阵列层(230)和匹配层(240)；柔性线路板(220)包括焊盘部(221)和至少一个延伸部(222)，焊盘部(221)包括阵列排布的多个连接焊盘(2211)，延伸部(222)包括与连接焊盘(2211)一一对应连接的外接引线(2221)；压电阵元阵列层(230)包括阵列排布的多个压电阵元，焊盘部(221)位于背衬层(210)与压电阵元阵列层(230)之间，且压电阵元与连接焊盘(2211)一一对应连接。将PET探测器(100)和二维面阵超声换能器(200)对位集成于多模态成像装置中，对PET探测器(100)采集的模态图像和二维面阵超声换能器(200)采集的模态图像融合。

Description

一种多模态成像装置及其方法和多模态成像系统 技术领域
本发明涉及成像技术领域，更为具体地说，涉及一种多模态成像装置及其方法和多模态成像系统。
背景技术
当前，各种模态的医学成像设备在临床诊断和医学研究中得到了广泛使用，这些多种模态的医学成像设备所涉及的影像技术主要包括正电子发射型断层成像(PositronEmission Computed Tomography，PET)、计算机断层扫描(Computed Tomography，CT)、磁共振成像(Magnetic Resonance，MR)、超声成像(Ultrasonography，US)等。
其中，CT图像、MR图像和US图像可提供成像部位的形态和结构信息；PET图像可提供成像部位的代谢和功能信息。现有任何一种模态的成像方式都存在自身的缺陷，因而，将不同模态医学图像信息融合，可以实现信息互补、较差验证，有效实现早期准确诊断。
发明内容
有鉴于此，本发明提供了一种多模态成像装置及其方法和多模态成像系统，有效解决现有技术存在的技术问题，将PET探测器和二维面阵超声换能器对位集成于多模态成像装置中，实现多模态图像的融合成像，从而能够提供更多成像信息。
为实现上述目的，本发明提供的技术方案如下：
一种多模态成像装置，包括：对位设置的PET探测器和二维面阵超声换能器；
所述PET探测器包括：闪烁晶体阵列和耦合于所述闪烁晶体阵列上的光电探测器阵列；
以及，所述二维面阵超声换能器包括：依次叠加的背衬层、柔性线路板、压电阵元阵列层和匹配层；其中，所述柔性线路板包括焊盘部和至少一个延伸 部，所述焊盘部包括阵列排布的多个连接焊盘，所述延伸部包括与所述连接焊盘一一对应连接的外接引线；所述压电阵元阵列层包括阵列排布的多个压电阵元，所述焊盘部位于所述背衬层与所述压电阵元阵列层之间，且所述压电阵元与所述连接焊盘一一对应连接。
可选的，所述闪烁晶体阵列的闪烁晶体为硅酸钇镥闪烁晶体、镥精细硅酸盐闪烁晶体、掺铈钆镓铝石榴石闪烁晶体或锗酸铋闪烁晶体。
可选的，所述闪烁晶体阵列的闪烁晶体为长方体闪烁晶体。
可选的，所述光电探测器阵列的光电探测器为位置灵敏型光电倍增管、雪崩光电二极管、硅光电倍增管或光电倍增管。
可选的，所述焊盘部还包括对准结构，所述对准结构用于所述焊盘部与所述压电阵元阵列层的对准。
可选的，所述PET探测器和/或二维面阵超声换能器还包括对位结构，所述对位结构用于所述PET探测器和所述二维面阵超声换能器的对位。
可选的，所述对位结构为定位孔和/或定位柱。
可选的，所述焊盘部包括沿背衬层至压电阵元阵列层方向依次叠加设置的多个子柔性层。
相应的，本发明还提供了一种多模态成像方法，采用上述的多模态成像装置，多模态成像方法包括：
采用所述PET探测器采集待测物体的第一模态图像，且采用所述二维面阵超声换能器采集所述待测物体的第二模态图像；
基于所述待测物体的相同空间位置及相同时间点，将所述第一模态图像和所述第二模态图像融合形成多模态图像。
相应的，本发明还提供了一种多模态成像系统，包括上述的多模态成像装置。
相较于现有技术，本发明提供的技术方案至少具有以下优点：
本发明提供了一种多模态成像装置及其方法和多模态成像系统，包括：对位设置的PET探测器和二维面阵超声换能器；所述PET探测器包括：闪烁晶体阵列和耦合于所述闪烁晶体阵列上的光电探测器阵列；以及，所述二维面阵超声换能器包括：依次叠加的背衬层、柔性线路板、压电阵元阵列层和匹配层； 其中，所述柔性线路板包括焊盘部和至少一个延伸部，所述焊盘部包括阵列排布的多个连接焊盘，所述延伸部包括与所述连接焊盘一一对应连接的外接引线；所述压电阵元阵列层包括阵列排布的多个压电阵元，所述焊盘部位于所述背衬层与所述压电阵元阵列层之间，且所述压电阵元与所述连接焊盘一一对应连接。本发明提供的技术方案，将PET探测器和二维面阵超声换能器对位集成于多模态成像装置中，并且基于待测物体相同空间位置及相同时间点，对PET探测器采集的模态图像和二维面阵超声换能器采集的模态图像融合，实现多模态图像的融合成像，从而能够提供更多成像信息。
附图说明
图1为本发明实施例提供的一种多模态成像装置的结构示意图；
图2为本发明实施例提供的一种柔性线路板的结构示意图；
图3为本发明实施例提供的一种PET探测器的结构示意图；
图4为本发明实施例提供的一种二维面阵超声换能器的结构示意图；
图5为本发明实施例提供的一种多模态成像方法的流程图。
具体实施方式
下面将结合本发明实施例中的附图，对本发明实施例中的技术方案进行清楚、完整地描述，显然，所描述的实施例仅仅是本发明一部分实施例，而不是全部的实施例。基于本发明中的实施例，本领域普通技术人员在没有做出创造性劳动前提下所获得的所有其他实施例，都属于本发明保护的范围。
正如背景技术所述，各种模态的医学成像设备在临床诊断和医学研究中得到了广泛使用，这些多种模态的医学成像设备所涉及的影像技术主要包括正电子发射型断层成像(PositronEmission Computed Tomography，PET)、计算机断层扫描(Computed Tomography，CT)、磁共振成像(Magnetic Resonance，MR)、超声成像(Ultrasonography，US)等。
其中CT图像、MR图像和US图像可提供成像部位的形态和结构信息；PET图像可提供成像部位的代谢和功能信息。现有任何一种模态的成像方式都存在 自身的缺陷，因而，将不同模态医学图像信息融合，可以实现信息互补、较差验证，有效实现早期准确诊断。
基于此，本发明实施例提供了一种多模态成像装置及其方法和多模态成像系统，有效解决现有技术存在的技术问题，将PET探测器和二维面阵超声换能器对位集成于多模态成像装置中，实现多模态图像的融合成像，从而能够提供更多成像信息。
为实现上述目的，本发明实施例提供的技术方案如下，具体结合图1至图5对本发明实施例提供的技术方案进行详细的描述。
结合图1和图2所示，图1为本发明实施例提供的一种多模态成像装置的结构示意图，图2为本发明实施例提供的一种柔性线路板的结构示意图。其中，多模态成像装置包括：对位设置的PET探测器100和二维面阵超声换能器200。
所述PET探测器100包括：闪烁晶体阵列110和耦合于所述闪烁晶体阵列110上的光电探测器阵列120。
以及，所述二维面阵超声换能器200包括：依次叠加的背衬层210、柔性线路板220、压电阵元阵列层230和匹配层240；其中，所述柔性线路板220包括焊盘部221和至少一个延伸部222，所述焊盘部221包括阵列排布的多个连接焊盘2211，所述延伸部222包括与所述连接焊盘2211一一对应连接的外接引线2221(需要说明的是，图2中仅仅示出部分外接引线)；所述压电阵元阵列层230包括阵列排布的多个压电阵元，所述焊盘部221位于所述背衬层210与所述压电阵元阵列层230之间，且所述压电阵元与所述连接焊盘一一对应连接。
进一步的，本发明实施例提供的多模态成像装置还包括有封装壳体300，封装壳体300将对位设置的PET探测器100和二维面阵超声换能器200封装集成于一体。
可以理解的，本发明实施例提供的技术方案，将PET探测器和二维面阵超声换能器对位集成于多模态成像装置中，并且基于待测物体相同空间位置及相同时间点，对PET探测器采集的模态图像和二维面阵超声换能器采集的模态图像融合，实现多模态图像的融合成像，从而能够提供更多成像信息。
在本发明一实施例中，本发明对多模态成像装置所包括的PET探测器和二维面阵超声换能器的对位放置关系不做具体限制，其中PET探测器和二维面阵超声换能器可以在朝向待测物体方向上叠加对位设置，或者，PET探测器和二维面阵超声换能器可以在垂直朝向待测物体方向的方向上并排对位设置，或者PET探测器可以为环形探测器，而将二维面阵超声换能器设置于环形探测器中间镂空处嵌套设置，对此需要根据实际应用具体进行设计。
如图3所示，为本发明实施例提供的一种PET探测器的结构示意图，其中，本发明提供的PET探测器包括闪烁晶体阵列110，其中采用合适的分割闪烁晶体阵列，且根据PET探测器的扫描需求，以实现高分辨率的PET探测器。其中本发明实施例提供的闪烁晶体阵列的闪烁晶体的形状不做具体限制；可选的，本发明实施例提供的所述闪烁晶体阵列的闪烁晶体为长方体闪烁晶体，其中长方体形状的闪烁晶体的截面边长可以为0.8mm-2mm且长度可以为10mm-30mm；具体的，本发明实施例提供的闪烁晶体可以为1.01*1.01*10mm3的尺寸，其中闪烁晶体阵列可以为多行*多列阵列排布，具体可以为23行*23列。以及，本发明实施例提供的闪烁晶体可以采用高密度、时间性能好且光输出高的材质；其中本发明提供的所述闪烁晶体阵列的闪烁晶体可以为硅酸钇镥闪烁晶体，其可以将高能量的伽马光子的能量接收转化为多个可见光子输出。或者，本发明实施例提供的闪烁晶体阵列的闪烁晶体可以为镥精细硅酸盐闪烁晶体、掺铈钆镓铝石榴石闪烁晶体或锗酸铋闪烁晶体，对此本发明不做具体限制。
如图3所示，在闪烁晶体阵列110的一端耦合有光电探测器阵列120。本发明实施例提供的光电探测器阵列的光电探测器的尺寸可以为3*3mm2，对此本发明不做具体限制，还可以采用其他尺寸，需要根据实际应用时分辨率等影响因素具体设计。本发明实施例提供的光电探测器阵列可以为多行*多列的阵列组合，具体可以为8行*8列，探测有效面积可以达到25.6*25.6mm2。其中，光电探测器阵列提供探测到的伽马光子的位置信息、能量信息和时间信息，同时通过采用闪烁晶体阵列光分享和光电探测器阵列读出信号编码的方法降低读出通道数。
具体的，本发明实施例提供的光电探测器阵列的编码读出方法可以采用离散定位法或电荷分配法将多路信号编码为更少路后进行采集，一般可以将多路信号编码为2*2的4路信号；其中本发明实施例提供的离散定位法可以为电阻网络读出方法，电荷分配法可以为行列相加读出方法，对此本发明不做具体限制。如，本发明实施例可以采用电阻网络读出方法，对光电探测器阵列进行读出，其中通过优化电阻组合与光电探测器阵列的通道连接，实现A1、B1、C1、D1四个信号通路的读出，其中判断闪烁晶体位置的计算方法满足：
Figure PCTCN2020130398-appb-000001
Figure PCTCN2020130398-appb-000002
其中，X1为判断闪烁晶体在x轴方向上的位置，Y1为判断闪烁晶体在y轴方向上的位置，及PET探测器的总能量为：
E 1＝A 1+B 1+C 1+D 1
在本发明一实施例中，本发明所提供的所述光电探测器阵列的光电探测器为位置灵敏型光电倍增管、雪崩光电二极管、硅光电倍增管或光电倍增管。
如图4所示，为本发明实施例提供的一种二维面阵超声换能器的结构示意图，其中，本发明实施例提供的二维面阵超声换能器包括：依次叠加的背衬层210、柔性线路板220、压电阵元阵列层230和匹配层240。其中，本发明实施例提供的压电阵元阵列层230可以为多行*多列阵列排布，具体可以为22行*22列的压电阵元阵列层。可选的，本发明实施例提供的压电阵元的面积与闪烁晶体的截面尺寸可以保持一致，进而实现PET探测器和二维面阵超声换能器在空间尺寸上实现更便捷的对位。
在本发明一实施例中，本发明实施例提供的所述背衬层的材质可以包括环氧树脂，其还可以包括钨粉、氧化铝粉等粉末与环氧树脂形成混合材料。以及，本发明提供的压电阵元阵列层可以为压电陶瓷、压电陶瓷复合材质、压点单晶材质或压电单晶复合材质。
本发明实施例提供的匹配层用于匹配二维面阵超声换能器与待测物体之间的声阻抗匹配，其中匹配层可以为单层结构，或者匹配层还可以为多个叠层结构。进一步二维面阵超声换能器还包括位于匹配层与压电阵元阵列层之间或位于匹配层背离背衬层一侧的声学超构表面，声学超构表面还能够改变声波的传输特性，如任意点反射聚焦、低频完美吸声、自弯曲声束、螺旋声波以及声能量非对称传输等，进一步提高二维面阵超声换能器的探测性能。
在本发明一实施例中，本发明实施例提供的所述焊盘部还包括对准结构，所述对准结构用于所述焊盘部与所述压电阵元阵列层的对准，进而通过对准结构实现压电阵元与连接焊盘之间的精确对准。可选的，本发明实施例提供的对准结构可以为对准线，且本发明对于对准线的数量和形状不做具体限制，如可以为4条对准线。
以及，本发明实施例提供的所述PET探测器和/或二维面阵超声换能器还包括对位结构，所述对位结构用于所述PET探测器和所述二维面阵超声换能器的对位，进而通过对位结构实现PET探测器和二维面阵超声换能器之间的精准对位，得到多模态成像装置。可选的，本发明实施例提供的所述对位结构为定位孔和/或定位柱，如可以将对位孔设置于柔性线路板的焊盘部，对此本发明不做具体限制。
在本发明一实施例中，本发明提供的压电阵元阵列层包括的压电阵元数量较大，因此需要在柔性线路板上设置更多的连接焊盘，其中，本发明实施例通过的所述焊盘部包括沿背衬层至压电阵元阵列层方向依次叠加设置的多个子柔性层，进而通过多个子柔性层的设置，实现更多连接焊盘的设计；如本发明实施例提供的压电阵元阵列层为22行*22列阵列排布时，焊盘部则包括22行*22列阵列排布的连接焊盘，其中焊盘部可以包括8个子柔性层来实现484连接焊盘的设置，对此本发明不做具体限制。此外，本发明实施例提供的延伸部的数量可以为多个，进而避免外接引线集中于一个延伸部而出现制作难度、线路密度较大的问题；如延伸部的数量可以为4个，延伸部两两相对设置于焊盘部的四个方向，对此本发明不做具体限制。
相应的，本发明实施例还提供了一种多模态成像方法。如图5所述，为本发明实施例提供的一种多模态成像方法的流程图，其中多模态成像方法采用上述任意一实施例提供的多模态成像装置，多模态成像方法包括：
S1、采用所述PET探测器采集待测物体的第一模态图像，且采用所述二维面阵超声换能器采集所述待测物体的第二模态图像。
S2、基于所述待测物体的相同空间位置及相同时间点，将所述第一模态图像和所述第二模态图像融合形成多模态图像。
可以理解的，本发明实施例提供的多模态图像为基于待测物体的相同空间位置及相同时间点；也就是说，将第一模态图像和第二模态图像关于待测物体相同空间位置处图像及相同时间点处图像相融合，保证多模态图像中关于待测物体的采集位置和采集时间的一致性。
其中，本发明实施例提供的PET探测器是将放射性同位素标记的化合物作为示踪剂注入生物体，然后在体外从不同角度测量生物体内放射性分布信息，并利用处理装置完成代谢物分布图像重建的三维成像；PET探测器是基于分子水平探测，可以有效探测到注入生物体内的标记了放射性示踪原子药物的时空分布，确定病变性质及恶化程度，其可以提供功能与代谢信息。而二维面阵超声换能器则是利用声波束扫描生物体，通过反射信号的接收和处理，获得生物体结构的图像，精准地反映病变组织形态、结构的改变。本发明实施例通过将PET探测器采集的第一模态图像与二维面阵超声换能器采集的第二模态图像融合得到多模态图像，使得多模态图像既能够反映生体组织形态、结构的改变，还能够反映功能与代谢信息，进而提供了更多的诊断信息。
相应的，本发明实施例还提供了一种多模态成像系统，包括上述任意一实施例提供的多模态成像装置。
本发明实施例提供了一种多模态成像装置及其方法和多模态成像系统，包括：对位设置的PET探测器和二维面阵超声换能器；所述PET探测器包括：闪 烁晶体阵列和耦合于所述闪烁晶体阵列上的光电探测器阵列；以及，所述二维面阵超声换能器包括：依次叠加的背衬层、柔性线路板、压电阵元阵列层和匹配层；其中，所述柔性线路板包括焊盘部和至少一个延伸部，所述焊盘部包括阵列排布的多个连接焊盘，所述延伸部包括与所述连接焊盘一一对应连接的外接引线；所述压电阵元阵列层包括阵列排布的多个压电阵元，所述焊盘部位于所述背衬层与所述压电阵元阵列层之间，且所述压电阵元与所述连接焊盘一一对应连接。本发明实施例提供的技术方案，将PET探测器和二维面阵超声换能器对位集成于多模态成像装置中，并且基于待测物体相同空间位置及相同时间点，对PET探测器采集的模态图像和二维面阵超声换能器采集的模态图像融合，实现多模态图像的融合成像，从而能够提供更多成像信息。
对所公开的实施例的上述说明，使本领域专业技术人员能够实现或使用本发明。对这些实施例的多种修改对本领域的专业技术人员来说将是显而易见的，本文中所定义的一般原理可以在不脱离本发明的精神或范围的情况下，在其它实施例中实现。因此，本发明将不会被限制于本文所示的这些实施例，而是要符合与本文所公开的原理和新颖特点相一致的最宽的范围。

Claims (10)

  1. 一种多模态成像装置，其特征在于，包括：对位设置的PET探测器和二维面阵超声换能器；
    所述PET探测器包括：闪烁晶体阵列和耦合于所述闪烁晶体阵列上的光电探测器阵列；
    以及，所述二维面阵超声换能器包括：依次叠加的背衬层、柔性线路板、压电阵元阵列层和匹配层；其中，所述柔性线路板包括焊盘部和至少一个延伸部，所述焊盘部包括阵列排布的多个连接焊盘，所述延伸部包括与所述连接焊盘一一对应连接的外接引线；所述压电阵元阵列层包括阵列排布的多个压电阵元，所述焊盘部位于所述背衬层与所述压电阵元阵列层之间，且所述压电阵元与所述连接焊盘一一对应连接。
  2. 根据权利要求1所述的多模态成像装置，其特征在于，所述闪烁晶体阵列的闪烁晶体为硅酸钇镥闪烁晶体、镥精细硅酸盐闪烁晶体、掺铈钆镓铝石榴石闪烁晶体或锗酸铋闪烁晶体。
  3. 根据权利要求1所述的多模态成像装置，其特征在于，所述闪烁晶体阵列的闪烁晶体为长方体闪烁晶体。
  4. 根据权利要求1所述的多模态成像装置，其特征在于，所述光电探测器阵列的光电探测器为位置灵敏型光电倍增管、雪崩光电二极管、硅光电倍增管或光电倍增管。
  5. 根据权利要求1所述的多模态成像装置，其特征在于，所述焊盘部还包括对准结构，所述对准结构用于所述焊盘部与所述压电阵元阵列层的对准。
  6. 根据权利要求1所述的多模态成像装置，其特征在于，所述PET探测器和/或二维面阵超声换能器还包括对位结构，所述对位结构用于所述PET探测器和所述二维面阵超声换能器的对位。
  7. 根据权利要求1所述的多模态成像装置，其特征在于，所述对位结构为定位孔和/或定位柱。
  8. 根据权利要求1所述的多模态成像装置，其特征在于，所述焊盘部包括沿背衬层至压电阵元阵列层方向依次叠加设置的多个子柔性层。
  9. 一种多模态成像方法，其特征在于，采用权利要求1-8任意一项所述的多模态成像装置，多模态成像方法包括：
    采用所述PET探测器采集待测物体的第一模态图像，且采用所述二维面阵超声换能器采集所述待测物体的第二模态图像；
    基于所述待测物体的相同空间位置及相同时间点，将所述第一模态图像和所述第二模态图像融合形成多模态图像。
  10. 一种多模态成像系统，其特征在于，包括权利要求1-8任意一项所述的多模态成像装置。
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US6587710B1 (en) * 1999-06-06 2003-07-01 Elgems Ltd. Hand-held gamma camera
EP1269916A1 (en) * 2001-06-21 2003-01-02 Anzai Medical Kabushiki Kaisha Medical hybrid imaging apparatus
CN101569536A (zh) * 2008-04-29 2009-11-04 上海爱培克电子科技有限公司 一种超声换能器的制造方法
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