CN108663703B - Detector, medical imaging system and information processing method - Google Patents
Detector, medical imaging system and information processing method Download PDFInfo
- Publication number
- CN108663703B CN108663703B CN201810289674.6A CN201810289674A CN108663703B CN 108663703 B CN108663703 B CN 108663703B CN 201810289674 A CN201810289674 A CN 201810289674A CN 108663703 B CN108663703 B CN 108663703B
- Authority
- CN
- China
- Prior art keywords
- crystal
- information
- photon
- detector
- column
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Active
Links
Images
Classifications
-
- 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
-
- 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)
Landscapes
- Physics & Mathematics (AREA)
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- General Physics & Mathematics (AREA)
- High Energy & Nuclear Physics (AREA)
- Molecular Biology (AREA)
- Spectroscopy & Molecular Physics (AREA)
- Engineering & Computer Science (AREA)
- Biomedical Technology (AREA)
- General Health & Medical Sciences (AREA)
- Medical Informatics (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Optics & Photonics (AREA)
- Nuclear Medicine (AREA)
- Measurement Of Radiation (AREA)
Abstract
The embodiment of the invention provides a detector, a medical imaging system and an information processing method. The detector comprises a plurality of crystal columns and a photoelectric detector coupled with the crystal columns, wherein the crystal columns are arranged in parallel to the axis of a scanning cavity, and at least one layer of the crystal columns is arranged in the circumferential direction of the scanning cavity. By replacing a plurality of crystal lattices in the same column in the axial direction in the traditional detector with the crystal columns, the number of paths of the reading structure is greatly reduced, and the hardware cost of the detector is saved. The problem that the hardware cost of a detector in medical imaging equipment is high in the prior art is solved to a certain extent.
Description
[ technical field ] A
The scheme relates to the technical field of medical treatment, in particular to a detector, a medical imaging system and an information processing method.
[ background of the invention ]
PET (Positron Emission Tomography) is a relatively important clinical examination image technology in the medical field, and has a wide application in the medical field.
PET scanning is performed by a PET system, the core component of which is the PET detectors. The PET system includes a gantry, which is provided with a cylindrical bore called a scanning chamber for accommodating a bed extending axially (referring to a central axis of the cylindrical bore) for carrying a scanned object. The PET detector is arranged on the inner side of the scanning cavity.
The PET detector is the most critical component for determining the performance of PET, and generally consists of a crystal, a photodetector and a high voltage power supply. The crystal is used for converting high-energy photons which are not easy to generate photoelectric effect into visible photons so as to be received by a photoelectric detector. The photoelectric sensor is used for converting visible photons generated by the crystal into electrons through a photoelectric effect, and outputting the electrons to an electronic circuit system in a backset in the form of current after the electrons are amplified step by step.
. In conventional PET detectors, the crystals are present in the form of crystal blocks. FIG. 1 is a schematic cross-sectional view of a conventional PET detector. Referring to FIG. 1, in a conventional PET detector, the crystal masses are arranged in a circumferential direction on the one hand and in an axial direction on the other hand. Therefore, conventional PET detectors are expanded to n × n lattices (i.e., n rows and n columns of lattices), each lattice has one readout structure (see fig. 1), and the n × n lattices require n × n readout structures in total, and the number of readout structures is large, which results in high hardware cost of the PET detector.
In addition, the conventional PET detector is developed into an n × n lattice (i.e., n rows and n columns of lattices), energy information collected by the lattices in the same column (axial direction) is the same, and the positions of photon incidence points in the radial direction (the direction perpendicular to the axial direction) cannot be distinguished, so that the incidence depth information of photons cannot be determined. This results in that two-dimensional coordinates of the photon incidence point can be obtained by conventional PET detectors, but three-dimensional coordinates of the incidence point cannot be obtained. Furthermore, each lattice has a readout structure, and n × n lattices require n × n readout structures in total, which leads to higher hardware cost of the PET detector.
[ summary of the invention ]
In view of this, the embodiment of the present disclosure provides a detector, a medical imaging system, and an information processing method, so as to solve the problem that hardware cost of a detector in a medical imaging device is high in the prior art.
In a first aspect, an embodiment of the present invention provides a detector, which includes a plurality of crystal pillars and a photodetector coupled to the plurality of crystal pillars, where the plurality of crystal pillars are disposed parallel to an axis of a scanning cavity, and at least one layer of the plurality of crystal pillars is arranged along a circumferential direction of the scanning cavity.
The above aspect and any possible implementation further provide an implementation in which a light guide is disposed between the crystal pillar and the photodetector.
The aspect and any possible implementation described above further provides an implementation in which a reflective film is disposed between adjacent ones of the plurality of crystal pillars.
The above aspect and any possible implementation further provide an implementation in which the photodetectors are arranged in pairs, and each pair of the photodetectors connects at least one of the crystal pillars.
The above aspect and any possible implementation further provides an implementation in which each of the crystal pillars has a corresponding crystal pillar disposed opposite thereto 180 degrees apart.
In a second aspect, an embodiment of the present invention provides a medical imaging system, including the detector of any one of the first aspect.
In a third aspect, an embodiment of the present invention provides an information processing method, which is applied to the medical imaging system according to the second aspect; the method comprises the following steps:
collecting energy information and time information of photons;
and determining the spatial position information of the photon according to the energy information and the time information, wherein the spatial position information comprises radial position information and axial position information.
The above-mentioned aspect and any possible implementation manner further provide an implementation manner, wherein determining spatial position information of the photon according to the energy information and the time information comprises:
respectively acquiring first energy information generated by the photon at a first end of a crystal pillar and second energy information generated at a second end of the crystal pillar;
acquiring total length information of the crystal column;
and determining the axial position information of the photon according to the first energy information, the second energy information and the total length information.
The above-mentioned aspect and any possible implementation manner further provide an implementation manner, wherein determining spatial position information of the photon according to the energy information and the time information comprises:
acquiring row information and column information of the crystal column in which the photon termination position is located in the crystal column array;
and determining the radial position information of the photon according to the row information and the column information.
As with the above-described aspects and any possible implementations, there is further provided an implementation, where the method further includes:
judging whether a coincidence event occurs based on the energy information and the time information;
upon occurrence of a coincidence event, the coincidence event is recorded.
The embodiment of the invention has the following beneficial effects:
according to the detector provided by the embodiment of the invention, the crystal columns are used for replacing a plurality of crystal lattices in the same column in the axial direction in the traditional detector, and each crystal column is connected with two paths of reading structures at most, so that the PET detector with n crystal columns needs 2n paths of reading structures at most, compared with the traditional detector needing n x n reading structures, the number of paths of reading structures is greatly reduced, and the hardware cost of the detector is saved.
[ description of the drawings ]
In order to more clearly illustrate the technical solutions of the embodiments of the present invention, the drawings required to be used in the embodiments will be briefly described below, and it is obvious that the drawings in the following description are only some embodiments of the present invention, and it is obvious for those skilled in the art that other drawings can be obtained according to the drawings without creative efforts.
FIG. 1 is a schematic cross-sectional view of a conventional PET detector.
Fig. 2 is a schematic diagram of an arrangement of crystal pillars in a detector according to an embodiment of the present invention.
Fig. 3 is a schematic diagram of a pair of photons incident on the corresponding 2 crystal pillars.
Fig. 4 is a schematic view of photons incident on a crystal pillar.
Fig. 5 is a flowchart illustrating an information processing method according to an embodiment of the present invention.
FIG. 6 is a schematic diagram of a pair of crystal pillars involved in an annihilation event provided by an embodiment of the invention.
[ detailed description ] embodiments
In order to better understand the technical scheme of the invention, the following detailed description of the embodiments of the invention is made with reference to the accompanying drawings.
It should be understood that the described embodiments are only some embodiments of the invention, and not all 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.
The terminology used in the embodiments of the invention is for the purpose of describing particular embodiments only and is not intended to be limiting of the invention. As used in the description of the invention and the appended claims, the singular forms "a", "an", and "the" are intended to include the plural forms as well, unless the context clearly indicates otherwise.
It should be understood that the term "and/or" as used herein is merely one type of association that describes an associated object, meaning that three relationships may exist, e.g., a and/or B may mean: a exists alone, A and B exist simultaneously, and B exists alone. In addition, the character "/" herein generally indicates that the former and latter related objects are in an "or" relationship.
The word "if" as used herein may be interpreted as "at … …" or "when … …" or "in response to a determination" or "in response to a detection", depending on the context. Similarly, the phrases "if determined" or "if detected (a stated condition or event)" may be interpreted as "when determined" or "in response to a determination" or "when detected (a stated condition or event)" or "in response to a detection (a stated condition or event)", depending on the context.
Example one
Embodiments of the present invention provide a detector, which may be applied to Single-modality medical imaging devices or multi-modality medical imaging devices such as PET, PET/MR (Magnetic Resonance), SPECT (Single-Photon Emission Computed Tomography), and PEM (Positron Emission Tomography).
The detector comprises a plurality of crystal columns and a photoelectric detector coupled with the crystal columns, wherein the crystal columns are arranged in parallel to the axis of the scanning cavity, and at least one layer of the crystal columns is arranged in the circumferential direction of the scanning cavity.
Wherein, the cross section of the crystal column can be round, square, rectangle, etc.
In one exemplary implementation, the photodetectors are arranged in pairs, with at least one crystalline pillar connected to each pair of photodetectors (each pair of photodetectors comprising two photodetectors). The at least one crystal column is formed into a group, and two ends of each group of crystal columns are respectively connected with a photoelectric detector.
It should be noted that, in this embodiment, each group of crystal pillars is connected to two readout structures. Two ends of each group of crystal columns are respectively connected with a reading structure, and each reading structure can comprise a photoelectric detector, a signal amplifier, a waveform filtering and shaping module, an analog-to-digital converter, a logic processing unit and the like.
Fig. 2 is a schematic diagram of an arrangement of crystal pillars in a detector according to an embodiment of the present invention. Referring to fig. 2, the crystal pillars are parallel to the axial direction of the scanning chamber, and the crystal pillars are arranged along the circumferential direction of the scanning chamber. In fig. 2, there are two crystal columns arranged along the circumferential direction of the scanning chamber, and in other embodiments, there may be one crystal column arranged along the circumferential direction of the scanning chamber, or there may be more than two crystal columns.
Fig. 3 is a schematic diagram of a pair of photons incident on the corresponding 2 crystal pillars. The 2 crystal pillars in fig. 3 are the corresponding crystal pillars that are oppositely disposed, 180 degrees apart. The wavy line in fig. 3 represents the entire path of back propagation of two photons annihilated by a positron (this wavy line is called a line of response LOR (line of response)), the solid black dots on the wavy line represent the position of the positron annihilation, and Δ x represents the distance of the annihilation position from the center of the LOR.
Fig. 4 is a schematic view of photons incident on a crystal pillar. In fig. 4, the solid black dots are the locations where the photons terminate into the crystal pillar.
According to the detector provided by the embodiment of the invention, n crystal lattices in the same column in the axial direction in the conventional detector are replaced by one crystal column, so that for the conventional detector of n x n lattices, the detector provided by the embodiment of the invention can use n crystal columns. Because each crystal pillar is connected with two paths of readout structures at most, the PET detector with n crystal pillars needs 2n paths of readout structures at most, and compared with the traditional detector needing n-by-n paths of readout structures, the number of paths of readout structures is greatly reduced, and the hardware cost of the detector is saved.
In one exemplary implementation, a light guide can be disposed between the crystal pillar and the photodetector. Light is reflected at the interface of two materials as it travels from one refractive index (n1) material to the other (n2), the greater the difference between n1 and n2, the greater the reflectivity and the lower the transmission, which is disadvantageous for detectors where higher transmission is required. The light guide can reduce the light reflectivity between the crystal pillar and the photodetector, thereby improving the quality of the detector.
In one exemplary implementation, a reflective film is disposed between adjacent ones of the plurality of crystalline pillars. When light propagates in the crystal column, some photons are incident on the side faces of the crystal and are scattered, and the number of photons finally transmitted to the end face is reduced by the scattering, so that the photon collection efficiency of the end face is reduced. The reflection film is arranged between the adjacent crystal columns, photons incident on the side faces of the crystals can be reflected back, the number of the photons finally transmitted to the end faces is increased, and therefore the photon collection efficiency of the end faces can be improved.
In one exemplary implementation, each crystal pillar has a corresponding crystal pillar disposed opposite thereto, 180 degrees apart. In one exemplary implementation, the crystal pillar may be an inorganic scintillation crystal, an organic scintillator, a liquid scintillator, a gas detector, a semiconductor, an RPC (Resistive Plate detector), or the like.
According to the detector provided by the embodiment of the invention, the crystal columns are used for replacing a plurality of crystal lattices in the same column in the traditional detector in the axial direction, and each crystal column is connected with two paths of readout structures at most, so that the PET detector with n crystal columns needs 2n paths of readout structures at most, compared with the traditional detector needing n x n readout structures, the number of paths of readout structures is greatly reduced, and the hardware cost of the detector is saved.
Example two
An embodiment of the present invention provides a medical imaging system, which includes any one of the detectors of the first embodiment. The medical imaging system provided by the embodiment of the invention can be a single-mode medical imaging system or a multi-mode medical imaging system such as a PET system, a PET/MR system, a SPECT system, a PEM system and the like.
Since the detector in the first embodiment reduces the number of the readout structures, and each readout structure corresponds to one signal to be processed, the number of the readout structures is reduced, so that the number of the signals to be processed is also reduced. In this way, the corresponding resource requirements for processing the signals to be processed in the medical imaging system are also reduced, so that the cost of the medical imaging system can be saved.
And, because the number of signals to be processed is reduced, the processing time of the medical imaging system is reduced, thereby improving the processing efficiency of the medical imaging system.
EXAMPLE III
The embodiment of the invention provides an information processing method, which is applied to the medical imaging system in the second embodiment.
Fig. 5 is a flowchart illustrating an information processing method according to an embodiment of the present invention. As shown in fig. 5, in this embodiment, the information processing method may include the following steps:
and S501, collecting energy information and time information of photons.
And S502, determining the spatial position information of the photon according to the energy information and the time information, wherein the spatial position information comprises radial position information and axial position information.
Photons incident into the crystal pillar (hereinafter referred to as incident photons) are converted into visible photons under the action of the crystal, the visible photons are emitted to two ends of the crystal pillar and received by photodetectors at two ends of the crystal pillar, and the visible photons are converted into electrons through a photoelectric effect and are output in the form of current after being amplified.
Wherein the photon in step S501 refers to an incident photon, the energy information may be a current signal corresponding to the photon, and the time information may be a time when the visible photon is recorded at both ends of the crystal pillar.
In step S502, the radial position refers to a position on the cross section of the scanning cavity corresponding to the position of the end point of the incident photon, and the axial position refers to a position of the end point of the incident photon on the axis parallel to the scanning cavity.
Please refer to fig. 4. In fig. 4, the position of the incident point is the position of the termination point of the incident photon, the grid shown by the dashed line where the position of the incident point is located is the cross section of the scanning cavity, and the coordinate of the position of the incident point on the plane of the dashed grid is the radial position. The position of the incidence point in fig. 4 and the axial distance between the position and the two ends of the crystal column are axial positions.
Therefore, the information processing method of the embodiment shown in fig. 5 can realize three-dimensional positioning of the position of the termination point of the incident photon.
In one exemplary implementation, determining spatial location information of the photons according to the energy information and the time information may include: respectively acquiring first energy information generated by photons at a first end of the crystal column and second energy information generated at a second end of the crystal column; acquiring total length information of the crystal column; and determining the axial position information of the photon according to the first energy information, the second energy information and the total length information.
For example, assuming that the distance from the photon termination point to the first end of the crystal pillar is L1, the distance from the photon termination point to the second end of the crystal pillar is L2, and the first energy information generated by the photon at the first end of the crystal pillar and the second energy information generated at the second end of the crystal pillar are E1 and E2, respectively, which can be obtained by using the relations of E1/E2 ═ L2/L1 and L1+ L2 ═ L (L is the total length of the crystal pillar).
In one exemplary implementation, determining spatial location information of the photons according to the energy information and the time information may include: acquiring row information and column information of a crystal column in which a photon termination position is located in a crystal column array; and determining the radial position information of the photon according to the row information and the column information.
For example. Please refer to fig. 4. In fig. 4, the dotted grid is a grid with 4 rows and 4 columns, the number of rows and the number of columns of the grid at the position of the incident point are 2, and therefore the position of the incident point in fig. 4 is (2, 2) in the radial direction.
In an exemplary implementation, the information processing method may further include: judging whether a coincidence event occurs based on the energy information and the time information; when a coincidence event occurs, the coincidence event is recorded.
The following illustrates the determination process of coincidence events.
FIG. 6 is a schematic diagram of a pair of crystal pillars involved in an annihilation event provided by an embodiment of the invention. Referring to fig. 6, crystal column a and crystal column B are a pair of oppositely disposed crystal columns 180 degrees apart, and in an annihilation event, one photon of a pair of generated photons is incident on crystal column a and the other photon is incident on crystal column B.
Referring to fig. 6, each of the crystal pillars a and B is composed of i × j small crystal pillars, so that the cross section of the crystal pillar a and the crystal pillar B is a plane having i × j crystal lattices, and i and j respectively indicate serial numbers of rows and columns in the plane.
Wherein, the two end points of the crystal column A are A1 and A2, and the two end points of the crystal column B are B1 and B2. The photon incident into the crystal column A generates energy E at the end A1 A1 The abscissa of the incident point is x A1 Ordinate is y A1 (ii) a The photon incident into the crystal column A generates energy E at the end A2 A2 The abscissa of the incident point is x A1 Ordinate is y A1 . The photon incident on the crystal pillar B generates energy E at the end B1 B1 The abscissa of the incident point is x B1 On the ordinate of y B1 (ii) a The photon incident into the crystal column B generates energy E at the end B2 B2 The abscissa of the incident point is x B2 Ordinate is y B2 。
For crystal column a, the following treatments were performed:
the energy E is calculated according to the following formula (1) A1 And E A2 ：
E＝∑E ij (1)
Wherein E is ij Representing the energy value collected on the crystal in the ith row and the jth column in the crystal column.
The abscissa x is calculated according to the following formula (2) A1 And x A2 ：
Wherein x is ij And the X coordinate value corresponding to the crystal in the ith row and the jth column on the plane of the i multiplied by j lattices representing the crystal column.
The total coordinate y is calculated according to the following equation (3) A1 And y A2 ：
Wherein, y ij And the Y coordinate value corresponding to the crystal in the ith row and the jth column on the plane of the i multiplied by j lattices representing the crystal column.
According to E A1 A result of the calculation of (D), judgment E A1 Whether within a specified energy window, and according to E A2 A result of the calculation of (D), judgment E A2 Whether within a specified energy window.
If E A1 Within a specified energy window and E A2 Within a given energy window, the energy of the energy,
reconstructing the transmission path of the photons incident into the crystal pillar A in the crystal pillar A, and obtaining Z by using the energy information and the time information A 。
In FIG. 6, the photon incident into the crystal pillar A has an incident depth Z corresponding to the incident depth A (assuming that the total length of the crystal pillar A is L A ，Z A Is the distance from the photon termination point to the end a 1), E A1 /E A2 ＝(L A -Z A )/Z A From which Z can be obtained A The value of (c).
The time for the photon incident into the crystal column A to reach the crystal column A is T A 。T A The calculation method of (c) is as follows:
when the photon reaches the crystal column A, it is now designated T A This moment is theoretical and has not been recorded by detection. At this time, the photon will generate 2 fluorescence photons in the crystal pillar a, and the 2 fluorescence photons respectively propagate to the two ends of the crystal pillar a, and are recorded at the two detection times T at the two ends of the crystal pillar a respectively A 1＝T A +a 1 ,T A 2＝T A +a 2 Wherein a is 1 、a 2 Is the propagation time of the fluorescence photon in the crystal, when T is determined A There are two ways:
the method I comprises the following steps: t is A ＝(T A 1+T A 2)/2；
The second method comprises the following steps: t is A ＝((T A 1+T A 2)-(a 1+ a 2 ))/2。
Wherein, a 1 、a 2 Can be obtained from the relationship between the crystal length and the propagation time.
T A 1 is the time at which the fluorescence photon reaches the first end of the crystal column A, T A 2 the time at which the fluorescence photon reaches the second end of crystal pillar a.
From the above information, the three-dimensional position (X) where photons are incident into the crystal pillar A is obtained A ，Y A ，Z A ，T A )。
Similarly, for the photon incident into the crystal cylinder B, the three-dimensional position (X) of the photon incident into the crystal cylinder B can be obtained B ，Y B ，Z B ，T B )。
According to T A And T B Calculate TOF (Time of Flight, Time difference of Flight), formula as follows:
TOF＝T A -T B (4)
and judging whether the value of the TOF is in the coincidence window, if so, judging that a coincidence event occurs, and if not, judging that no coincidence event occurs.
Recording coincidence events (X) A ，Y A ，Z A ，T A ，E A ；X B ，Y B ，Z B ，T B ，E B )。
Wherein E is A ＝E A1 +E A1 And represents the total energy of the photon generated in the crystal pillar a.
E B ＝E B1 +E B2 And represents the total energy generated by the photon in the crystal pillar B.
Because the photodetector itself has a dark count, there is a certain probability of spontaneously generating a dark signal in the absence of a signal. In the process of judging and selecting the coincidence time by the information processing method provided by the embodiment of the invention, when the photoelectric detectors at two ends of the crystal column have signals, the effective coincidence event is considered, the probability that dark signals exist at two ends of the crystal column at the same time is very low, and the photoelectric detectors at two ends of the crystal column have signals at the same time only through real photon signals, so that the dark signals are eliminated, and the effective photon signals are kept.
It can be clearly understood by those skilled in the art that, for convenience and brevity of description, the specific working processes of the system, the apparatus and the module described above may refer to the corresponding processes in the foregoing method embodiments, and are not described herein again.
In the several embodiments provided in the present invention, it should be understood that the disclosed system, apparatus and method may be implemented in other ways. For example, the above-described apparatus embodiments are merely illustrative, and for example, the division of the modules is only one type of logical functional division, and other divisions may be realized in practice, for example, a plurality of modules or components may be combined or integrated into another system, or some features may be omitted, or not executed. In addition, the shown or discussed coupling or direct coupling or communication connection between each other may be through some interfaces, indirect coupling or communication connection between devices or modules, and may be in an electrical, mechanical or other form.
The modules described as separate parts may or may not be physically separate, and parts displayed as modules may or may not be physical modules, may be located in one place, or may be distributed on a plurality of network units. Some or all of the modules may be selected according to actual needs to achieve the purpose of the solution of this embodiment.
In addition, functional modules in the embodiments of the present invention may be integrated into one processing unit, or each module may exist alone physically, or two or more modules are integrated into one unit. The integrated unit may be implemented in the form of hardware, or in the form of hardware plus a software functional unit.
The integrated unit implemented in the form of a software functional unit may be stored in a computer-readable storage medium. The software functional unit is stored in a storage medium and includes several instructions for causing a computer device (which may be a personal computer, a server, or a network device) or a Processor (Processor) to execute some steps of the method according to the embodiments of the present invention. And the aforementioned storage medium includes: various media capable of storing program codes, such as a usb disk, a removable hard disk, a Read-Only Memory (ROM), a Random Access Memory (RAM), a magnetic disk, or an optical disk.
The above description is only for the purpose of illustrating the preferred embodiments of the present invention and should not be taken as limiting the scope of the present invention, and any modifications, equivalents, improvements and the like made within the spirit and principle of the present invention should be included in the scope of the present invention.
Claims (8)
1. An information processing method, characterized by being applied to a medical imaging system; the medical imaging system comprises a plurality of crystal pillars and a photodetector coupled with the plurality of crystal pillars, wherein the plurality of crystal pillars are arranged in parallel to the axis of a scanning cavity, and the plurality of crystal pillars are arranged in multiple layers along the circumferential direction of the scanning cavity; the method comprises the following steps:
collecting energy information and time information of photons, wherein the energy information is current signals corresponding to the photons, and the time information is the time when the photons are recorded at two ends of the crystal column;
determining spatial position information of the photons according to the energy information and the time information, wherein the spatial position information comprises radial position information and axial position information;
the determining the spatial position information of the photon according to the energy information and the time information comprises:
respectively acquiring first energy information generated by the photon at a first end of a crystal column and second energy information generated at a second end of the crystal column;
acquiring total length information of the crystal column;
determining axial position information of the photon according to the first energy information, the second energy information and the total length information;
acquiring row information and column information of the crystal pillar where the photon termination position is located in the crystal pillar array;
and determining the radial position information of the photon according to the row information and the column information.
2. The method of claim 1, further comprising:
judging whether a coincidence event occurs based on the energy information and the time information;
upon occurrence of a coincidence event, the coincidence event is recorded.
3. The method of claim 1, wherein a light guide is disposed between the crystal pillar and the photodetector.
4. The method of claim 1, wherein a reflective film is disposed between adjacent ones of the plurality of crystalline pillars.
5. The method of claim 1, wherein the photodetectors are arranged in pairs, each pair connecting at least one of the crystal pillars.
6. The method of claim 1, wherein each of the crystal pillars has a corresponding crystal pillar disposed opposite thereto 180 degrees apart.
7. The method of claim 1, wherein each crystal pillar is connected to at most two-way readout structures.
8. The method of claim 7, wherein each of the readout structures comprises a photodetector, a signal amplifier, a waveform filter shaping module, an analog-to-digital converter, and a logic processing unit.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201810289674.6A CN108663703B (en) | 2018-03-30 | 2018-03-30 | Detector, medical imaging system and information processing method |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN201810289674.6A CN108663703B (en) | 2018-03-30 | 2018-03-30 | Detector, medical imaging system and information processing method |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN108663703A CN108663703A (en) | 2018-10-16 |
| CN108663703B true CN108663703B (en) | 2022-07-26 |
Family
ID=63782905
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN201810289674.6A Active CN108663703B (en) | 2018-03-30 | 2018-03-30 | Detector, medical imaging system and information processing method |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN108663703B (en) |
Families Citing this family (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN109498044B (en) * | 2018-10-15 | 2020-09-08 | 华中科技大学 | PET annular detection imaging system based on scintillation optical fiber |
Citations (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4823016A (en) * | 1986-09-18 | 1989-04-18 | Hamamatsu Photonics Kabushiki Kaisha | Scintillation detector for three-dimensionally measuring the gamma-ray absorption position and a positron CT apparatus utilizing the scintillation detector |
| US4870280A (en) * | 1986-12-11 | 1989-09-26 | Hamamatsu Photonics Kabushiki | Radiation detector |
| US5210420A (en) * | 1991-12-19 | 1993-05-11 | Positron Corporation | Positron emission tomography scanner |
| CN205608196U (en) * | 2016-01-18 | 2016-09-28 | 中国人民解放军防化学院 | Well type scintillation body gamma register for easy reference detection device |
| CN205826876U (en) * | 2016-06-30 | 2016-12-21 | 上海联影医疗科技有限公司 | Positron emission tomography |
| US9575192B1 (en) * | 2016-06-16 | 2017-02-21 | FMI Medical Systems Co., Ltd. | Optical channel reduction method and apparatus for photodetector arrays |
| CN106562799A (en) * | 2016-10-19 | 2017-04-19 | 武汉中派科技有限责任公司 | Detector for positron emission imaging equipment, and positron emission imaging equipment |
Family Cites Families (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US7332721B2 (en) * | 2005-04-13 | 2008-02-19 | Photodetection Systems, Inc. | Separation of geometric system response matrix for three-dimensional image reconstruction |
-
2018
- 2018-03-30 CN CN201810289674.6A patent/CN108663703B/en active Active
Patent Citations (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4823016A (en) * | 1986-09-18 | 1989-04-18 | Hamamatsu Photonics Kabushiki Kaisha | Scintillation detector for three-dimensionally measuring the gamma-ray absorption position and a positron CT apparatus utilizing the scintillation detector |
| US4870280A (en) * | 1986-12-11 | 1989-09-26 | Hamamatsu Photonics Kabushiki | Radiation detector |
| US5210420A (en) * | 1991-12-19 | 1993-05-11 | Positron Corporation | Positron emission tomography scanner |
| CN205608196U (en) * | 2016-01-18 | 2016-09-28 | 中国人民解放军防化学院 | Well type scintillation body gamma register for easy reference detection device |
| US9575192B1 (en) * | 2016-06-16 | 2017-02-21 | FMI Medical Systems Co., Ltd. | Optical channel reduction method and apparatus for photodetector arrays |
| CN205826876U (en) * | 2016-06-30 | 2016-12-21 | 上海联影医疗科技有限公司 | Positron emission tomography |
| CN106562799A (en) * | 2016-10-19 | 2017-04-19 | 武汉中派科技有限责任公司 | Detector for positron emission imaging equipment, and positron emission imaging equipment |
Also Published As
| Publication number | Publication date |
|---|---|
| CN108663703A (en) | 2018-10-16 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| US7381959B2 (en) | Technique for reconstructing PET scan images | |
| US6791090B2 (en) | Compton deconvolution camera | |
| JP5037119B2 (en) | Gamma-ray detector with interaction depth encoding | |
| JP5641930B2 (en) | Diagnostic imaging system, time stamp calculation method, processor for executing the method, and computer-readable medium programmed with the method | |
| US8767908B2 (en) | Exact and approximate rebinning of time-of-flight PET positron emission tomography data | |
| CN105452902A (en) | Pixel identification for small pitch scintillation crystal arrays | |
| Lewellen | The challenge of detector designs for PET | |
| US5532489A (en) | Positron imaging apparatus | |
| US20060076496A1 (en) | SPECT gamma camera | |
| CN105125231B (en) | A kind of minimizing technology and device of PET image ring artifact | |
| US7732773B2 (en) | Gamma-ray tracking method for pet systems | |
| WO2009157526A1 (en) | Gamma-ray detector, radiation diagnostic device, tomographic device, and analysis method therefor | |
| US20130015352A1 (en) | High performance computing for three dimensional proton computed tomography (hpc-pct) | |
| CN113777648B (en) | Method and gamma camera based on random encoding and neural network detector imaging | |
| CN101278318A (en) | Method and system for PET image reconstruction using a surrogate image | |
| US7332721B2 (en) | Separation of geometric system response matrix for three-dimensional image reconstruction | |
| US10222490B2 (en) | PET scanner with emission and transmission structures in a checkerboard configuration | |
| CN108663703B (en) | Detector, medical imaging system and information processing method | |
| WO2024131738A1 (en) | Crystal array detector and emission imaging device | |
| JP7453359B2 (en) | Method for position and energy determination in scintillation detectors | |
| WO2023197626A1 (en) | Spatial encoding detector, spatial encoding method, spatial decoding method, spatial decoding apparatuses, and storage medium | |
| CN205506718U (en) | Dual intensity detector device, system | |
| CN110680368B (en) | Method and device for detecting effective single event, and method and system for reading signal | |
| JP2019200162A (en) | Pet device and method for acquiring gamma ray generation position of scattering coincidence counting in pet device | |
| CN106405607A (en) | Cherenkov single event detection method and apparatus |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| CB02 | Change of applicant information | ||
| CB02 | Change of applicant information |
Address after: 201807 Shanghai city Jiading District Industrial Zone Jiading Road No. 2258 Applicant after: Shanghai Lianying Medical Technology Co.,Ltd. Address before: 201807 Shanghai city Jiading District Industrial Zone Jiading Road No. 2258 Applicant before: SHANGHAI UNITED IMAGING HEALTHCARE Co.,Ltd. |
|
| GR01 | Patent grant | ||
| GR01 | Patent grant |