CN110441811B - PET detector and medical imaging equipment with same - Google Patents
PET detector and medical imaging equipment with same Download PDFInfo
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- CN110441811B CN110441811B CN201910767830.XA CN201910767830A CN110441811B CN 110441811 B CN110441811 B CN 110441811B CN 201910767830 A CN201910767830 A CN 201910767830A CN 110441811 B CN110441811 B CN 110441811B
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- 238000002059 diagnostic imaging Methods 0.000 title claims abstract description 15
- 239000013078 crystal Substances 0.000 claims abstract description 84
- 239000000758 substrate Substances 0.000 claims description 9
- 239000000498 cooling water Substances 0.000 claims description 8
- 230000003287 optical effect Effects 0.000 claims description 8
- 239000003292 glue Substances 0.000 claims description 6
- 239000011248 coating agent Substances 0.000 claims description 5
- 238000000576 coating method Methods 0.000 claims description 5
- 238000004891 communication Methods 0.000 claims description 4
- 238000003384 imaging method Methods 0.000 description 4
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 description 4
- 241001465754 Metazoa Species 0.000 description 3
- 239000002826 coolant Substances 0.000 description 3
- 210000003484 anatomy Anatomy 0.000 description 2
- 230000000903 blocking effect Effects 0.000 description 2
- 238000006243 chemical reaction Methods 0.000 description 2
- 238000010586 diagram Methods 0.000 description 2
- 230000005611 electricity Effects 0.000 description 2
- 230000017525 heat dissipation Effects 0.000 description 2
- 238000000034 method Methods 0.000 description 2
- 229910021418 black silicon Inorganic materials 0.000 description 1
- 238000001816 cooling Methods 0.000 description 1
- 238000005260 corrosion Methods 0.000 description 1
- 230000007797 corrosion Effects 0.000 description 1
- 230000008878 coupling Effects 0.000 description 1
- 230000001808 coupling effect Effects 0.000 description 1
- 238000010168 coupling process Methods 0.000 description 1
- 238000005859 coupling reaction Methods 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 239000003973 paint Substances 0.000 description 1
- 238000002600 positron emission tomography Methods 0.000 description 1
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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
- A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
- A61B6/03—Computed tomography [CT]
- A61B6/037—Emission tomography
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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
- A61B6/42—Arrangements for detecting radiation specially adapted for radiation diagnosis
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- 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
- G01T1/2985—In depth localisation, e.g. using positron emitters; Tomographic imaging (longitudinal and transverse section imaging; apparatus for radiation diagnosis sequentially in different planes, steroscopic radiation diagnosis)
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- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
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Abstract
The invention provides a PET detector and a medical imaging device with the same, which comprises a crystal array, a photoelectric converter and a reading circuit, wherein the crystal array is optically coupled with the photoelectric converter, the photoelectric converter is arranged on a photoelectric converter array plate, the reading circuit is arranged on a reading circuit board, the photoelectric converter array plate is electrically connected with the reading circuit board, the crystal array comprises a plurality of crystals, the crystal extension direction is determined from the gamma photon incident surface of the crystal to the direction of the crystal end surface opposite to the incident surface, the straight line passing through the crystal array along the crystal extension direction does not pass through the reading circuit board, compared with the prior art, the straight line passing through the crystal array along the crystal extension direction does not pass through the reading circuit board, namely, the reading circuit board is arranged in the non-upper or lower area of the crystal array, so that when the PET detector is arranged between an outer cylinder and an inner cylinder, the occupation of the PET detector to the radial size space between the outer cylinder and the inner cylinder can be effectively reduced.
Description
Technical Field
The invention relates to the field of medical images, in particular to a PET detector and medical imaging equipment with the same.
Background
Pet (positron Emission tomography) is a functional imaging device, often combined with structural imaging devices (e.g., CT, MR, etc.) to form a multi-modality imaging device. The PET detector is one of important components of a PET apparatus, and is used for receiving X-rays transmitted through a certain part of a human body or an animal, converting the X-rays transmitted through the layer into visible light, converting the visible light into an electrical signal by photoelectric conversion, converting the electrical signal into a digital signal by an analog/digital converter (analog/digital converter), and inputting the digital signal into a computer for processing to form a CT image. At present, a PET detector structure generally adopts a layered structure, that is, a crystal array, a photoelectric conversion device (circuit board), a cooling (supporting) structural member, a rear-end readout circuit, and the like are sequentially layered to form a detector module.
However, for small PET devices, the layered structure of the existing detector modules occupies a large radial space inside the gantry when the detector modules are installed in the gantry, so as to affect the size of the aperture of the gantry, and thus the quality of image reconstruction.
Disclosure of Invention
The invention provides a PET detector and medical imaging equipment with the same, which are used for solving the technical problem that when an existing detector module is installed in a rack in the prior art, a layered structure of the detector module occupies a larger radial space in the rack to influence the aperture size of the rack, so that the image reconstruction quality is influenced.
In order to solve the technical problems, the invention adopts the following technical scheme:
the utility model provides a PET detector, includes crystal array, photoelectric converter and reading circuit, the crystal array with photoelectric converter optical coupling, photoelectric converter sets up on photoelectric converter array board, reading circuit sets up on reading circuit board, photoelectric converter array board with reading circuit board electricity is connected, the crystal array includes a plurality of crystals, follow the gamma photon incident surface of crystal is confirmed with the direction of the relative crystal terminal surface of incident surface the crystal extension direction, follows crystal extension direction and process the straight line of crystal array does not pass through reading circuit board.
In one embodiment, the photoelectric converter array board and the readout circuit board are electrically connected by a flexible printed circuit board.
In one embodiment, the photoelectric converter array plate is arranged perpendicular to the crystal extending direction.
In one embodiment, the photoelectric converter array board is disposed on one side of the crystal end face of the crystal array.
In one embodiment, the PET detector further comprises a first cooler thermally coupled directly to the readout circuit board and a second cooler thermally coupled to the photoelectric converter array board.
In one embodiment, the first cooler comprises a cold plate and a cooling water pipe communicated with the cold plate, and the second cooler comprises at least one heat pipe, and the heat pipe is in thermal communication with the first cooler.
In one embodiment, the outer surface of the crystal array is provided with a light blocking coating.
In one embodiment, the crystal array is fixedly connected or detachably connected with the photoelectric converter array plate.
In one embodiment, the crystal array is fixedly connected with the photoelectric converter through optical glue.
The invention also provides the following technical scheme:
a medical imaging device comprises a sickbed, a rack and the PET detector arranged in the rack.
Compared with the prior art, the PET detector and the medical imaging equipment with the same provided by the invention have the following advantages:
the straight line which is along the crystal extension direction and passes through the crystal array does not pass through the reading circuit board, namely the reading circuit board is placed in the non-upper or lower area of the crystal array, so that when the PET detector is installed between the outer cylinder and the inner cylinder, the occupation of the PET detector on the radial dimension space between the outer cylinder and the inner cylinder can be effectively reduced.
Drawings
The following drawings are only for better understanding of the technical solutions of the present invention by those skilled in the art, and are not intended to limit the present invention, and other drawings may be obtained by those skilled in the art according to the technical solutions of the present invention.
Fig. 1 is a schematic structural diagram of a medical imaging apparatus according to an embodiment of the present invention;
fig. 2 is a first schematic view of another perspective of a medical imaging apparatus according to an embodiment of the present invention;
fig. 3 is a schematic structural diagram of another view angle of the medical imaging apparatus according to an embodiment of the present invention.
Description of reference numerals:
100. a medical imaging device; 10. a frame; 11. an inner barrel; 12. an outer cylinder; 20. a PET detector; 21. an array of crystals; 211. a crystal; 212. a gamma photon incident surface; 22. a photoelectric converter; 23. a readout circuit; 24. a photoelectric converter array board; 25. a readout circuit board; 26. a flexible printed circuit board; 27. a first cooler; 271. a cold plate; 272. a cooling water pipe; 28. a second cooler; 281. a heat pipe; 29. a substrate.
Detailed Description
The technical solutions in the embodiments of the present invention will be clearly and completely described below with reference to the drawings in the embodiments of the present invention, and it is obvious that the described embodiments are only a part of the embodiments of the present invention, and not all of the embodiments. All other embodiments, which can be derived by a person skilled in the art from the embodiments given herein without making any creative effort, shall fall within the protection scope of the present invention.
For a better description and illustration of embodiments of the application, reference may be made to one or more of the drawings, but additional details or examples used in describing the drawings should not be construed as limiting the scope of any of the inventive concepts of the present application, the presently described embodiments, or the preferred versions.
It will be understood that when an element is referred to as being "connected" to another element, it can be directly connected to the other element or intervening elements may also be present. When a component is referred to as being "disposed on" another component, it can be directly on the other component or intervening components may also be present.
Unless defined otherwise, all technical and scientific terms used herein have the same meaning as commonly understood by one of ordinary skill in the art to which this invention belongs. The terminology used in the description of the invention herein is for the purpose of describing particular embodiments only and is not intended to be limiting of the invention. As used herein, the term "or/and" includes any and all combinations of one or more of the associated listed items.
As shown in fig. 1 and 2, the present invention provides a medical imaging apparatus 100, wherein the medical imaging apparatus 100 is mainly used for imaging human or animal anatomy structures to obtain medical image information of a detected object.
Specifically, the medical imaging apparatus 100 includes a patient table (not shown), a gantry 10, and a PET detector 20 disposed in the gantry 10. The rack 10 comprises an inner cylinder 11 and an outer cylinder 12, the inner cylinder 11 is sleeved in the outer cylinder 12, the PET detector 20 is arranged between the inner cylinder 11 and the outer cylinder 12, and the inner cylinder 11 is provided with a mounting hole (not shown) for accommodating an anatomical structure of a human body or an animal.
The inner cylinder 11 and the outer cylinder 12 are both substantially cylindrical, and the outer cylinder 12 is used for mounting the inner cylinder 11. Preferably, the axis of the inner cylinder 11 and the axis of the outer cylinder 12 are substantially coincident.
Further, as shown in fig. 3, the PET detector 20 includes a crystal array 21, a photoelectric converter 22, and a readout circuit 23, the crystal array 21 is optically coupled to the photoelectric converter 22, the photoelectric converter 22 is disposed on a photoelectric converter array board 24, the readout circuit 23 is disposed on a readout circuit board 25, and the photoelectric converter array board 24 is electrically connected to the readout circuit board 25.
It is understood that the gamma photon incident surface 212 on the crystal array 21 is disposed toward the mounting hole, the crystal array 21 receives gamma photons and transmits the gamma photons (not shown) to the photoelectric converter 22, the photoelectric converter 22 receives the gamma photons and processes the gamma photons to convert the gamma photons into photoelectric signals, the photoelectric signals are transmitted to the readout circuit 23, and the readout circuit 23 receives and converts the photoelectric signals into digital signals, thereby outputting an image.
Further, as shown in fig. 3, the crystal array 21 includes a plurality of crystals 211, a direction from a gamma photon incident surface 212 of the crystals 211 to a crystal end surface (not labeled) opposite to the incident surface 212 determines an extending direction of the crystals 211, and a straight line passing through the crystal array 21 along the extending direction of the crystals 211 does not pass through the readout circuit board 25.
It can be understood that the straight line along the extending direction of the crystal 211 and passing through the crystal array 21 does not pass through the readout circuit board 25, that is, the readout circuit board 25 is disposed in a non-upper or lower region of the crystal array 21, so that when the PET detector 20 is installed between the outer cylinder 12 and the inner cylinder 11, the occupation of the radial dimension space between the outer cylinder 12 and the inner cylinder 11 by the PET detector 20 can be effectively reduced.
In the present embodiment, the PET detector 20 further includes a substrate 29, the substrate 29 being disposed between the outer cylinder 12 and the inner cylinder 11 in the axial direction of the gantry 10; the crystal array 21, the readout circuit 23, and the photoelectric converter 22 are disposed on the substrate 29, the readout circuit 23 and the crystal array 21 are disposed on the substrate 29 at an interval, and when the PET detector 20 is mounted on the gantry 10, the PET detector 20 occupies a space having a radial dimension between the outer cylinder 12 and the inner cylinder 11.
Further, the outer surface of the crystal array 21 is provided with a light-shielding coating (not shown).
It will be appreciated that the crystal array 21 is shaded by applying a shading paint to the outer surface of the gel crystal array 21. The thickness of the shading coating is thin, so that the occupation of the radial dimension space between the outer cylinder 12 and the inner cylinder 11 by the PET detector 20 can be further reduced.
Preferably, the light blocking coating is a black silicon layer.
Further, the photoelectric converter array board 24 and the readout circuit board 25 are electrically connected by a flexible printed circuit board 26.
It is understood that the photoelectric converter array board 24 and the readout circuit board 25 are electrically connected through the flexible printed circuit board 26, so that data, signals, electricity and the like can be transmitted between the photoelectric converter 22 and the readout circuit 23 through the flexible printed circuit board 26, the photoelectric converter 22 transmits signals to the readout circuit 23 through the flexible printed circuit board 26, the photoelectric signal is converted into a digital signal, and the readout circuit board 25 supplies power to the photoelectric converter array board 24 through the flexible printed circuit board 26.
In the present embodiment, the flexible printed circuit board 26 is a flexible PCB board. Of course, in other embodiments, the flexible printed circuit board 26 may also be a connector, a connector + cable combination, or the like.
Further, the photoelectric converter array plate 24 is disposed in a direction perpendicular to the direction in which the crystal 211 extends. It can be understood that the photoelectric converter array plate 24 is arranged along a direction perpendicular to the extending direction of the crystal 211, that is, the photoelectric converter array plate 24 is not installed in the radial direction of the crystal 211, which not only can effectively reduce the occupation of the PET detector 20 on the radial dimension space between the outer cylinder 12 and the inner cylinder 11; at the same time, the mounting between the crystal array 21 and the photoelectric converter array board 24 can be facilitated.
Preferably, the photoelectric converter array plate 24 is disposed at the gamma photon incident surface 212 and a crystal end surface opposite to the incident surface.
Further, in an embodiment, the crystal array 21 is fixedly connected to the photoelectric converter array board 24.
Preferably, the crystal array 21 may be fixed on the photoelectric converter array board by optical glue, so that the fixed connection between the crystal array 21 and the photoelectric converter array board 24 is realized. It can be understood that, by using optical glue for fixing, the crystal array 21 can be prevented from being fixed on the photoelectric converter array plate 24 by a side clamping and fixing structure, so that the increase of the radial gap between the outer cylinder 12 and the inner cylinder 11 due to the fixing structure between the crystal array 21 and the photoelectric converter array plate 24 is avoided, and the occupation of the PET detector 20 on the radial dimension space between the outer cylinder 12 and the inner cylinder 11 is further avoided.
In another embodiment, the crystal array 21 and the photoelectric converter array plate 24 can be detachably connected, so as to facilitate the assembly and disassembly of the crystal array 21 and the photoelectric converter array plate 24.
In this embodiment, the crystal array 21 is fixedly connected to the photoelectric converter 22 by an optical glue (not shown).
It can be understood that, the crystal array 21 is bonded to the photoelectric converter 22 by using optical glue, so that the fixing and optical coupling effects between the crystal array 21 and the photoelectric converter 22 can be realized simultaneously, and the crystal array 21 is prevented from being fixed by a side clamping and fixing structure, so that the circumferential gap between the inner cylinder 11 and the outer cylinder 12 is reduced, and the gap between the PET detectors 20 is reduced.
Further, as shown in fig. 3, the PET detector 20 further includes a first cooler 27 and a second cooler 28, the first cooler 27 is thermally coupled directly to the readout circuit board 25, and the second cooler 28 is thermally coupled to the photoelectric converter array board 24.
It is understood that the first cooler 27 conducts out heat generated by the readout circuit 23 and the readout circuit board 25 to lower the temperature of the readout circuit 23 and the readout circuit board 25; the second cooler 28 conducts heat generated by the photoelectric converter 22 and the photoelectric converter array board 24 to lower the temperature of the photoelectric converter 22 and the photoelectric converter array board 24.
Preferably, the first cooler 27 includes a cold plate 271 and a cooling water pipe 272 communicated with the cold plate 271, and the second cooler 28 includes at least one heat pipe 281, and the heat pipe 281 is in thermal communication with the first cooler 27.
It is understood that the readout circuit board 25 is mounted on the cold plate 271, and the cold plate 271 cools down the readout circuit 23 and the readout circuit board 25. The photoelectric converter array plate 24 conducts heat to the cold plate 271 through the heat pipe 281 to lower the temperature of the photoelectric converters 22 and the photoelectric converter array plate 24.
Meanwhile, because the cold plate 271 is not limited by the radial space between the inner cylinder 11 and the outer cylinder 12, the thickness of the cold plate 271 can be made larger, and the diameter of the corresponding cooling water pipe 272 can also be made larger, so that the blockage of a circulating pipeline caused by corrosion can be reduced, and the reliability of the PET detector 20 is further improved.
Meanwhile, since the readout circuit board 25 and the photoelectric converter array plate are located at different positions on the substrate 29, and the readout circuit board 25 and the photoelectric converter array plate are in indirect thermal contact (the position of the heat pipe 281 can separate the photoelectric converter array plate from the readout circuit board 25), thermal influence of the readout circuit board 25 (high heat dissipation area) on the photoelectric converter array plate (low heat dissipation area) can be avoided as much as possible.
Further, the first cooler 27 further includes a cooler (not shown) and a cooling medium (not shown), the number of the cooling water pipes 272 is two, one end of one cooling water pipe 272 is connected to a water outlet of the cooler, and the other end is communicated with the cold plate 271; one end of the other cooling water pipe 272 is connected with the water inlet of the cold machine, and the other end is communicated with the cold plate 271. The chiller delivers cooling medium to the cold plates 271 through one of the chilled water tubes 272 and then carries the cooling medium to the chiller through the other chilled water tube 272, thus completing the circuit through which the first chiller 27 circulates.
The technical features of the embodiments described above may be arbitrarily combined, and for the sake of brevity, all possible combinations of the technical features in the embodiments described above are not described, but should be considered as being within the scope of the present specification as long as there is no contradiction between the combinations of the technical features.
The above-mentioned embodiments only express several embodiments of the present invention, and the description thereof is more specific and detailed, but not construed as limiting the scope of the invention. It should be noted that, for a person skilled in the art, several variations and modifications can be made without departing from the inventive concept, which falls within the scope of the present invention. Therefore, the protection scope of the present patent shall be subject to the appended claims.
Claims (10)
1. A PET detector comprising a crystal array (21), a photoelectric converter (22) and a readout circuit (23), the crystal array (21) being optically coupled with the photoelectric converter (22), the photoelectric converter (22) being disposed on a photoelectric converter array board (24), the readout circuit (23) being disposed on a readout circuit board (25), the photoelectric converter array board (24) being electrically connected with the readout circuit board (25), characterized in that the PET detector further comprises a substrate (29), the crystal array (21), the photoelectric converter (22) and the readout circuit (23) being sequentially disposed on the substrate (29) along a length direction of the substrate (29); the crystal array (21) comprises a plurality of crystals (211), the extending direction of the crystals (211) is determined from the direction from a gamma photon incident surface (212) of the crystals (211) to a crystal end surface opposite to the incident surface (212), and a straight line which passes through the crystal array (21) along the extending direction of the crystals (211) does not pass through the readout circuit board (25).
2. The PET detector according to claim 1, wherein the photoelectric converter array board (24) and the readout circuit board (25) are electrically connected by a flexible printed circuit board (26).
3. The PET detector of claim 1, wherein the photoelectric converter array plate (24) is disposed perpendicular to the crystal extension direction.
4. The PET detector according to claim 1, wherein the photoelectric converter array board (24) is disposed on one side of a crystal end face of the crystal array (21).
5. The PET detector of claim 1, wherein the PET detector (20) further includes a first cooler (27) and a second cooler (28), the first cooler (27) being thermally coupled directly to the readout circuit board (25), the second cooler (28) being thermally coupled to the optoelectric converter array board (24).
6. The PET detector of claim 5, wherein the first cooler (27) includes a cold plate (271) and a cooling water pipe (272) in communication with the cold plate (271), the second cooler (28) including at least one heat pipe (281), the heat pipe (281) being in thermal communication with the first cooler (27).
7. The PET detector according to claim 1, characterized in that the outer surface of the crystal array (21) is provided with a light-shielding coating.
8. The PET detector of claim 1, wherein the crystal array (21) is fixedly or removably attached to the photo-electric converter array board (24).
9. The PET detector according to claim 1, characterized in that the crystal array (21) is fixedly connected to the photoelectric converter (22) by means of optical glue.
10. A medical imaging apparatus (100) comprising a patient bed, a gantry (10) and a PET detector (20) according to any one of claims 1 to 9 arranged in the gantry (10).
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| Application Number | Priority Date | Filing Date | Title |
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| CN201910767830.XA CN110441811B (en) | 2019-08-20 | 2019-08-20 | PET detector and medical imaging equipment with same |
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| Application Number | Priority Date | Filing Date | Title |
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| CN201910767830.XA CN110441811B (en) | 2019-08-20 | 2019-08-20 | PET detector and medical imaging equipment with same |
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| CN110441811A CN110441811A (en) | 2019-11-12 |
| CN110441811B true CN110441811B (en) | 2021-05-04 |
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| CN112353410B (en) * | 2020-10-26 | 2023-04-25 | 武汉联影生命科学仪器有限公司 | Miniature positron emission imaging detector and miniature positron emission imaging equipment |
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| CN103339527A (en) * | 2011-02-03 | 2013-10-02 | 皇家飞利浦有限公司 | Single or multi-energy vertical radiation sensitive detectors |
| CN104603638A (en) * | 2012-05-22 | 2015-05-06 | Analogic公司 | Detection system and detector array interconnect assemblies |
| CN205015485U (en) * | 2015-09-09 | 2016-02-03 | 同方威视技术股份有限公司 | Detector subassembly and X -ray detector |
| CN105723243A (en) * | 2013-11-15 | 2016-06-29 | 皇家飞利浦有限公司 | Double-sided organic photodetector on flexible substrate |
| CN106772532A (en) * | 2017-01-04 | 2017-05-31 | 沈阳东软医疗系统有限公司 | Photodetector encapsulating structure and its method for packing based on water-cooled |
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| Publication number | Priority date | Publication date | Assignee | Title |
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| US7573040B2 (en) * | 2007-03-23 | 2009-08-11 | General Electric Company | Energy discriminating detector different materials direct conversion layers |
| US10680021B2 (en) * | 2017-05-12 | 2020-06-09 | General Electric Company | Active pixel sensor computed tomography (CT) detector and method of readout |
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Patent Citations (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN103339527A (en) * | 2011-02-03 | 2013-10-02 | 皇家飞利浦有限公司 | Single or multi-energy vertical radiation sensitive detectors |
| CN104603638A (en) * | 2012-05-22 | 2015-05-06 | Analogic公司 | Detection system and detector array interconnect assemblies |
| CN107529624A (en) * | 2012-05-22 | 2018-01-02 | Analogic公司 | Computed tomography detector, method and apparatus |
| CN105723243A (en) * | 2013-11-15 | 2016-06-29 | 皇家飞利浦有限公司 | Double-sided organic photodetector on flexible substrate |
| CN205015485U (en) * | 2015-09-09 | 2016-02-03 | 同方威视技术股份有限公司 | Detector subassembly and X -ray detector |
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Address after: 201807 2258 Chengbei Road, Jiading District, Shanghai Applicant after: Shanghai Lianying Medical Technology Co., Ltd Address before: 201807 2258 Chengbei Road, Jiading District, Shanghai Applicant before: SHANGHAI UNITED IMAGING HEALTHCARE Co.,Ltd. |
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