Background
Cancer is the most common type of malignancy, which is the first killer threatening human health. Currently, global cancer cases present a rapidly growing situation, with new cases coming mainly from developing countries. Because of the characteristics of high mortality, high disability rate, large medical burden and the like, malignant tumors become a public health problem and even a social problem which are important to be paid attention to in the world. Of the patient's lethal factors caused by cancer, tumor metastasis is the most important factor.
Currently, studies on tumor metastasis are mainly performed in small animals typified by mice and rats. In the specific study, a tumor disease model is firstly established on a small animal, and then the physiological-pathological characteristics of tumor metastasis are studied, new cancer diagnosis technology is developed, anti-tumor drugs are developed, and the curative effect evaluation is carried out on the drugs. In various methods for researching small animals, the whole body living body imaging technology of the small animals can observe the whole body of the same batch of small animals at different time points for a long time, greatly reduce the experimental cost, acquire repeated and reliable experimental data, and effectively observe the small animals in early tumor metastasis by means of a high-sensitivity molecular probe so as to realize whole-course monitoring of the whole tumor cell metastasis process. The main imaging technologies involved include structural imaging such as computed tomography (Computed Tomography, CT), magnetic resonance imaging (Magnetic Resonance Imaging, MRI) and Ultrasound imaging (Ultrasound), and functional imaging such as photoacoustic imaging (Photoacoustic Imaging), positron emission tomography (Positron Emission Tomography, PET) and single photon emission computed tomography (Single Photon Emission Computed Tomography, SPECT). However, the information acquired by these single-mode imaging techniques has a certain limitation, and cannot fully reflect the complex specificity of the organism, so that the research on tumor metastasis cannot provide comprehensive and accurate information.
In view of the above-mentioned shortcomings of the single-modality imaging technique, the prior art proposes a multi-modality imaging technique combining structural and functional information, and the multi-modality imaging technique is increasingly being applied to whole-body living body imaging of small animals, for example, the multi-modality imaging technique combining PET and CT has become a clinical reference standard of multi-modality molecular imaging, which has demonstrated value in predicting the efficacy of new adjuvant therapy and new targeted therapy, and has recently been used to detect early tumor metastasis, and the multi-modality imaging technique combining optical imaging and PET has been used to detect lymphangiogenesis induced during tumor metastasis.
However, in the prior art, the whole-body living body multi-mode imaging technology of the small animals has certain defects. For example, in PET-CT imaging, the accuracy and resolution of PET can be improved by means of a high-energy photon attenuation coefficient map obtained from a CT image, but near-infrared photons are more easily affected by tissue light absorption coefficients relative to high-energy photons than PET or SPECT, so that better imaging effects can be obtained by utilizing an attenuation correction concept in optical imaging. In addition, in cancer treatment, due to the excessively low spatial resolution of PET/SPECT, it is difficult to accurately describe the targeting and aggregation of drugs, and in order to obtain the overall and local drug metabolism simultaneously, dual-mode probes that can respond to the optical modality are often used for drug assessment and analysis. However, the optical imaging technology can cause the imaging depth to be only about 1 millimeter due to the strong scattering effect of organisms, so that the application is limited. In addition, in the modes capable of providing high-resolution structural imaging, CT imaging has advantages in terms of displaying anatomical structures, morphology, density and the like, has high imaging speed, and can also enhance the contrast of soft tissues by injecting contrast agents, adopting energy spectrum imaging or phase contrast imaging, but excessive X-ray radiation can change the physiological structure of small animals and influence the accurate judgment of the cancer development and metastasis process and drug action. In long-term longitudinal studies of small animals using in vivo imaging techniques, it is also necessary to ensure that the small animals are exposed to as low a dose of radiation as possible to mitigate their physiological effects on the small animals. Therefore, the existing living body whole body multimode imaging technology for the small animals still has the problems of low image resolution, small imaging depth and large radiation dose in specific application.
Disclosure of Invention
The invention aims to provide a multimode imaging system which aims to solve the technical problems of low image resolution, small imaging depth and large radiation dose of the existing living body whole body multimode imaging technology of small animals in specific application.
In order to achieve the purpose, the multi-mode imaging system comprises a display, multi-mode imaging equipment and a host electrically connected between the display and the multi-mode imaging equipment, wherein an image reconstruction and processing subsystem is arranged in the host, an animal scanning control subsystem, a static computer tomography subsystem and a photoacoustic imaging subsystem are arranged in the multi-mode imaging equipment, the static computer tomography subsystem comprises an electronic control circuit, a multi-beam carbon nano X-ray source array for generating X rays required by static computer tomography scanning, a photon counting detector for collecting and high-speed processing computer tomography projection data and a power supply for supplying power to the multi-beam carbon nano X-ray source array, and the multi-beam carbon nano X-ray source array, the photon counting detector and the power supply are electrically connected with the electronic control circuit.
Optionally, the multi-beam carbon nano X-ray source array includes a plurality of carbon nano X-ray sources that the array distributes, the carbon nano X-ray source includes vacuum cavity, carbon nano field emission cathode, grid, focusing electrode and positive pole, carbon nano field emission cathode the grid, focusing electrode with positive pole is all located in the vacuum cavity, positive pole interval slope is located carbon nano field emission cathode's top, grid with focusing electrode is all located carbon nano field emission cathode with between the positive pole, just the grid is located focusing electrode with carbon nano field emission cathode is between, the vacuum cavity is equipped with and is located the X ray exit window of positive pole side.
Optionally, the carbon nano field emission cathode comprises a substrate and a cold cathode material layer arranged on the surface of the substrate.
Optionally, the substrate is a metal base plate or a silicon wafer coated with a metal coating, and/or,
The cold cathode material layer is made of carbon nanotubes or graphene and a mixture of the carbon nanotubes and the graphene.
Optionally, the number of the carbon nano X-ray sources is 90-180, and/or,
Each carbon nano X-ray source is distributed in a circular array or a polygonal array, and/or,
The X-ray exit window is an aluminium window or a beryllium window, and/or,
The vacuum degree of the vacuum cavity is 10-6 mm Hg to 10-11 mm Hg, and/or,
The grid comprises a bracket and a grid mesh arranged on the bracket, wherein the grid mesh is provided with an opening for allowing electrons to penetrate, and/or,
The anode forms an inclination angle of 5-15 degrees relative to the horizontal plane and/or,
The relative distances among the carbon nano field emission cathode, the grid electrode, the focusing electrode and the anode are adjusted through an insulating gasket.
Optionally, the photoacoustic imaging subsystem comprises an optical subsystem for providing excitation light required by photoacoustic imaging, an acoustic subsystem for collecting multiple photoacoustic signals, and a photoacoustic coplanarity adjusting subsystem for adjusting the incidence angle of the excitation light to ensure that the optical signal and the acoustic signal remain coplanar.
Optionally, the optical subsystem includes excitation light source, lens group, optic fibre bundle and cyclic annular light bowl, the lens group is located excitation light source with between the optic fibre bundle, the optic fibre bundle is fixed in on the cyclic annular light bowl and be located between lens group and the cyclic annular light bowl.
Optionally, the acoustic subsystem comprises a high-frequency ultrasonic transducer array for detecting acoustic signals and a multi-channel data acquisition platform for processing the detected signals of the high-frequency ultrasonic transducer array.
Optionally, the high-frequency ultrasonic transducer array comprises a plurality of high-frequency ultrasonic transducers distributed in an array, and the high-frequency ultrasonic transducers are of a multi-layer laminated structure and comprise an acoustic lens, a matching layer, a piezoelectric composite material layer and an insulating backing layer which are sequentially laminated from front to back.
Optionally, the animal scanning control subsystem includes a positioning structure for positioning an animal and an electromechanical control platform for driving the positioning structure and the animal on the positioning structure to move in a vertical direction, and/or,
The image reconstruction and processing subsystem comprises an image reconstruction module carrying an image reconstruction algorithm, an image calibration module carrying image correction and registration software, an image fusion module carrying multi-mode image fusion software and an information output module carrying information extraction and display software.
The multimode imaging system provided by the invention adopts a multimode imaging technology formed by combining the static CT imaging subsystem and the photoacoustic imaging subsystem, realizes synchronous acquisition of the structure and function information of the small animal, and has the advantages of high image resolution, high imaging speed, large imaging depth, low radiation dose and long-term monitoring compared with the existing multimode imaging system. Specifically, compared with the prior art, the invention has the following beneficial effects:
(1) The static CT imaging subsystem adopts the multi-beam carbon nano X-ray source array, does not need mechanical rotation, can realize high-speed CT scanning by only carrying out quick switching among all carbon nano X-ray sources, overcomes the limit of mechanical rotation speed, has higher imaging speed, eliminates artifacts caused by movement, and can obtain higher spatial resolution. In addition, the multi-beam carbon nano X-ray source array can perform high-speed pulse emission, so that the invalid radiation dose in the CT scanning process is greatly reduced, and the ultra-low radiation effect is further realized.
(2) Different from the optical imaging technology, the spatial resolution of the photoacoustic imaging sub-technology is derived from ultrasonic signals, and the ultrasonic scattering of biological tissues is weaker than the light scattering by two orders of magnitude, so that the photoacoustic imaging technology has high optical contrast and the capability of high-resolution imaging of deep tissues by ultrasound, and meanwhile, the molecular probe has the advantages of high sensitivity, no radioactivity and high specificity.
(3) The fusion of the static CT imaging technology and the photoacoustic imaging technology has the characteristics of complementary advantages, mutual coordination and mutual contrast, on one hand, by means of the advantages of high static CT imaging resolution and ultralow radiation, three-dimensional visualization is easy to perform to locate tumor tissues, and on the other hand, the advantages of excellent soft tissue contrast and high sensitivity of photoacoustic imaging are utilized, so that early accurate diagnosis of tumor metastasis and accurate description of drug metabolism can be realized.
Detailed Description
The following description of the embodiments of the present invention will be made clearly and fully with reference to the accompanying drawings, in which it is evident that the embodiments described are only some, but not all embodiments of the invention. All other embodiments, which can be made by those skilled in the art based on the embodiments of the invention without making any inventive effort, are intended to be within the scope of the invention.
It should be noted that all directional indicators (such as up, down, left, right, front, and rear are used in the embodiments of the present invention) are merely for explaining the relative positional relationship, movement conditions, and the like between the components in a certain specific posture (as shown in the drawings), and if the specific posture is changed, the directional indicators are changed accordingly.
It will also be understood that when an element is referred to as being "mounted" or "disposed" on another element, it can be directly on the other element or intervening elements may also be present. When an element is referred to as being "connected" to another element, it can be directly connected to the other element or intervening elements may also be present.
Furthermore, the description of "first," "second," etc. in this disclosure is for descriptive purposes only and is not to be construed as indicating or implying a relative importance or implicitly indicating the number of technical features indicated. Thus, a feature defining "a first" or "a second" may explicitly or implicitly include at least one such feature. In addition, the technical solutions of the embodiments may be combined with each other, but it is necessary to base that the technical solutions can be realized by those skilled in the art, and when the technical solutions are contradictory or cannot be realized, the combination of the technical solutions should be considered to be absent and not within the scope of protection claimed in the present invention.
As shown in fig. 1 and fig. 2, the multimode imaging system provided by the embodiment of the invention includes a display 100, a multimode imaging device 200, and a host 300 electrically connected between the display 100 and the multimode imaging device 200, an image reconstruction and processing subsystem (not shown) is disposed in the host 300, an animal scanning control subsystem 210, a static computed tomography subsystem 220 (i.e. a static CT imaging subsystem), and a photoacoustic imaging subsystem 230 are disposed in the multimode imaging device 200, the static computed tomography subsystem 220 includes an electronic control circuit 221, a multi-beam carbon nano X-ray source array 222 for generating X-rays 500 required for static computed tomography scanning, a photon counting detector 223 for computed tomography projection data acquisition and high-speed processing, and a power supply 224 for supplying power to the multi-beam carbon nano X-ray source array 222, and the multi-beam carbon nano X-ray source array 222, the photon counting detector 223, and the power supply 224 are all electrically connected to the electronic control circuit 221. The multimode imaging device 200 is mainly used for scanning and imaging the animal 400, the host 300 is mainly used for processing information of the multimode imaging device 200, and the display 100 is mainly used for intuitively outputting the information processed by the host 300. Wherein, in the multimode imaging device 200, the animal scanning control subsystem 210 is mainly used for carrying the animal 400 and carrying the animal 400 for movement, the static computed tomography imaging subsystem 220 is mainly used for imaging the structure of the animal 400, the photoacoustic imaging subsystem 230 is mainly used for imaging the function of the animal 400,
Specifically, in the embodiment of the invention, the static CT imaging subsystem of the multi-beam carbon nano X-ray source array 222 is adopted, mechanical rotation is not needed, and high-speed CT scanning can be realized only by rapidly switching among the carbon nano X-ray sources 2220, and the static CT system overcomes the limit of mechanical rotation speed, has higher imaging speed and eliminates artifacts caused by movement, thereby obtaining higher spatial resolution. In addition, since the multi-beam carbon nano X-ray source array 222 can perform high-speed pulse emission, the ineffective radiation dose in the CT scanning process is greatly reduced, and the ultra-low radiation effect is further realized.
In addition, because the space resolution of the photoacoustic imaging sub-technology comes from ultrasonic signals, and the ultrasonic scattering of biological tissues is weaker than the light scattering by two orders of magnitude, the photoacoustic imaging method has the advantages of high optical contrast, high resolution imaging capability of ultrasound on deep tissues, high sensitivity, no radioactivity and high specificity by the aid of the molecular probe.
Because the imaging time of the photoacoustic imaging subsystem and the imaging time of the static CT imaging subsystem are different, when the system works, the trigger signal of the photoacoustic imaging subsystem can be precisely controlled through the clock of the static CT imaging subsystem 220, so that the trigger signal can be synchronously acquired according to the acquisition time sequence of the static CT imaging subsystem 220, and synchronous imaging of the photoacoustic imaging subsystem and the static CT imaging subsystem can be realized.
The multimode imaging system provided by the embodiment of the invention adopts a scheme of combining a static CT imaging technology and a photoacoustic imaging technology, has the characteristics of complementary advantages, mutual coordination and mutual contrast, wherein on one hand, by means of the advantages of high static CT imaging resolution and ultralow radiation, three-dimensional visualization is easy to position tumor tissues, and on the other hand, early and accurate diagnosis of tumor metastasis and accurate description of drug metabolism can be realized by utilizing the advantages of excellent soft tissue contrast and high sensitivity of photoacoustic imaging. Therefore, the multimode imaging system provided by the embodiment of the invention adopts the multimode imaging technology formed by combining the static computed tomography imaging subsystem 220 and the photoacoustic imaging subsystem 230, so that the synchronous acquisition of the structural and functional information of the animal 400 is realized, and the multimode imaging system has the advantages of high image resolution, high imaging speed, large imaging depth, low radiation dose and long-term monitoring.
Preferably, the multi-beam carbon nano X-ray source array 222 includes a plurality of carbon nano X-ray sources 2220 distributed in an array, the carbon nano X-ray sources 2220 include a vacuum cavity 2221, a carbon nano field emission cathode 2222, a grid 2223, a focusing electrode 2224 and an anode 2225, the carbon nano field emission cathode 2222, the grid 2223, the focusing electrode 2224 and the anode 2225 are all disposed in the vacuum cavity 2221, the anode 2225 is obliquely disposed above the carbon nano field emission cathode 2222 at intervals, the grid 2223 and the focusing electrode 2224 are both disposed between the carbon nano field emission cathode 2222 and the anode 2225, the grid 2223 is disposed between the focusing electrode 2224 and the carbon nano field emission cathode 2222, and the vacuum cavity 2221 is provided with an X-ray exit window 2226 located beside the anode 2225. The multi-beam carbon nano X-ray source array 222 is used for generating X-rays 500 with different projection angles required by static CT scanning, the photon counting detector 223 is used for collecting and processing CT projection data at a high speed, and the power supply 224 is used for supplying power to the multi-beam carbon nano X-ray source array 222. The carbon nano X-ray source 2220 has the characteristics of stable current, good high voltage resistance and small focal spot, specifically, the tube current of the carbon nano X-ray source 2220 is greater than 0.1 milliamp, the tube voltage is greater than 50 kv, and the focal point is less than 0.1 mm.
Preferably, each carbon nano X-ray source 2220 is distributed in a circular ring array or a polygonal array, and the number of the carbon nano X-ray sources 2220 is 90-180, so that 360-degree full coverage of the scanning angle is facilitated.
Preferably, the X-ray exit window 2226 is an aluminum window or a beryllium window.
Preferably, the vacuum chamber 2221 has a vacuum level of 10-6 mm Hg to 10-11 mm Hg.
Preferably, the carbon nano-field emission cathode 2222 includes a substrate and a cold cathode material layer provided on the surface of the substrate. The cold cathode material layer may be prepared by electrophoretic deposition or chemical vapor deposition, and its shape and size may be precisely controlled by photolithography, and in addition, the shape of the cold cathode material layer is preferably elliptical or rectangular to obtain a focus having uniform sizes in all directions.
The substrate is preferably a metal base plate or a silicon chip coated with a metal coating, the metal base plate can be a stainless steel sheet or a copper sheet or a titanium sheet or a molybdenum sheet, and the metal coating can be a copper coating or a titanium coating or a molybdenum coating or iron, and the like.
Preferably, the material of the cold cathode material layer is carbon nanotubes or graphene and a mixture of carbon nanotubes and graphene.
Preferably, the carbon nano-field emission cathode 2222 is disposed on the base of the vacuum chamber 2221.
Preferably, the grid 2223 includes a support and a grid provided on the support, the grid having openings for passing electrons therethrough. The gate electrode 2223 is mainly used to provide an electric field required for the cold cathode material layer to emit electrons. The openings in the grid are primarily used to ensure that electrons can pass through the grid 2223 to the anode 2225. The mesh includes, but is not limited to, a tungsten mesh or a molybdenum mesh.
Preferably, anode 2225 is inclined at an angle a of 5 ° to 15 ° relative to the horizontal. The anode 2225 is mainly used for acceleration of the electron beam to obtain high-energy electrons. Anode 2225 has a reflective target that is primarily used to reflect X-rays 500 produced by electron bombardment. The reflective target may be a tungsten target, a molybdenum target, or the like.
Specifically, the focusing electrode 2224 is mainly used to focus the electron beam to obtain a focus of a desired size. The focusing electrode 2224 is provided with a focusing hole, which may be a rotationally symmetrical circular hole, or a non-rotationally symmetrical elliptical hole or a rectangular hole.
Preferably, the relative distances between the carbon nano-field emission cathode 2222, the gate electrode 2223, the focusing electrode 2224 and the anode 2225 are adjusted by an insulating spacer (not shown), so that the best focusing effect is advantageously achieved.
Preferably, the power supply 224 includes two medium and low voltage power supplies and one high voltage power supply. The medium-low voltage power supply is respectively connected with the grid electrode 2223 and the focusing electrode 2224, the voltage range is 2kV-5kV, the high-voltage power supply is connected with the anode 2225, and the power supply range is 50kV-140kV.
Specifically, the photon counting detector 223 has the characteristics of high-speed data acquisition, high spatial resolution and high resolution capability, and can fully play the advantages of high-speed pulse exposure of the carbon nano X-ray source array 222. The photon counting detector 223 is ring-shaped or polygonal in shape, and the X-photon conversion material thereof may be cadmium telluride or cadmium zinc telluride. The photon counting detector 223 preferably has a dimension in the vertical direction of greater than 0.5cm and a pixel of less than 100 microns.
Preferably, the electronic control circuit 221 includes a pulse drive and timing control circuit, a current consistency control circuit, and a parallel exposure and data acquisition control circuit. The pulse driving and timing control circuit is used for realizing the switching and the exposure time adjustment of the carbon nano X-ray source 2220 and realizing the rapid switching among different carbon nano X-ray sources 2220. Due to the limitation of the preparation process, the field emission performance of the cathode is inevitably different, and the current consistency control system can modulate the emission current of the cathode by precisely adjusting the voltage of the grid electrode 2223 of each carbon nano X-ray source 2220, so that the consistency of the currents of different carbon nano X-ray sources 2220 in the working process can be maintained, and the same exposure dose of different angles can be ensured. The parallel exposure and data acquisition circuit mainly triggers the carbon nano X-ray source 2220 to be started through a trigger signal when the detector is started, so that the synchronous performance of the exposure of the carbon nano X-ray source 2220 and the data acquisition of the detector is realized.
Preferably, the pulse driving and timing control circuit includes a driving circuit, a control circuit, and an isolation protection circuit. The driving circuit is preferably an IGBT (Insulated Gate Bipolar Transistor, i.e., insulated gate bipolar transistor) based driving circuit, and is mainly used for controlling a strong electric signal (kilovolt high voltage) by a weak electric signal, the control circuit is preferably an FPGA (Field-Programmable GATE ARRAY, i.e., field Programmable gate array) based control circuit, and is mainly used for outputting a Programmable signal with high time precision, and the isolation circuit is mainly used for ensuring effective protection of a control system.
Preferably, the current uniformity control circuit comprises a gate current adjustment unit, a gate current measurement unit and a control element.
Specifically, the multimode imaging device 200 further includes a housing 240, and the animal scanning control subsystem 210, the stationary computed tomography subsystem 220, and the photoacoustic imaging subsystem 230 are all disposed within the housing 240.
Preferably, the photoacoustic imaging subsystem 230 includes an optical subsystem 231 for providing excitation light required for photoacoustic imaging, an acoustic subsystem 232 for collecting multiple photoacoustic signals, and a photoacoustic coplanarity adjustment subsystem (not shown) for adjusting the incidence angle of the excitation light to ensure that the optical signals remain coplanar with the acoustic signals. The optical subsystem 231 is mainly used for providing excitation light required for photoacoustic imaging, and comprises an excitation light source and a multi-wavelength optical focusing component. The acoustic subsystem 232 is mainly used for collecting multiple photoacoustic signals, and mainly comprises a high-frequency ultrasonic transducer array 2321 and a multi-channel data collection platform 2322. The optoacoustic coplane adjusting subsystem is mainly used for automatically adjusting the incidence angle of the exciting light so as to ensure that light/sound always keeps coplane.
In a specific application, due to the non-uniformity of the periphery of the animal 400 body, the coincidence of the photoacoustic excitation (beam section) and the photoacoustic detection (beam section) cannot be always maintained in the whole scanning process of the animal 400, so that the signal-to-noise ratio is reduced, and the reconstruction quality of the image is greatly affected. In this embodiment, the photoacoustic coplanar adjustment subsystem monitors the exact size of the periphery of the animal 400 in real time through CT, calculates the exact position of the light incident surface, and further controls the light incident angle so that the light incident angle is always coplanar with the ultrasound detection position, thereby ensuring high excitation-detection efficiency of photoacoustic.
Preferably, the optical subsystem 231 comprises an excitation light source, a lens group, an optical fiber bundle and an annular light bowl, wherein the lens group is arranged between the excitation light source and the optical fiber bundle, and the optical fiber bundle is fixed on the annular light bowl and is positioned between the lens group and the annular light bowl. The lens group, the optical fiber bundle and the annular optical bowl together form a multi-wavelength optical focusing component. The optical fiber bundle is mainly used for coupling and transmitting the excitation light, and the annular optical bowl is mainly used for fixing the optical fiber bundle.
Preferably, the excitation light source is a high-energy rapid nanosecond pulse optical parametric oscillator, and the lens group comprises a spectroscope, a plano-convex lens, a collimating lens and a focusing lens.
Preferably, the acoustic subsystem 232 includes a high frequency ultrasound transducer array 2321 for detecting acoustic signals and a multi-channel data acquisition platform 2322 for processing detected signals of the high frequency ultrasound transducer array 2321. The high frequency ultrasonic transducer array 2321 is mainly used to detect an excited acoustic signal, and may specifically be a ring structure. The multi-channel data acquisition platform 2322 is mainly used for processing the detection signals. The multi-channel data acquisition platform 2322 may correspond to each array element of the high-frequency ultrasonic transducer array 2321 to an independent data acquisition, amplification, filtering and other preprocessing channel, so as to realize real-time high-speed acquisition and preprocessing of data.
Preferably, the high frequency ultrasonic transducer array 2321 includes a plurality of high frequency ultrasonic transducers distributed in an array, each high frequency ultrasonic transducer corresponding to one array element of the high frequency ultrasonic transducer array 2321. The high-frequency ultrasonic transducer is of a multi-layer laminated structure and comprises an acoustic lens, a matching layer, a piezoelectric composite material layer and an insulating backing layer which are sequentially laminated from front to back.
Preferably, the animal scanning control subsystem 210 includes a positioning structure 211 for positioning the animal 400 and an electromechanical control platform 212 for driving the positioning structure 211 and the animal 400 on the positioning structure 211 to move in a vertical direction. The positioning structure 211 is mainly used for precisely fixing the animal 400, and the electromechanical control platform 212 is mainly used for controlling and realizing the effect that the animal 400 moves along the vertical direction.
Preferably, the image reconstruction and processing subsystem comprises an image reconstruction module carrying an image reconstruction algorithm, an image calibration module carrying image correction and registration software, an image fusion module carrying multi-mode image fusion software, and an information output module carrying information extraction and display software. The image reconstruction module specifically carries a reconstruction algorithm of the CT image and the photoacoustic image.
The embodiment of the invention provides a living body multimode imaging technology and a living body multimode imaging system of an animal 400, which have high spatial resolution, large imaging depth, extremely low side effect and long-term monitoring. Experiments prove that the static computed tomography imaging subsystem 220 has the advantages of high imaging speed, high spatial resolution and ultra-low radiation dose, the photoacoustic imaging subsystem 230 has the characteristics of large imaging depth, high sensitivity and specificity, and the fusion of the static computed tomography imaging subsystem 220 and the photoacoustic imaging subsystem 230 is proved to have feasibility.
The foregoing description is only of the preferred embodiments of the present invention and is not intended to limit the scope of the invention, and all equivalent structural changes made by the description of the present invention and the accompanying drawings or direct/indirect application in other related technical fields are included in the scope of the invention.