CN116350253A

CN116350253A - Detector, data acquisition method and device and medical equipment

Info

Publication number: CN116350253A
Application number: CN202310282203.3A
Authority: CN
Inventors: 张喜龙; 胡小青; 相欣
Original assignee: Neusoft Medical Systems Co Ltd
Current assignee: Neusoft Medical Systems Co Ltd
Priority date: 2023-03-21
Filing date: 2023-03-21
Publication date: 2023-06-30

Abstract

The invention discloses a detector, a data acquisition method, a data acquisition device and medical equipment. The detector comprises a plurality of detection submodules, a processor and a pre-buffer unit, and each detection submodule comprises a signal conversion unit. Firstly, converting a ray analog signal into a recordable digital electric signal through a signal conversion unit so as to obtain ray data; then, the processor writes the ray data converted by the plurality of signal conversion units into the pre-buffer unit or reads the ray data from the pre-buffer unit through a first transmission path; and finally, outputting the ray data in the front buffer unit by the detector through a second transmission path. The prepositive buffer memory of the ray data obtained by the conversion of the signal conversion unit is realized, the data transmission bandwidth pressure of the transmission path between the detector and the plate between the data processing module can be relieved, and the data acquisition speed and the data acquisition performance are further improved.

Description

Detector, data acquisition method and device and medical equipment

Technical Field

The present invention relates to the field of medical devices, and in particular, to a detector, a data acquisition method, a data acquisition device, and a medical device.

Background

With the development of science and technology, the pixel size of the detector of a nuclear medicine device (such as an X-ray device) is gradually reduced, or a multi-energy acquisition mode such as a photon counting type detector is presented, so that the data volume acquired by a single scan is larger and larger. Accordingly, a need exists for a nuclear medicine device that has the ability to acquire and/or store larger amounts of data in real time.

However, the inter-board interface between the detector and the data processing module in the nuclear medicine device limits the transmission rate of the radiation data to some extent in the face of large data volume acquisition tasks.

Disclosure of Invention

The embodiments of the present specification aim to solve at least one of the technical problems in the related art to some extent. For this purpose, the embodiment of the present specification proposes a detector, a data acquisition method, a data acquisition device and a medical device.

The embodiment of the specification provides a detector, which comprises a plurality of detection submodules, a processor and a pre-buffer unit, wherein each detection submodule comprises a signal conversion unit;

the signal conversion unit is used for converting the ray analog signals into digital electric signals so as to obtain ray data;

the processor is used for writing the ray data converted by the plurality of signal conversion units into the pre-buffer unit through a first transmission path or reading the ray data from the pre-buffer unit, and outputting the ray data through a second transmission path;

Wherein the transmission rate of the second transmission path is smaller than the transmission rate of the first transmission path.

In an alternative embodiment, the processor includes a plurality of sub-processors, and the pre-cache unit includes a plurality of sub-pre-cache units corresponding to the sub-processors one by one; the first transmission path includes a plurality of first sub-transmission paths, and the second transmission path includes a plurality of second sub-transmission paths;

the detection sub-modules and the sub-processors are arranged in one-to-one correspondence;

the sub-processor is configured to write the radiation data to the sub-pre-buffer unit or read the radiation data from the sub-pre-buffer unit through the first sub-transmission path, and output the radiation data through the second sub-transmission path.

In an alternative embodiment, the processor further includes a plurality of sub-processors and an integrated processor connected to the plurality of sub-processors; the first transmission path includes a plurality of first sub-transmission paths;

the prepositive buffer unit comprises a plurality of subprocessors which are in one-to-one correspondence with the subprocessors, and the detection submodules and the subprocessors are in one-to-one correspondence with each other;

The sub-processor is used for writing the ray data into the sub-pre-cache unit through a first sub-transmission path or reading the ray data from the sub-pre-cache unit and transmitting the ray data to the integrated processor;

the integration processor is used for integrating the ray data output by the plurality of sub-processors and outputting the ray data through the second transmission path.

In an alternative embodiment, the first transmission path is an in-board transmission path.

In an alternative embodiment, the second transmission path is an inter-board transmission path, including wireless transmission and wired transmission modes.

In an alternative embodiment, the pre-cache unit is integrated on the processor; alternatively, the processor is integrated on the signal conversion unit.

In an alternative embodiment, the collecting device includes at least one detector as in any one of the above embodiments and a data processing module, where the detector is connected to the data processing module through a second transmission path, and the data processing module is configured to process line data output by the detector.

An embodiment of the present disclosure provides a data acquisition device, where the data acquisition device includes at least one detector and a data processing module according to any one of the foregoing embodiments, where the detector is connected to the data processing module through a second transmission path, and the data processing module is configured to process line data output by the detector.

In an optional embodiment, the data acquisition device further includes a post-data buffer module, connected to the data processing module, for buffering the radiation data processed by the data processing module.

Embodiments of the present disclosure provide a medical device comprising a data acquisition apparatus as described in any one of the above.

The embodiment of the specification provides a data acquisition method, which comprises the following steps:

acquiring ray data, wherein the ray data are digital electric signals converted from ray analog signals;

storing the ray data into a pre-cache unit through a first transmission path;

and reading the ray data from the pre-buffer unit and outputting the ray data through a second transmission path, wherein the transmission rate of the second transmission path is smaller than that of the first transmission path.

In the above embodiments, the detector includes a plurality of detection submodules, a processor and a pre-buffer unit, and each detection submodule includes a signal conversion unit. Firstly, converting a ray analog signal into a recordable digital electric signal through a signal conversion unit so as to obtain ray data; then, the processor writes the ray data converted by the plurality of signal conversion units into the pre-buffer unit or reads the ray data from the pre-buffer unit through a first transmission path; and finally, outputting the ray data in the front buffer unit by the detector through a second transmission path. The front buffer memory of the ray data obtained by the conversion of the signal conversion unit can be realized, so that the data transmission bandwidth pressure of the transmission path between the detector and the plate between the data processing module can be relieved, and the data acquisition speed and the data acquisition performance can be further improved.

Drawings

FIG. 1a is a schematic diagram of a ray data acquisition structure provided in an embodiment of the present disclosure;

FIG. 1b is a schematic diagram of data collection and buffering provided in an embodiment of the present disclosure;

FIG. 1c is a schematic diagram of a detector provided in an embodiment of the present disclosure;

FIG. 2 is a schematic diagram of a detector provided in an embodiment of the present disclosure;

FIG. 3a is a schematic diagram of a detector provided in an embodiment of the present disclosure;

FIG. 3b is a schematic diagram of a detector provided in an embodiment of the present disclosure;

FIG. 3c is a schematic diagram of a detector provided in an embodiment of the present disclosure;

FIG. 3d is a schematic diagram of a detector provided in an embodiment of the present disclosure;

FIG. 3e is a schematic diagram of a detector provided in an embodiment of the present disclosure;

FIG. 4a is a schematic diagram of a detector provided in an embodiment of the present disclosure;

FIG. 4b is a schematic diagram of a detector provided in an embodiment of the present disclosure;

FIG. 4c is a schematic diagram of a data processing unit according to an embodiment of the present disclosure;

FIG. 5a is a schematic diagram of a detector provided in an embodiment of the present disclosure;

FIG. 5b is a schematic diagram of a detector provided in an embodiment of the present disclosure;

FIG. 6 is a schematic diagram of a radiation data acquisition device according to an embodiment of the present disclosure;

FIG. 7 is a schematic view of a medical device provided in an embodiment of the present disclosure;

fig. 8 is a schematic flow chart of a data acquisition method according to an embodiment of the present disclosure;

fig. 9 is a schematic diagram of a data acquisition device according to an embodiment of the present disclosure.

Detailed Description

Embodiments of the present invention are described in detail below, examples of which are illustrated in the accompanying drawings, wherein like or similar reference numerals refer to like or similar elements or elements having like or similar functions throughout. The embodiments described below by referring to the drawings are illustrative and intended to explain the present invention and should not be construed as limiting the invention.

Related art nuclear medicine devices such as CT devices (Computed Tomography, computed tomography systems) include a radiation data acquisition structure. Referring to fig. 1a, the radiation data acquisition structure includes a plurality of detectors 100 and a data processing module 104. Each detector has a corresponding transmission path 106, and each detector is connected to the data processing module 104 via the transmission path 106. The transmission path 106 may be understood as an inter-board transmission path between the probe 100 and the data processing module 104, and may be a wired transmission mode or a wireless transmission mode. The detector 100 may include a sensor element (referred to as a radiation sensing unit) for converting radiation into an analog electrical signal, and an electronic substrate (referred to as a signal conversion unit) for converting the analog electrical signal into a digital electrical signal. The signal conversion unit of each detector 100 transmits the converted digital electrical signal to the data processing module 104. The data processing module 104 may integrate, process, buffer, etc. the digital electrical signals transmitted by the detector 100, and then transmit the integrated, processed, buffered, etc.

In the related art, since the probe 100 does not have the function of buffering data, the data transmission rate of the transmission path 106 must be greater than the data rate collected by the probe 100, otherwise the data sampling speed will be affected (i.e. the sampling speed cannot be increased more). For example, the transmission path 106 in the related art has a limitation in implementing a scan type such as a cardiac scan, which requires a high scan speed and a large coverage of a single scan; or the detector reduces the data quantity by means of compression and the like before outputting, so that the image quality is reduced; alternatively, by reducing the layer thickness of a single CT scan, the number of scan passes is increased, which can affect the scan quality, such as artifacts caused by inconsistent cardiac motion positions per pass. The transmission paths 106 in the related art are connected by an inter-board transmission path in a wireless manner or a wired manner. Therefore, the larger the data transmission bandwidth requirement is, the more difficult the hardware design of the transmission path between boards is, and the higher the design cost of the transmission path between boards is.

In addition, referring to fig. 1b, in a scenario with an ultra-high data volume (such as a device with a photon counting detector), the time interval between two samples is one integration time period, and before the data is buffered, the data sampled once needs to be transmitted within one integration time (sampling time). I.e. the length of the integration time, affects the amount of data sampled at one time. If the data size is limited, the data accuracy is limited, and the image details cannot be clearly displayed. The ultra-high data volume scene may be a scan scene having a wider field of view (FOV) in the Z direction, and the data volume acquired when the field of view in the Z direction is increased.

While the foregoing exemplarily illustrates the related art, it will be appreciated that the problems associated with the related art are not limited to the X-ray field, but may include the gamma ray field, and the detector structure and method described below may be employed as long as there is a discrepancy between data acquisition and data transmission.

Based on this, the present description embodiment provides a detector. The detector comprises a plurality of detection submodules, a processor and a pre-buffer unit, wherein each detection submodule comprises a signal conversion unit. The signal conversion unit and the pre-buffer unit are provided with a first transmission path. Specifically, the radiation analog signals are converted into recordable digital electric signals through the signal conversion units to obtain radiation data, and then the processor writes the radiation data converted by the plurality of signal conversion units into the pre-buffer unit or reads the radiation data from the pre-buffer unit through the first transmission path. The detector outputs the radiation data in the pre-buffer unit to the data processing module via a second transmission path (i.e. the transmission path 106 described above). Wherein the transmission rate of the second transmission path is smaller than the transmission rate of the first transmission path.

The embodiment of the specification sets the front buffer unit on the detector, so that the data transmission bandwidth of the inter-board transmission path between the detector and the data processing module is not a bottleneck of data transmission anymore when the detector faces the condition of faster integration time and/or acquisition task with large data quantity. The first transmission path between the signal conversion unit in the detector and the front buffer unit is an in-board path in the detector, and the data transmission rate can be improved through hardware to meet the data acquisition speed requirement, and the acquisition speed can be improved through a third party IP core application mode and the like aiming at the in-board path.

The detector provided by the embodiments of the present specification may be applied to any one of an electronic computed tomography (Computed Tomography, CT), a digital subtraction angiography (Digital subtraction angiography, DSA), a digital radiography apparatus (Digital Radiography, DR), a Mobile digital radiography apparatus (Mobile-DR), a Breast X-ray Machine (Breast X-ray Machine), a C-arm X-ray apparatus, or a digital subtraction angiography apparatus (Digital Subtraction Angiograph, DSA), a computer X-ray radiography apparatus (Computed Radiography, CR). The X-ray apparatus using the principle of X-ray phase contrast imaging is of a wide variety. The X-ray source may employ a conventional X-ray tube, which is based on the principle of generating X-rays by impacting a metal target with high-speed particles, a micro-focal spot source, a synchrotron radiation source, etc.

The present embodiments provide a probe, referring to fig. 1c, the probe 100 may include: comprises a plurality of detection sub-modules 340, a processor 310 and a pre-buffering unit 120, each detection sub-module 340 comprising a signal conversion unit 110. The signal conversion unit 110 is configured to convert the radiation analog signal into a digital electrical signal to obtain radiation data; the processor 310 is configured to write the radiation data converted by the plurality of signal conversion units to the pre-buffer unit 120 or read the radiation data from the pre-buffer unit 120 through the first transmission path 130, and output the radiation data through the second transmission path 140. Wherein, the transmission rate of the second transmission path 140 is smaller than the transmission rate of the first transmission path 130.

The plurality of detection sub-modules can increase the scanning area or increase the focus part for scanning. Such as: the A detection sub-module can acquire a ray analog signal obtained when the heart part of the patient is scanned, and the B detection sub-module can acquire a ray analog signal obtained when the liver part of the patient is scanned. The signal conversion unit 110 may be an electronic substrate and/or an integrated circuit of an analog-to-digital converter (Analog to Digital Converter, ADC) or an application specific integrated circuit (Application Specific Integrated Circuit, ASIC). The processor 310 may be a Microcontroller (MCU) which may be used to control the output of the signal conversion unit. Because the analog signal is obtained by collecting the radiation energy, the analog signal is continuous, and the computer equipment can only process discrete specific data, the analog signal obtained by collecting the radiation energy needs to be subjected to analog-to-digital conversion by the signal conversion unit 110, and the radiation data obtained by conversion can be subjected to operation processing by the computer equipment. It should be noted that the process of analog-to-digital conversion may be implemented by means of division sampling, quantization, and encoding.

By providing the pre-buffer unit 120 in the detector, the pre-buffer unit 120 can be used to buffer data in the case of a faster integration time and/or a large data amount of acquisition task, so that the data transmission bandwidth of the inter-board transmission path between the processor 310 and the data processing module 104 will not become a bottleneck of data transmission. The first transmission path between the processor 310 and the pre-cache unit 120 is an intra-board path in the probe, and for the intra-board path, the data transmission rate can be improved by hardware to meet the data acquisition speed requirement, and the acquisition speed can also be improved by a third party IP core application and other modes. The pre-cache unit 120 may be any Random Access Memory (RAM), a Read Only Memory (ROM) type memory, a dynamic hard disk with an access speed meeting the requirement, or a nonvolatile memory, so that if power is off, data can be saved and not lost. It should be noted that, the pre-cache unit may use a new memory that appears with the development of technology and meets the data acquisition speed requirement.

Specifically, by collecting the radiation energy, a radiation analog signal can be obtained. The detection sub-module may perform analog-to-digital conversion on the acquired radiation analog signal through the signal conversion unit 110 included in the detection sub-module, so as to obtain a recordable digital electrical signal, so as to obtain radiation data. The processor 310 is connected to one end of the first transmission path 310, the other end of the first transmission path 130 is connected to the pre-buffer unit 120, and the processor 310 is configured to write the ray data converted by the plurality of signal conversion units into the pre-buffer unit 120 or read the ray data from the pre-buffer unit 120 through the first transmission path 130. The pre-buffer unit 120 buffers the ray data. The processor 310 may output the ray data buffered in the pre-buffer unit 120 through the second transmission path 140.

The detector comprises a plurality of detection submodules, a processor and a front buffer unit, and each detection submodule comprises a signal conversion unit. Firstly, converting a ray analog signal into a recordable digital electric signal through a signal conversion unit so as to obtain ray data; then, the processor writes the ray data converted by the plurality of signal conversion units into the pre-buffer unit or reads the ray data from the pre-buffer unit through a first transmission path; and finally, outputting the ray data in the front buffer unit by the detector through a second transmission path. The front buffer memory of the ray data obtained by conversion of the signal conversion unit is realized, the transmission rate of the second transmission path can be smaller than that of the first transmission path, the data transmission bandwidth pressure of the inter-board transmission path between the detector and the data processing module can be relieved, and the data acquisition speed and performance are further improved.

In some embodiments, referring to fig. 2, the detection sub-module 340 includes a radiation sensing unit 210 connected to an input end of the signal conversion unit 110, and is configured to collect radiation and output a radiation analog signal to the signal conversion unit 110; the radiation sensing unit 210 includes at least one of a scintillator sensor or a semiconductor sensor.

The energy of the radiation emitted by the tube is not consistent after the radiation is attenuated by different tissues of a human body, and the intensity of a radiation signal received by the radiation sensing unit depends on the density of the tissues in a human body section of the part. Tissues with high density, such as bones, absorb more rays, and signals received by the ray sensing units are weaker; tissues with lower density, such as fat, absorb less radiation, and the signals obtained by the radiation sensing unit are stronger. The tissue property can be judged by the intensity of the signal received by the ray sensing unit.

In particular, the detector 100 includes a radiation sensing unit 210. The radiation sensing unit 210 may collect radiation passing through a human body and then process the collected radiation to obtain a radiation analog signal. The radiation sensing unit 210 transmits the obtained radiation analog signal to the signal conversion unit 110.

For example, for a radiation analog signal input by a scintillator sensor, analog amplitude values of all input pixels (pixels) are converted into digital signals in one sampling period. For the radiation analog signal input to the semiconductor sensor, photon pulses of corresponding energy segments of all input pixel arrays are converted into photon count values in one sampling period.

According to the detector, rays are collected through the ray sensing unit included in the detector, and the ray analog signals are output to the signal conversion unit, so that the rays attenuated by different tissues of a human body are collected.

In some embodiments, the processor 310 is integrated on the signal conversion unit 110, i.e. the signal conversion unit 110 is configured with the processor 310, the processor 310 being arranged to write the radiation data to the pre-cache unit 120 or to read the radiation data from the pre-cache unit 120. Alternatively, the pre-cache unit 120 is integrated on the processor 310.

In some cases, a signal conversion unit with a processor may be employed, as the hardware design of the medical device may be spatially limited and there is a need for conditioning the radio signal. For example, the processor configured for the signal conversion unit may be a Microcontroller (MCU) which may be used to control the output of the signal conversion unit.

Specifically, the signal conversion unit 110 is connected to the pre-buffer unit 120 and the radiation sensing unit 210, respectively. Referring to fig. 3a, the processor 310 may be located between the signal conversion unit 110 and the pre-buffer unit 120. The processor 310 may write the digital electric signal converted by the signal conversion unit 110, that is, the radiation data, to the pre-buffer unit 120, or the processor 310 may read the radiation data from the pre-buffer unit 120.

For example, referring to fig. 3b, the signal conversion unit 110 includes a signal converter, and the processor 310 is also integrated inside the signal conversion unit 110. Referring to fig. 3c, the pre-buffer unit 120 may also be integrated inside the signal conversion unit 110.

It is understood that the processor 310 may also be located between the radiation sensing unit 210 and the signal conversion unit 110, and the processor 310 may be configured to control the input of the radiation sensing unit 210 to the signal conversion unit 110.

The detector, the signal conversion unit is provided with a processor, and the processor writes the ray data into the pre-buffer unit or reads the ray data from the pre-buffer unit. The pre-cache unit may be integrated on the processor; in the alternative, the processor may be integrated on the signal conversion unit. The data transmission bandwidth pressure of the transmission path between the detector and the data processing module can be relieved without affecting the data quality.

In some embodiments, referring to fig. 3d, the processor 310 includes a plurality of sub-processors 320, and the pre-cache unit 120 includes a plurality of sub-pre-cache units 330 corresponding to the sub-processors 320 one by one; the first transmission path 130 includes a plurality of first sub-transmission paths 350, and the second transmission path 140 includes a plurality of second sub-transmission paths 360; the detection sub-modules 340 are disposed in one-to-one correspondence with the sub-processors 320, and the sub-processors 320 are configured to write the radiation data into the sub-pre-buffer 330 or read the radiation data from the sub-pre-buffer 330 through the first sub-transmission path 350, and output the radiation data through the second sub-transmission path 360.

Wherein the sub-processor may be a Microcontroller (MCU) which may be used to control the output of the signal conversion unit. The sub-pre-cache unit can adopt various Random Access Memories (RAMs), read-only memories (ROMs) and dynamic hard disks with access speed meeting requirements, and nonvolatile memories, so that data can be saved and not lost under the condition of power failure. It should be noted that, the sub-pre-cache unit may use a new memory that appears with the development of technology and meets the data acquisition speed requirement. Each detection submodule comprises a signal conversion unit.

In some cases, the probe may include a plurality of sub-processors, a plurality of sub-pre-cache units, and a plurality of probe sub-modules. The collection and processing efficiency of the ray data can be improved by arranging a plurality of groups of devices. Each group of devices may include at least one sub-processor, a sub-pre-cache unit, and a detection sub-module. Each group of equipment can be mutually independent, for example, the A sub-processor corresponding to the A detection sub-module can transmit the ray data obtained by the A detection sub-module to the A sub-pre-cache unit corresponding to the A sub-processor; the ray data obtained by the B detection sub-module can be transmitted to the B sub-pre-caching unit corresponding to the B sub-processor through the B sub-processor corresponding to the B detection sub-module. The plurality of detection sub-modules can collect the ray simulation signals of the same focus position and can also detect the ray simulation signals of different focus positions.

Specifically, with continued reference to fig. 3d, the probe may include a plurality of sub-processors 320 and each sub-processor 320 has a sub-pre-cache unit 330 corresponding thereto. The detection sub-module may perform analog-to-digital conversion on the acquired radiation analog signal through the signal conversion unit 110 included in the detection sub-module, so as to obtain a recordable digital electrical signal, so as to obtain radiation data. The sub-processor 320 corresponding to the detection sub-module is configured to write the converted radiation data to the sub-pre-buffer unit 330 corresponding to the sub-processor or read the radiation data from the sub-pre-buffer unit 330 through the first transmission path 130. The sub-processor 320 may read the ray data from the sub-pre-buffer 330 corresponding to the sub-processor, and output the ray data to the data processing module 104 through the second sub-transmission path 360 for data processing.

Illustratively, the a-detection sub-module may perform analog-to-digital conversion on the acquired radiation analog signal by an a-signal conversion unit included inside the a-detection sub-module, to obtain a recordable digital electrical signal, so as to obtain radiation data. The A sub-processor is used for writing the converted ray data into the A sub-pre-cache unit or reading the ray data from the A sub-pre-cache unit through a first transmission path. The B detection sub-module can carry out analog-to-digital conversion on the acquired ray analog signals through a B signal conversion unit contained in the B detection sub-module to obtain recordable digital electric signals so as to obtain ray data. The B sub-processor is used for writing the converted ray data into the B sub-pre-cache unit or reading the ray data from the B sub-pre-cache unit through the first transmission path. The sub-processor A can read the ray data from the sub-pre-cache unit A, the sub-processor B can read the ray data from the sub-pre-cache unit B, and the sub-processor A and the sub-processor B output the ray data to the same data processing module through a second sub-transmission path so as to process and integrate the data.

The detector comprises a plurality of sub-processors, wherein the pre-caching unit comprises a plurality of sub-pre-caching units which are in one-to-one correspondence with the sub-processors, the detection sub-modules are arranged in one-to-one correspondence with the sub-processors, and the sub-processors are used for writing ray data into the sub-pre-caching units or reading the ray data from the sub-pre-caching units through a first sub-transmission path and outputting the ray data through a second sub-transmission path. The data transmission bandwidth pressure of the transmission path between the detector and the data processing module can be relieved without affecting the data quality.

In some embodiments, referring to fig. 3e, the processor further includes a plurality of sub-processors 320 and an integrated processor 370 connected to the plurality of sub-processors; the first transmission path includes a plurality of first sub-transmission paths; the pre-buffer unit 120 includes a plurality of sub-pre-buffer units 330 corresponding to the sub-processors one by one, the detection sub-modules 340 are arranged corresponding to the sub-processors 320 one by one, and the sub-processors 320 are configured to write the ray data into the sub-pre-buffer units 330 through the first sub-transmission paths 350, or read the ray data from the sub-pre-buffer units 330, and transmit the ray data to the integration processor 370, where the integration processor is configured to integrate the ray data output by the plurality of sub-processors and output the ray data through the second transmission paths 140.

In some cases, the integration processor may be used to perform data integration on the radiation data, or the integration processor may be used to perform operations of data integration and data processing (e.g., lossless compression, lossy compression, data alignment, data extraction, data retransmission, data transmission, etc.) on the radiation data. The integrated processor may be a Microcontroller (MCU) which may be used to control the output of the signal conversion unit.

Specifically, with continued reference to fig. 3e, the probe may include a plurality of sub-processors 320 and each sub-processor 320 has a sub-pre-cache unit 330 corresponding thereto. The sub-processor 320 is configured to write the ray data converted by the signal conversion unit 110 corresponding to the sub-processor to the sub-pre-buffer unit 330 corresponding to the sub-processor or read the ray data from the sub-pre-buffer unit 330 through the first transmission path 130. The sub-processor 320 may read the radiation data from the sub-pre-cache unit 330 corresponding to the sub-processor, and output the radiation data to the integration processor 370, and the integration processor 370 integrates the radiation data read from the sub-pre-cache unit 330. The integrated radiation data is then transmitted to the data processing module 104 via the second transmission path 140.

The detector further comprises a plurality of sub-processors and an integration processor connected with the plurality of sub-processors, the pre-caching unit comprises a plurality of sub-pre-caching units corresponding to the sub-processors one by one, the detection sub-modules and the sub-processors are arranged one by one, the sub-processors are used for writing ray data into the sub-pre-caching units through a first sub-transmission path or reading the ray data from the sub-pre-caching units and transmitting the ray data to the integration processor, the integration processor is used for integrating the ray data output by the plurality of sub-processors and outputting the ray data through a second transmission path, and the first transmission path comprises a plurality of first sub-transmission paths. The data transmission bandwidth pressure of the transmission path between the detector and the data processing module can be relieved without affecting the data quality.

In some embodiments, referring to FIG. 4a, a processor may employ a data processing unit 410; the radiation data is written to the pre-cache unit 120 or read from the pre-cache unit 120 by the data processing unit 410.

The data processing unit 410 may be at least one of a field programmable gate array (Field Programmable Gate Array, FPGA), a central processing unit (Central Processing Unit, CPU), a graphics processor (Graphics Processing Unit, GPU), an application specific integrated circuit (Application Specific Integrated Circuit, ASIC), and the like. The data processing unit 410 may configure the operation mode of the signal conversion unit 110 and/or buffer and process data. The data processing unit 410 may perform data integration, lossless compression, lossy compression, data alignment, data extraction, data retransmission, data transmission, and the like. Referring to fig. 4b, the data processing unit 410 includes a pre-cache unit 120 and a data processor, wherein the pre-cache unit 120 is integrated inside the data processing unit 410.

Specifically, the data processing unit 410 is connected to the signal conversion unit 110 and the pre-buffer unit 120, respectively, the signal conversion unit 110 and the data processing unit 410 may perform data transmission through an on-board data transmission interface designed by hardware, and a maximum transmission rate between the signal conversion unit 110 and the data processing unit 410 may be denoted as KA. The data processing unit 410 may write the radiation data to the pre-buffer unit 120, or the data processing unit 410 may read the radiation data from the pre-buffer unit 120, and the maximum transmission rate of the output of the data processing unit 410 may be denoted KC. The maximum transmission rate KC at the output of the data processing unit 410 may be smaller than the maximum transmission rate KA between the signal conversion unit 110 and the data processing unit 410 on the premise of satisfying the data acquisition performance of the detector 100.

For example, referring to fig. 4c, the data processing unit 410 may determine whether there is block data to be written into the pre-cache unit 120, and if so, the data processing unit 410 writes the block data into the pre-cache unit 120; if not, the data processing unit 410 determines whether there is block data to be output, if so, the data processing unit 410 reads the block data from the pre-cache unit 120 and outputs the read block data, and if not, continues to determine whether there is block data to be written to the pre-cache unit 120. Wherein the block data represents quantization of data written into the pre-buffer unit 120 or read out of the pre-buffer unit 120 each time.

The detector also comprises a data processing unit connected with the signal conversion unit; the data processing unit may write the radiation data to the pre-cache unit or read the radiation data from the pre-cache unit. The data transmission bandwidth pressure of the transmission path between the detector and the data processing module can be relieved and the data content is not affected.

In some embodiments, referring to fig. 5a, the probe 100 further comprises a post-buffer unit 510 connected to the data processing unit 410; the post-buffer unit 510 is configured to buffer the ray data processed by the data processing unit 410.

Specifically, the data processing unit 410 may obtain the ray data that is not subjected to the data processing through the pre-buffer unit 120. The data processing unit 410 may perform data processing (e.g., quantization) on the unprocessed radiation data, and may buffer the processed radiation data in the post-buffer unit 510. The post-cache unit 510 may be any Random Access Memory (RAM), a Read Only Memory (ROM) type memory, a dynamic hard disk with an access speed meeting the requirement, or a nonvolatile memory, so that if power is off, data can be saved and not lost. It should be noted that, the pre-cache unit may use a new memory that appears with the development of technology and meets the data acquisition speed requirement.

For example, referring to fig. 5b, the data processing unit 410 includes a post-cache unit 510 and a data processor. Wherein the post-cache unit 510 may be integrated within the data processing unit 410.

In some embodiments, the pre-cache unit 120 employs at least one of double rate synchronous dynamic random access memory, quad data rate static random access memory, or single data rate static random access memory; and/or

The post-cache unit employs 510 at least one of a double rate synchronous dynamic random access memory, a quad data rate static random access memory, or a single data rate static random access memory.

Among them, the pre-cache unit 120 may preferably use a memory with a high transmission speed and a large cache capacity, and the memory may have an influence on the access speed or the operation complexity. The post-cache unit 510 may be preferably a memory with high transmission speed and large cache capacity, which may affect the access speed or the complexity of the operation. The pre-cache unit 120 and the post-cache unit 510 may be any carrier having a cache function. Such as: DDR, DDRX, QDR, SDRAM, hard disk, etc. The pre-cache unit 120 and post-cache unit 510 may also be a combination of different types of caches.

The present embodiments provide a radiation data acquisition device comprising a detector 100 according to any of the above embodiments.

In some embodiments, referring to fig. 6, the number of detectors 100 is a plurality; the radiation data acquisition device 600 further includes:

the data processing module 104 is connected with the plurality of detectors 100 through the second transmission paths 140, and is used for processing the ray data output by the plurality of detectors 100;

the post-data buffer module 620 is connected to the data processing module 104, and is configured to buffer the ray data processed by the data processing module 104.

In particular, the detectors B1 to BN convert radiation into recordable digital electrical signals, which are then buffered and/or processed to obtain radiation data. The detectors B1 to BN output the ray data to the data processing module 104 through the second transmission path 140, the data processing module 104 may perform an integrating or/and processing or/and buffering operation on the ray data, and then the data processing module 104 outputs the processed ray data to the post-data buffering module 620. The post-data caching module 620 caches the ray data processed by the data processing module 104. The data processing may be lossless compression or lossy compression of the data, among other things. The post-data caching module 620 may be integrated within the data processing module 104.

In some embodiments, when the output bandwidth of the data processing module 104 is smaller than the input bandwidth, the data processing module 104 may satisfy the scan task (DDD task) by outputting only effective field of view (FOV) data. By providing the pre-buffer unit 110 within the detector 100, limitations of the application scenario in which the data output of the radiation detection 100 is integrated in a faster time and/or a large data volume exist in the ddd task even though the input bandwidth of the data processing module 104 is larger than the output bandwidth. The DDD task may not interact with the acquisition and/or processing of data by the probe 100. That is, there is no concept of overlapping each other. The DDD tasks may or may not be performed concurrently with the acquisition and/or processing of data by the detector.

The ray data acquisition device is provided with the data processing modules respectively connected with the plurality of detectors and the rear data caching module connected with the data processing modules, so that ray data processed by the data processing modules can be cached, and further the requirements of acquisition tasks of faster integration time and/or large data volume are met.

The present specification embodiment provides a medical device comprising the data acquisition apparatus of any one of the above embodiments.

In some embodiments, referring to fig. 7, the medical device includes a slip ring assembly 710 coupled to the data processing module; wherein the transmission rate of the slip ring assembly 710 is less than the transmission rate of the first transmission path 130.

The slip ring is one of core components of the CT system and is used for transmitting power, signals and data between a rotating end and a fixed end of the CT system. The medical images that are ultimately presented by CT scanning are generally classified into real-time and off-line imaging images. The real-time imaging image requires that the CT data acquisition system be capable of transmitting data in real time. The slip ring assembly 710 is typically a transmission bottleneck on the way from the detector 100 to the imaging system 720. The transmission rate of the transmission path 106 is both sufficient for the acquisition rate of the detector and greater than the transmission rate of the slip ring assembly 710.

Specifically, slip ring assembly 710 is coupled to data processing module 104 and imaging system 720, respectively. The radiation data processed by the data processing module 104 may be transmitted to an imaging system 720 via a slip ring assembly 710.

The medical equipment comprises the slip ring assembly connected with the data processing module, so that the threshold requirement on hardware design is reduced, and the design cost is also reduced.

The embodiment of the present disclosure provides a data acquisition method, referring to fig. 8, the data acquisition method may include the following steps:

S810, acquiring ray data, wherein the ray data are digital electric signals converted from ray analog signals.

S820, the ray data is stored into a pre-buffer unit through a first transmission path.

S830, the ray data is read from the front buffer unit and output through a second transmission path. Wherein the transmission rate of the second transmission path is smaller than the transmission rate of the first transmission path.

Specifically, the radiation analog signal obtained by the radiation sensing unit is input to the signal conversion unit, which converts the radiation analog signal into a recordable digital electrical signal, i.e., radiation data, to obtain the radiation data. The front-end buffer unit is connected with the signal conversion unit through a first transmission path, and the ray data can be transmitted to the front-end buffer unit through the first transmission path and buffered. The detector can read the ray data from the pre-buffer unit and output the ray data buffered to the pre-buffer unit through the second transmission path.

Firstly, converting a ray analog signal into a recordable digital electric signal through a signal conversion unit to obtain ray data; then, the ray data is cached to the front-end caching unit through a first transmission path between the signal conversion unit and the front-end caching unit; and finally outputting the ray data through a second transmission path. The data transmission bandwidth pressure of the interface between the detector and the data processing module can be relieved, and the data acquisition speed and performance are further improved.

In some embodiments, the data acquisition method is applied to a device having real-time imaging requirements, and the data acquisition method may further include: and under the condition that the transmission of the ray data required by the real-time imaging is completed and the second transmission path is in an idle state, transmitting the ray data required by the non-real-time imaging through the second transmission path.

Wherein the medical images that the medical device generally ultimately presents are classified into real-time and off-line imaging images. The scanning and imaging of the real-time imaging image are performed simultaneously, so that the medical device is required to be able to transmit data in real time, and then transmit the acquired and processed radiation data to the imaging system.

Specifically, after the transmission of the radiation data required for real-time imaging is completed, the image data is required to be imaged under the transmission line. And transmitting data required for off-line image formation to the image formation system under the condition that the second transmission path is in an idle state. The transmission of the off-line image data in the second transmission path needs to be suspended when the second transmission path is in a non-idle state or when the medical device has a scanning requirement.

According to the data acquisition method, under the condition that the transmission of the ray data required by real-time imaging is completed and the second transmission path is in an idle state, the ray data required by non-real-time imaging is transmitted through the second transmission path. By transmitting the data required for image creation under the line at idle time, the waiting time of the data required for image creation under the line can be reduced without affecting the next scan.

Referring to fig. 9, the data acquisition device 900 according to the embodiment of the present disclosure includes: an analog-to-digital conversion module 910, a data buffer module 920, and a data transmission module 930.

The analog-to-digital conversion module 910 obtains radiation data, which is a digital electrical signal converted from a radiation analog signal.

The data buffer module 920 stores the ray data into the pre-buffer unit through the first transmission path.

The data transmission module 930 reads the radiation data from the pre-buffer unit and outputs the radiation data through a second transmission path, where a transmission rate of the second transmission path is smaller than a transmission rate of the first transmission path.

For a specific description of the data acquisition device, reference may be made to the description of the data acquisition method hereinabove, and the description thereof will not be repeated here.

The terms "first", "second", etc. used in the embodiments of the present specification are used for descriptive purposes only and are not to be construed as indicating or implying relative importance or implicitly indicating the number of technical features indicated in the embodiments. Thus, the definition of a term "first," "second," or the like in an embodiment of this specification can expressly or implicitly indicate that at least one such feature is included in the embodiment. In the description of the present specification, the word "plurality" means at least two or more, for example, two, three, four, etc., unless explicitly defined otherwise in the embodiments.

While embodiments of the present invention have been shown and described above, it will be understood that the above embodiments are illustrative and not to be construed as limiting the invention, and that variations, modifications, alternatives and variations may be made to the above embodiments by one of ordinary skill in the art within the scope of the invention.

It should be noted that the logic and/or steps represented in the flowcharts or otherwise described herein, for example, may be considered as a ordered listing of executable instructions for implementing logical functions, and may be embodied in any computer-readable medium for use by or in connection with an instruction execution system, apparatus, or device, such as a computer-based system, processor-containing system, or other system that can fetch the instructions from the instruction execution system, apparatus, or device and execute the instructions. For the purposes of this description, a "computer-readable medium" can be any means that can contain, store, communicate, propagate, or transport the program for use by or in connection with the instruction execution system, apparatus, or device. More specific examples (a non-exhaustive list) of the computer-readable medium would include the following: an electrical connection (electronic device) having one or more wires, a portable computer diskette (magnetic device), a Random Access Memory (RAM), a read-only memory (ROM), an erasable programmable read-only memory (EPROM or flash memory), an optical fiber device, and a portable compact disc read-only memory (CDROM). Additionally, the computer-readable medium may even be paper or other suitable medium upon which the program is printed, as the program may be electronically captured, via, for instance, optical scanning of the paper or other medium, then compiled, interpreted or otherwise processed in a suitable manner, if necessary, and then stored in a computer memory.

Claims

1. The detector is characterized by comprising a plurality of detection submodules, a processor and a front-end buffer unit, wherein each detection submodule comprises a signal conversion unit;

2. The detector of claim 1, wherein the processor comprises a plurality of sub-processors, and the pre-cache unit comprises a plurality of sub-pre-cache units in one-to-one correspondence with the sub-processors; the first transmission path includes a plurality of first sub-transmission paths, and the second transmission path includes a plurality of second sub-transmission paths;

3. The detector of claim 1, wherein the processor further comprises a plurality of sub-processors and an integrated processor coupled to the plurality of sub-processors; the first transmission path includes a plurality of first sub-transmission paths;

4. The detector of claim 1, wherein the first transmission path is an in-board transmission path.

5. The detector of claim 1, wherein the second transmission path is an inter-board transmission path, including wireless transmission and wired transmission.

6. The detector of claim 1, wherein the pre-cache unit is integrated on the processor; or,

The processor is integrated on the signal conversion unit.

7. A data acquisition device comprising at least one detector as claimed in any one of claims 1 to 6 and a data processing module, the detector being connected to the data processing module via a second transmission path, the data processing module being arranged to process line data output by the detector.

8. The data acquisition device of claim 7, further comprising a post-data caching module coupled to the data processing module for caching the radiation data processed by the data processing module.

9. A medical device, characterized in that it comprises a data acquisition device according to any one of claims 7 or 8.

10. A method of data acquisition, the method comprising:

storing the ray data into a pre-cache unit through a first transmission path;