CN112051600B - Channel multiplexing circuit and imaging system - Google Patents
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Abstract
The present disclosure relates to a channel multiplexing circuit and an imaging system, the channel multiplexing circuit is used for collecting imaging signals generated by a detector array of the imaging system, and the channel multiplexing circuit comprises: the resistor network is provided with at least one signal acquisition node, and each signal acquisition node is connected with one detector in the detector array and is used for acquiring imaging signals generated by the corresponding detector; the correction network comprises at least one correction unit, each correction unit is connected with one detector in the detector array and is used for correcting distortion errors of imaging signals generated by the corresponding detector so that the signal acquisition nodes acquire corrected imaging signals, and the distortion errors are errors caused by capacitance-resistance circuits formed between the detector and the resistance network.
Description
Technical Field
The present disclosure relates to the field of medical devices, and in particular, to a channel multiplexing circuit and an imaging system.
Background
Positron emission computed tomography (PET) technology is a novel imaging technology capable of displaying the activities of biomolecule metabolism, receptors and neuromediators on living bodies, and is widely used for diagnosis and differential diagnosis of various diseases, disease judgment, curative effect evaluation, organ function research, new medicine development and the like. In PET imaging technology, positrons released during decay of a substance encounter electrons to produce a pair of photons that are detected using a detector array to generate an imaging signal for imaging. In the related art, a channel multiplexing circuit for acquiring an imaging signal may cause measurement errors, affecting imaging quality.
Disclosure of Invention
To overcome the problems in the related art, embodiments of the present disclosure provide a channel multiplexing circuit and an imaging system, which are used to solve the drawbacks in the related art.
According to a first aspect of embodiments of the present disclosure, there is provided a channel multiplexing circuit for acquiring imaging signals generated by a detector array of an imaging system, comprising:
the resistor network is provided with at least one signal acquisition node, and each signal acquisition node is connected with one detector in the detector array and is used for acquiring imaging signals generated by the corresponding detector;
the correction network comprises at least one correction unit, each correction unit is connected with one detector in the detector array and is used for correcting distortion errors of imaging signals generated by the corresponding detector so that the signal acquisition nodes acquire corrected imaging signals, and the distortion errors are errors caused by capacitance-resistance circuits formed between the detector and the resistance network.
In one embodiment, the detector has a cathode and an anode, the correction unit includes a bias resistor, an isolation capacitor and a cancellation amplifier, the anode of the detector is connected to the signal acquisition node and the non-inverting input terminal of the cancellation amplifier, respectively, the cathode of the detector is connected to one end of the bias resistor and one end of the isolation capacitor, the other end of the bias resistor is connected to the bias voltage, and the other end of the isolation capacitor is connected to the inverting input terminal and the output terminal of the cancellation amplifier, respectively;
wherein the cancellation amplifier is used for canceling the potential difference of the cathode and the anode of the detector.
In one embodiment, the resistor network is a network structure formed by at least one first resistor branch and two second resistor branches, wherein the first resistor branch comprises at least two resistors connected in sequence, the second resistor branch comprises at least two resistors connected in sequence, a signal acquisition node is formed between two adjacent resistors of the first resistor branch, one end of the first resistor branch and one second resistor branch form a connection point, and the other end of the first resistor branch and the other second point lease branch form another connection point.
In one embodiment, the imaging system further comprises at least four signal acquisition modules, wherein each signal acquisition module is connected with one connection point and is used for acquiring imaging signals acquired by each signal acquisition node through the connection point.
In one embodiment, the signal acquisition module comprises an integrator and an analog-to-digital converter connected to each other, wherein the integrator is connected to the corresponding connection point.
In one embodiment, the device further comprises a time signal summation module and a timing triggering module which are connected in sequence, wherein the time signal summation module is connected with at least four connection points;
the timing trigger module is used for outputting a time signal according to the summation result of the time signal summation module.
In one embodiment, the correction unit further comprises a summing resistor connected to the inverting input of the cancellation amplifier and the output of the cancellation amplifier, respectively.
In one embodiment, the system further comprises a time summation module and a timing triggering module which are sequentially connected, wherein the time summation module is connected with the summation resistor of each correction unit;
the timing triggering module is used for outputting a time signal according to the summation result of the time signal summation module.
In one embodiment, the system further comprises an energy summation module and a judgment module which are sequentially connected, wherein the energy summation module is connected with each signal acquisition module, and the judgment module is connected with the timing triggering module;
the energy summation module is used for carrying out energy summation on imaging signals acquired by the at least four signal acquisition modules, the judging module is used for comparing the summation result of the energy summation module with a preset energy threshold value, and the timing triggering module is used for outputting a time signal according to the summation result of the time signal summation module and the comparison result of the judging module.
According to a second aspect of embodiments of the present disclosure, there is provided an imaging system comprising the channel multiplexing circuit of any one of the first aspects.
The technical scheme provided by the embodiment of the disclosure can comprise the following beneficial effects:
the present disclosure provides for the correction of distortion errors in imaging signals of one detector by providing a resistor network having at least one signal acquisition node, then correspondingly acquiring imaging signals of one detector with each signal acquisition node, and by providing a correction network having at least one correction unit, then correspondingly correcting imaging signals of one detector with each correction unit. The signal acquisition node can acquire corrected imaging signals, namely distortion errors caused by a capacitance-resistance circuit formed between the detector and the resistance network are corrected, and the channel multiplexing circuit acquires the imaging signals generated by the detector array to be corrected, so that measurement errors are avoided, and imaging quality is improved.
Drawings
The accompanying drawings, which are incorporated in and constitute a part of this specification, illustrate embodiments consistent with the invention and together with the description, serve to explain the principles of the invention.
FIG. 1 is a diagram illustrating the true position of each detector of a detector array in accordance with an exemplary embodiment of the present disclosure;
FIG. 2 is a distorted position of individual detectors of a detector array shown in accordance with an exemplary embodiment of the present disclosure;
fig. 3 is a schematic diagram of a channel multiplexing circuit according to an exemplary embodiment of the present disclosure;
fig. 4 is a schematic diagram of a channel multiplexing circuit structure shown in another exemplary embodiment of the present disclosure;
fig. 5 is a schematic diagram of a channel multiplexing circuit structure shown in yet another exemplary embodiment of the present disclosure;
fig. 6 is a schematic diagram of a channel multiplexing circuit structure shown in yet another exemplary embodiment of the present disclosure.
Detailed Description
Reference will now be made in detail to exemplary embodiments, examples of which are illustrated in the accompanying drawings. When the following description refers to the accompanying drawings, the same numbers in different drawings refer to the same or similar elements, unless otherwise indicated. The implementations described in the following exemplary examples are not representative of all implementations consistent with the present disclosure. Rather, they are merely examples of apparatus and methods consistent with some aspects of the present disclosure as detailed in the accompanying claims.
The terminology used in the present disclosure is for the purpose of describing particular embodiments only and is not intended to be limiting of the disclosure. As used in this disclosure 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 also be understood that the term "and/or" as used herein refers to and encompasses any or all possible combinations of one or more of the associated listed items.
It should be understood that although the terms first, second, third, etc. may be used in this disclosure to describe various information, these information should not be limited to these terms. These terms are only used to distinguish one type of information from another. For example, first information may also be referred to as second information, and similarly, second information may also be referred to as first information, without departing from the scope of the present disclosure. The word "if" as used herein may be interpreted as "at … …" or "at … …" or "responsive to a determination", depending on the context.
Positron emission computed tomography (PET) technology is a novel imaging technology capable of displaying the activities of biomolecule metabolism, receptors and neuromediators on living bodies, and is widely used for diagnosis and differential diagnosis of various diseases, disease judgment, curative effect evaluation, organ function research, new medicine development and the like. In PET imaging technology, positrons released during decay of a substance encounter electrons to produce a pair of photons that are detected using a detector array to generate an imaging signal for imaging. In the related art, a channel multiplexing circuit for acquiring an imaging signal may cause measurement errors, affecting imaging quality.
Specifically, the detector can be equivalently in a form of connecting a current source in parallel with a parasitic capacitor, and after the detector is connected with the channel multiplexing circuit, a resistor in the channel multiplexing circuit is connected with the parasitic capacitor to form a capacitance-resistance circuit, so that current pulses generated by the current source of the detector are influenced by an RC time constant. Thus, if the duration of the current pulse is not long enough compared to the RC time constant, the amplitude of the current pulse acquired through the channel multiplexing circuit is distorted and becomes smaller than the original peak value.
In addition, the resistivity of each position of the channel multiplexing circuit is different, so that the RC time constants of different detectors are different, and the amplitude distortion errors of current pulses generated by the detectors are not uniform. This causes distortion in the resulting position of the circuit pulse (i.e., the position of the detector) as determined thereby, referring to fig. 1 and 2, fig. 1 is the true position of each detector, and fig. 2 is the position after distortion.
In addition, the capacitive resistor circuit can lengthen both rising edge and falling edge of the current pulse generated by the detector, and because of the difference of RC time constants of different detectors, the degree of elongation of the current pulse generated by each detector is different, and therefore, the time information determined by the capacitive resistor circuit can generate larger timing error.
Based on this, in a first aspect, at least one embodiment of the present disclosure provides a channel multiplexing circuit for acquiring imaging signals generated by a detector array of an imaging system, please refer to fig. 3, which illustrates a structure of the channel multiplexing circuit, including:
a resistor network 310 having at least one signal acquisition node 311, each signal acquisition node 311 being connected to one detector 321 of the detector array 320 (only a connection relationship between a pair of detectors 321 and a signal acquisition node 311 is shown) for acquiring imaging signals generated by the corresponding detector 321.
The resistor network 310 is a mesh structure formed by a plurality of networks, and a plurality of signal acquisition nodes 311 form a node array corresponding to the detector array 320 one by one, and the nodes are sequentially connected. After each signal acquisition node 311 acquires the imaging signal generated by the corresponding detector 321, the imaging signal is sent to at least one signal acquisition point of the resistor network 310 through a resistor or other signal acquisition nodes, and the position of the detector generating the imaging signal can be determined according to the signal intensity at each signal acquisition point.
Referring to fig. 4, in an example, a resistor network 400 has 16 signal collection nodes 401, and is respectively connected to 16 detectors 402 in a one-to-one correspondence, and is provided with four signal collection points A, B, C and D. The coordinates of the signal can be calculated by the current IA, IB, IC, ID at A, B, C, D, for example, the origin (0, 0) is set at the center of the array, the current of the two signal collection points B, D is added and subtracted by the current of the two signal collection points A, C, and then the sum of the currents of the four signal collection points A, B, C, D is divided to obtain the abscissa X of the signal; the current of the two signal collection points C, D is subtracted by adding the current of the two signal collection points A, B and divided by the sum of the currents of the four signal collection points A, B, C, D to obtain the ordinate Y of the signal, thereby obtaining the position coordinates (X, Y) of the signal. The specific calculation formula is as follows:
wherein A is peak 、B peak 、C peak And D peak The currents at the four signal collection points A, B, C, D, respectively.
With continued reference to fig. 3, the channel multiplexing circuit further includes a correction network 330, where the correction network 330 includes at least one correction unit 331, and each correction unit 331 is connected to one detector 321 in the detector array 320 (only a connection relationship between a pair of detectors 321 and the correction unit 321 is shown in the drawing) and is configured to correct a distortion error of an imaging signal generated by the corresponding detector 321, so that the signal acquisition node 311 acquires the corrected imaging signal, where the distortion error is an error caused by a capacitive-resistive circuit formed between the detector 321 and the resistive network 310.
The calibration network 330 has a plurality of calibration units 331 corresponding to the plurality of detectors 321 one by one. Each correction unit 331 corrects the corresponding detector independently.
Embodiments of the present disclosure provide for imaging signals of one detector to be acquired by providing a resistor network having at least one signal acquisition node, then using each signal acquisition node, and for distortion errors of imaging signals of one detector to be corrected by providing a correction network having at least one correction unit, then using each correction unit. The signal acquisition node can acquire corrected imaging signals, namely distortion errors caused by a capacitance-resistance circuit formed between the detector and the resistance network are corrected, and the channel multiplexing circuit acquires the imaging signals generated by the detector array to be corrected, so that measurement errors are avoided, and imaging quality is improved.
In some embodiments of the present disclosure, the channel multiplexing circuit is configured as shown in fig. 5, and the configuration of the correction unit of the correction network 502 is described in detail below. The detector S has a cathode and an anode, and the correction unit includes a bias resistor R b Isolation capacitor C and cancellation amplifier A f The anode of the detector S is respectively connected with the signal acquisition node and the cancellation amplifier A f The cathode of the detector S is connected with the bias resistor R respectively b Is connected to one end of the isolation capacitor C, the bias resistor R b And the other end of the bias voltage V bisa The other end of the isolation capacitor C is connected with the cancellation amplifier A respectively f Is connected with the output end; wherein the cancellation amplifier A f For eliminating the potential difference between the cathode and anode of the detector.
Wherein, bias resistor R b Providing bias high voltage to sensor S while liftingThe pulse voltage drop for sensor S. Cancellation amplifier A f The depth negative feedback is introduced to zero the potential difference across the sensor S, thereby canceling out the impulse response of the pulsed current on the parasitic capacitance of the sensor. The isolation capacitance C may keep the bias voltage of the sensor S from being pulled low. The correction unit is thus able to correct distortion errors caused by the capacitive resistive circuit, thereby enabling the resistive network to extract undistorted sensor imaging signals (e.g. current pulse signals).
In some embodiments of the present disclosure, the channel multiplexing circuit is configured as shown in fig. 5, and the structure of the resistor network 501 is described in detail below. The resistor network 501 is a network structure formed by at least one first resistor branch and two second resistor branches, wherein the first resistor branch comprises at least two resistors R connected in sequence r The second resistor branch comprises at least two resistors R which are connected in sequence c Adjacent two resistors R of the first resistor branch r And a signal acquisition node is formed between the first resistor branch and the second resistor branch, one end of the first resistor branch and one second resistor branch form a connection point, and the other end of the first resistor branch and the other second resistor branch form another connection point.
The first resistor branch may be a row resistor, and the second resistor branch may be a column resistor.
Wherein, the two second resistor branches are identical, the two ends of each second resistor branch are grounded, and the adjacent resistor R of each second resistor branch c A connection point is formed between the two first resistor branches, and a first resistor branch is connected between the corresponding connection points of the two second resistor branches. For example, as shown in FIG. 5, each first resistive branch has 5 resistors R r Each second resistance branch has 5 resistances R c Four first resistance branches are arranged between four pairs of connection points formed by the two second resistance branches in a one-to-one correspondence mode.
According to the embodiment of the disclosure, the resistor network is formed by resistor branches in two directions, so that a plurality of signal acquisition nodes are formed, and each signal acquisition node can be used for acquiring an imaging signal generated by one detector.
In some embodiments of the present disclosure, the channel multiplexing circuit further includes at least four signal acquisition modules, wherein each signal acquisition module is connected to one of the connection points, and is configured to acquire the imaging signal acquired by each signal acquisition node through the connection point.
Wherein the signal acquisition module comprises an integrator and an analog-to-digital converter (ADC) connected to each other, wherein the integrator is connected to the corresponding connection point.
With continued reference to fig. 5, in one example, the channel multiplexing circuit includes four signal acquisition modules E A 、E B 、E C And E is D Wherein, the signal acquisition module E A A first connection point A connected with the second resistor branch and used for acquiring imaging signals acquired by each signal acquisition point from the point A, and a signal acquisition module E B A first connection point B connected with the second resistor branch and used for acquiring imaging signals acquired by each signal acquisition point from the point B, and a signal acquisition module E C A first connection point C connected with the second resistor branch and used for acquiring imaging signals acquired by each signal acquisition point from the point C, and a signal acquisition module E D And the imaging signal acquisition device is connected with the first connection point D of the second resistor branch and is used for acquiring imaging signals acquired by each signal acquisition point from the point D. The electric charge amount can be acquired by the four signal acquisition modules, and the position coordinates of the detector for generating the imaging signal can be calculated according to the following formula:
wherein Q is A 、Q B 、Q C And Q D Respectively is a signal acquisition module E A 、E B 、E C 、E D The collected charge quantity, Q ∑ Is Q A 、Q B 、Q C And Q D A kind of electronic device.
In some embodiments of the present disclosure, the channel multiplexing circuit is configured as shown in fig. 5, and the channel multiplexing circuit further includes a time signal summing module 503 and a timing triggering module 504 connected in sequence, where the time signal summing module 503 is connected to at least four connection points; wherein the time signal summation module 503 is configured to time sum imaging signals acquired through the at least four connection points, and the timing trigger module 504 is configured to output a time signal according to a summation result of the time signal summation module 503.
The summation result of the time signal summation module 503 is a pulse signal, and when the amplitude of the pulse signal exceeds a preset amplitude threshold, the timing trigger module 504 may output a time signal or send a timing trigger signal. The timing trigger signal is sent to a time to digital converter 505 (TDC) for determining the time of generation of the imaging signal.
In some embodiments of the present disclosure, the structure of the channel multiplexing circuit is shown in fig. 6, where the channel multiplexing circuit shown in fig. 6 is substantially the same as the channel multiplexing circuit shown in fig. 5, and the difference is first represented in the structure of the correction network, and the structure of the correction unit of the correction network 601 is described in detail below: on the basis of the correction unit of the correction network 501, the correction unit further comprises a summing resistor R s The sum resistor R s Respectively with the cancellation amplifier A f Is connected to the inverting input of the cancellation amplifier A f Is connected with the output end of the power supply.
In addition, the channel multiplexing circuit shown in fig. 6 is different from the channel multiplexing circuit shown in fig. 5 in that the time summation module 603 is further embodied in a time summation module 603, specifically, the time signal summation module 603 is connected with a timing triggering module 604, and the time summation module 603 is further connected with a summation resistor R of each correction unit s And the timing triggering module 604 is used for outputting a time signal according to the summation result of the time signal summation module 603.
The corrected imaging signals are directly acquired through the correction units, distortion of the imaging signals is further avoided, and inaccuracy of the determined time caused by the fact that rising edges are lengthened is prevented.
The summation result of the time signal summation module 603 is a pulse signal, and the timing trigger module 604 may output a time signal or send a timing trigger signal when the amplitude of the pulse signal exceeds a preset amplitude threshold. The timing trigger signal is sent to a time to digital converter 605 (TDC) for determining the time of generation of the imaging signal.
In some embodiments of the present disclosure, the channel multiplexing circuit is configured as shown in fig. 5 and fig. 6, and the channel multiplexing circuit further includes an energy summation module 506, 606 and a judgment module 507, 607 connected in sequence, where the energy summation module 506, 606 is connected to each signal acquisition module, and the judgment module 507, 607 is connected to the timing triggering module 504, 604; the energy summation modules 506 and 606 are used for energy summation of imaging signals acquired by the at least four signal acquisition modules, the judging modules 507 and 607 are used for comparing summation results of the energy summation modules 506 and 606 with preset energy thresholds, and the timing triggering modules 504 and 604 are used for outputting time signals according to summation results of the time signal summation modules 503 and 603 and comparison results of the judging modules 507 and 607.
When the summation results of the time signal summation modules 503 and 603 meet the preset requirements, the timing triggering modules 504 and 604 acquire the judgment results of the judgment modules 507 and 607, and when the summation results of the energy summation modules 506 and 606 are within the preset energy interval, the timing triggering modules 504 and 604 can output time signals or send timing triggering signals. Through energy summation and summation result judgment, false triggering of abnormal time signals is avoided, and accuracy of output time signals is further improved.
According to a second aspect of embodiments of the present disclosure, there is provided an imaging system comprising the channel multiplexing circuit of any one of the first aspects.
Other embodiments of the disclosure will be apparent to those skilled in the art from consideration of the specification and practice of the disclosure disclosed herein. This application is intended to cover any adaptations, uses, or adaptations of the disclosure following, in general, the principles of the disclosure and including such departures from the present disclosure as come within known or customary practice within the art to which the disclosure pertains. It is intended that the specification and examples be considered as exemplary only, with a true scope and spirit of the disclosure being indicated by the following claims.
It is to be understood that the present disclosure is not limited to the precise arrangements and instrumentalities shown in the drawings, and that various modifications and changes may be effected without departing from the scope thereof. The scope of the present disclosure is limited only by the appended claims.
Claims (9)
1. A channel multiplexing circuit for acquiring imaging signals generated by a detector array of an imaging system, the detector having a cathode and an anode, comprising:
the resistor network is provided with at least one signal acquisition node, and each signal acquisition node is connected with one detector in the detector array and is used for acquiring imaging signals generated by the corresponding detector;
the correction network comprises at least one correction unit, each correction unit is connected with one detector in the detector array and is used for correcting distortion errors of imaging signals generated by the corresponding detector so that the signal acquisition nodes acquire corrected imaging signals, wherein the distortion errors are errors caused by capacitance-resistance circuits formed between the detector and the resistance network;
the correction unit comprises a bias resistor, an isolation capacitor and an elimination amplifier, wherein the anode of the detector is respectively connected with the signal acquisition node and the non-inverting input end of the elimination amplifier, the cathode of the detector is respectively connected with one end of the bias resistor and one end of the isolation capacitor, the other end of the bias resistor is connected with bias voltage, and the other end of the isolation capacitor is respectively connected with the inverting input end and the output end of the elimination amplifier;
wherein the cancellation amplifier is used for canceling the potential difference of the cathode and the anode of the detector.
2. The channel multiplexing circuit of claim 1, wherein the resistor network is a network structure formed by at least one first resistor branch and two second resistor branches, wherein the first resistor branch comprises at least two resistors connected in sequence, the second resistor branch comprises at least two resistors connected in sequence, a signal acquisition node is formed between two adjacent resistors of the first resistor branch, one end of the first resistor branch and one second resistor branch form a connection point, and the other end of the first resistor branch and the other second resistor branch form another connection point.
3. The channel multiplexing circuit of claim 2, further comprising at least four signal acquisition modules, wherein each signal acquisition module is coupled to one of the connection points for acquiring imaging signals acquired by each signal acquisition node through the connection point.
4. A channel multiplexing circuit according to claim 3 wherein the signal acquisition module comprises an integrator and an analog to digital converter connected to each other, wherein the integrator is connected to the corresponding connection point.
5. The channel multiplexing circuit of claim 3, further comprising a time signal summing module and a timing trigger module connected in sequence, the time signal summing module being connected to at least four of the connection points;
the timing trigger module is used for outputting a time signal according to the summation result of the time signal summation module.
6. A channel multiplexing circuit according to claim 3 wherein the correction unit further comprises a summing resistor connected to the inverting input of the cancellation amplifier and the output of the cancellation amplifier, respectively.
7. The channel multiplexing circuit of claim 6, further comprising a time signal summing module and a timing trigger module connected in sequence, said time signal summing module being connected to a summing resistor of each of said correction units,
the timing triggering module is used for outputting a time signal according to the summation result of the time signal summation module.
8. The channel multiplexing circuit of claim 5 or 7, further comprising an energy summation module and a judgment module connected in sequence, wherein the energy summation module is connected with each signal acquisition module, and the judgment module is connected with the timing trigger module;
the energy summation module is used for carrying out energy summation on imaging signals acquired by the at least four signal acquisition modules, the judging module is used for comparing the summation result of the energy summation module with a preset energy threshold value, and the timing triggering module is used for outputting a time signal according to the summation result of the time signal summation module and the comparison result of the judging module.
9. An imaging system comprising the channel multiplexing circuit of any of claims 1 to 8.
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Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1673772A (en) * | 2003-12-08 | 2005-09-28 | 西门子公司 | Radiation detector, as well as a method for synchronized radiation detection |
| CN109602438A (en) * | 2018-12-12 | 2019-04-12 | 彭浩 | The whole body PET data acquisition method and system of high reusing degree |
| CN110327063A (en) * | 2019-06-10 | 2019-10-15 | 东软医疗系统股份有限公司 | Energy correction method, device, console device and PET system |
| CN110381659A (en) * | 2019-06-04 | 2019-10-25 | 西安电子科技大学 | A kind of radio frequency dynamic capacity coupled plasma diagnostic system and method |
Family Cites Families (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| ES2239506B1 (en) * | 2003-04-10 | 2006-11-16 | Consejo Superior Investigacion | GAMMA RAY DETECTOR WITH INTERACTION DEPTH CODING. |
| JP5301158B2 (en) * | 2004-08-13 | 2013-09-25 | コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ | TOF-PET timing adjustment |
| JP4877766B2 (en) * | 2006-08-25 | 2012-02-15 | 独立行政法人放射線医学総合研究所 | Positron emission tomography imaging apparatus and radiation detector |
| US8779367B2 (en) * | 2012-02-20 | 2014-07-15 | General Electric Company | System and method for correcting timing errors in a medical imaging system |
-
2020
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Patent Citations (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN1673772A (en) * | 2003-12-08 | 2005-09-28 | 西门子公司 | Radiation detector, as well as a method for synchronized radiation detection |
| CN109602438A (en) * | 2018-12-12 | 2019-04-12 | 彭浩 | The whole body PET data acquisition method and system of high reusing degree |
| CN110381659A (en) * | 2019-06-04 | 2019-10-25 | 西安电子科技大学 | A kind of radio frequency dynamic capacity coupled plasma diagnostic system and method |
| CN110327063A (en) * | 2019-06-10 | 2019-10-15 | 东软医疗系统股份有限公司 | Energy correction method, device, console device and PET system |
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