CN116942103B - Dark-field photoacoustic tomography system and method - Google Patents
Dark-field photoacoustic tomography system and method Download PDFInfo
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Abstract
The invention provides a dark field photoacoustic tomography system and a method, wherein a body to be measured absorbs energy of beam expansion pulse light to generate local pressure change, and ultrasonic signals are transmitted to a plurality of directions outside the body to be measured in an ultrasonic mode; the ultrasonic detection module in the system comprises a plurality of ultrasonic transducer units to form one or a plurality of ultrasonic transducer arrays, wherein the ultrasonic transducer arrays detect ultrasonic signals along a plurality of propagation directions in an effective ultrasonic detection range and convert the ultrasonic signals into voltage signals to be output; and the irradiation range of the beam expansion pulse light on the surface of the to-be-detected body and the effective ultrasonic detection range of the ultrasonic detection module do not have an overlapping area on the surface of the to-be-detected body, or the area of the overlapping area of the irradiation range of the surface of the to-be-detected body and the effective ultrasonic detection range of the ultrasonic detection module on the surface of the to-be-detected body is not more than 50 percent of the irradiation range on the surface of the to-be-detected body, and the system is used for restraining the shape and the azimuth of the surface of the to-be-detected body, so that photoacoustic tomography dark field illumination is realized in the surface area of the effective imaging area of the to-be-detected body.
Description
Technical Field
The invention relates to biomedical imaging technology, in particular to a dark-field photoacoustic tomography system and a dark-field photoacoustic tomography method.
Background
As an emerging biomedical imaging technology, photoacoustic tomography has the characteristics of high speed, high resolution, rich imaging information, safety and no radiation, and is complementary with the traditional biomedical imaging technology, and in recent years, the photoacoustic tomography starts to be clinically converted. The photoacoustic tomography technology irradiates biological tissue with pulsed light, and biological tissue components absorbing the light generate ultrasonic signals under the photoacoustic effect, and an image of the light absorbing components in the biological tissue is reconstructed by detecting the ultrasonic signals.
The mechanism of the photoacoustic effect is that when pulsed light irradiates an organism, the tissue constituents that absorb this wavelength of light will have a short temperature rise, causing rapid changes in local pressure. The pressure change propagates outside the living body in the form of ultrasonic waves (also called photoacoustic signals) and is detected by peripheral ultrasonic transducers. Based on photoacoustic signals with different intensities detected by the ultrasonic transducer at different positions and times, an image reconstruction algorithm calculates and calculates components (such as hemoglobin), concentration and positions of light absorbing color clusters in an organism and provides a light absorbing color cluster distribution image. Therefore, in the photoacoustic tomography system, the cooperation of the pulsed light irradiation and the ultrasonic detection fundamentally determines the imaging performance of the photoacoustic tomography system.
Through development for more than twenty years, the photoacoustic imaging technology has been a long-standing advance. However, in the design of the existing photoacoustic tomography system, especially in the cooperative combination of pulse illumination and ultrasonic detection, optimization and standardization have not been performed, and a common problem is that in the existing photoacoustic tomography system, the illumination distribution of pulse illumination on the surface of biological tissue and the ultrasonic detection range have large overlapping, so that the distribution difference of luminous flux (light energy per unit area) in the ultrasonic detection area is large. Since light decays exponentially with depth after entering biological tissue, photoacoustic signals from the tissue surface are typically received by photoacoustic imaging systems much stronger than photoacoustic signals from deep tissues. However, large differences in photoacoustic signal amplitude within the effective imaging region can result in the presence of non-negligible shallow signal artifacts in deep tissue images when using image reconstruction algorithms such as back projection or delay-and-sum. In addition, the propagation of strong acoustic signals generated by strong luminous fluxes at the tissue surface in biological tissues with inhomogeneous acoustic properties may experience irregular scattering, which invalid scattering signals will also generate artifacts in the reconstructed image after being received by the ultrasound transducer.
Disclosure of Invention
Aiming at the defects of the existing photoacoustic tomography technology, the invention provides a dark-field photoacoustic tomography system and a dark-field photoacoustic tomography method.
A dark field photoacoustic tomography system comprises a light guide module, an ultrasonic detection module and a bearing shaping module;
the light guide module expands and/or shapes the pulse light beam to form expanded pulse light to irradiate a to-be-measured body, wherein components which absorb the expanded pulse light in the to-be-measured body absorb the energy of the expanded pulse light to generate local pressure change, and the local pressure change propagates ultrasonic signals in a plurality of directions outside the to-be-measured body in an ultrasonic mode; the ultrasonic detection module detects ultrasonic signals propagating along a plurality of directions and converts the ultrasonic signals into voltage signals; the bearing molding module bears the body to be measured and constrains the surface form and the direction of the body to be measured through installing the molding groove, so that the irradiation range and the incidence angle of the beam expansion pulse light on the surface of the body to be measured are stable and controllable;
the light guide module adjusts the irradiation range of the beam expansion pulse light on the surface of the to-be-detected body, so that the relative position and the angle between the irradiation range of the beam expansion pulse light on the surface of the to-be-detected body and the effective ultrasonic detection range of the ultrasonic detection module are adjusted, and no overlapping area exists on the surface of the to-be-detected body, or the area of the overlapping area is not more than 50% of the irradiation range of the beam expansion pulse light on the surface of the to-be-detected body, so that dark field illumination is formed;
the body to be detected is one or a combination of a plurality of organisms, biological tissues or non-organisms;
the ultrasonic detection module comprises a plurality of ultrasonic transducer units which are distributed around a body to be detected, wherein the ultrasonic transducer units form one or more ultrasonic transducer arrays, and the ultrasonic transducer arrays detect ultrasonic signals which are generated by beam expansion pulse light in the body to be detected and propagate along a plurality of directions in an effective ultrasonic detection range and convert the ultrasonic signals into voltage signals to be output; each transducer unit can select a self-focusing or non-self-focusing shape, and the effective detection range of each transducer unit is subject to an ultrasonic diffraction formula; the effective ultrasound detection range of each ultrasound transducer array or detection matrix also obeys the spatial sampling theorem;
the ultrasonic detection module can be designed into different forms according to different requirements, and specifically comprises the following components:
(1) The ultrasonic detection module comprises one or more arc-shaped ultrasonic transducer arrays, the radian range of the ultrasonic transducer arrays is 10-359 degrees, and the arc-shaped ultrasonic transducer arrays form an arc-shaped ultrasonic transducer module;
(2) The ultrasonic detection module comprises two or more linear ultrasonic transducer arrays which are arranged to form a polygon or a part of a polygon;
(3) The ultrasonic detection module comprises a plurality of ultrasonic transducer units which are spatially distributed to form a part of a sphere to form a spherical ultrasonic transducer array;
(4) The ultrasonic detection module comprises a plurality of ultrasonic transducer units which are spatially distributed into a part of a polyhedron to form a polyhedral ultrasonic transducer array;
light guide modules are arranged at two sides of the arc ultrasonic transducer array to form bilateral dark field illumination; a light guide module is arranged on one side of the linear ultrasonic transducer array to form single-side dark field illumination; a light guide module is arranged at the edge of the spherical ultrasonic transducer array to form annular dark field illumination; the light guide module is placed in the ultrasonic transducer unit gap of the polyhedral ultrasonic transducer array to form polygonal dark field illumination;
the bearing molding module bears and molds the body to be measured by installing a molding groove near the imaging window, and the molding groove is made of a firm or difficultly deformed material; the bearing shaping module reserves an imaging window for the beam expanding pulse light and the ultrasonic signal to pass through near the effective imaging area, the window is covered by a material which is easy to pass through by light and ultrasonic, the irradiation of the beam expanding pulse light to the to-be-detected body is not blocked, and the detection of the ultrasonic signal by the ultrasonic detection module is not blocked while the surface shape of the to-be-detected body is restrained;
the effective imaging area is an area where the effective ultrasonic detection range of the ultrasonic detection module is covered in the body to be detected, and is a section with a certain thickness of the body to be detected or a three-dimensional space of the body to be detected; the effective imaging area comprises a surface area and a deep layer area, the surface area is close to the carrying shaping module, and the deep layer area is far away from the carrying shaping module; the surface area distance of the effective imaging area is close to the surface vertical distance 0 to 1mm of the body to be measured of the carrying shaping module, and the deep area distance of the effective imaging area is close to the surface vertical distance of the body to be measured of the carrying shaping module, is more than 1mm and less than 100mm;
the irradiation direction of the beam expansion pulse light points to or approximately points to the central position of the effective imaging area, the straight line distance from the irradiation area on the surface of the object to be detected to the central position of the effective imaging area is not more than 5cm, and after the beam expansion pulse light propagates and attenuates in the object to be detected, the luminous flux distribution intensity of the deep layer area of the imaging area is at least 1/1000 higher than the maximum luminous flux on the surface of the object to be detected;
the irradiation range and angle of the beam expansion pulse light on the surface of the object to be detected are matched with the size and shape of the effective imaging area, so that the luminous flux distribution in the object to be detected after the beam expansion pulse light propagates and scatters in the object to be detected covers the deep layer area and the surface area of the effective imaging area, and the relationship between the strongest luminous flux in the effective imaging area and the weakest luminous flux in the effective imaging area is as follows: the ratio of the strongest light flux to the weakest light flux is less than or equal to 200;
the dark-field photoacoustic tomography system further includes: pulse generation module, space scanning module, data acquisition module and image reconstruction module:
the pulse light generating module comprises one or more light sources for generating single-wavelength or multi-wavelength pulse light beams; the space scanning module adjusts the relative position of the to-be-detected body and the photoacoustic imaging system main body; the data acquisition module processes the voltage signal output by the ultrasonic detection module to output signal data; the image reconstruction module calculates the distribution of the concentration of each light absorbing color group in the to-be-detected body according to the signal data, and generates an image of the to-be-detected body;
the space scanning module adjusts the effective imaging area of the to-be-detected body to be overlapped with the area expected to be observed by an operator, and increases the imaging range of the photoacoustic tomography system; the relative position or angle of the body to be detected and the main body of the photoacoustic tomography system is fed back through a positioning lens or a marked positioning point; according to the placement position of the to-be-measured body, moving or rotating the relative position of the photoacoustic imaging system main body and the to-be-measured body in any one or more modes of manual, automatic and self-adaptive modes; the photoacoustic imaging system body includes: the device comprises a pulse generation module, a light guide module, an ultrasonic detection module and a data acquisition module;
the data acquisition module is used for carrying out acquisition, processing, transmission and storage on the voltage signals output by the ultrasonic detection module and outputting signal data, wherein the amplitude of the output signal data is proportional to the amplitude of ultrasonic signals related to the type of the to-be-detected body and also proportional to the local pressure change amplitude in the to-be-detected body;
the image reconstruction module performs image reconstruction of the object to be detected according to time information and amplitude information contained in the signal data of the data acquisition module, and calculates the local pressure variation amplitude in the effective imaging areaFurther calculating the distribution of the concentration of each light absorbing color group in the body to be detected, and generating an image of the body to be detected;
the local pressure change amplitude is proportional to the optical absorption coefficient of the light absorption componentThe product of the local luminous flux F, the optical absorption coefficient of the light-absorbing component +.>Can characterize the concentration of each absorbance group in the test object in order to be based on the local pressure variation amplitude +.>Finally obtaining the optical absorption coefficient of the light absorption component in the object to be measured>It is necessary to provide a relatively uniform or controllable luminous flux F distribution to the effective imaging area according to the pulse light generating module, the light guiding module and the kind of the object to be measured.
A dark-field photoacoustic tomography method is realized based on the dark-field photoacoustic tomography system, and comprises the following steps:
step 1: designing and testing an effective ultrasonic detection range of an ultrasonic detection module;
step 2: installing a carrying shaping module according to the effective ultrasonic detection range of the ultrasonic detection module, and fixing the position of the carrying shaping module, so as to further calibrate the position relation between the pulse illumination area and the carrying shaping module;
step 3: determining the initial installation position and angle of the light guide module, installing the light guide module, and guiding the light beam emitted by the pulse light generating module to irradiate the area to be illuminated after shaping and expanding the light beam; adjusting the illumination range and angle by adjusting the optical device of the light guide module, and overlapping the pulse illumination area calibrated in the step 2 to realize photoacoustic tomography dark field illumination;
step 4: placing a bionic prosthesis with the acoustic characteristics similar to those of a human body in a body bearing molding module to be tested to test the imaging effect, and optimizing the imaging quality by fine-adjusting the illumination range and angle; after the optimization is completed, judging whether the optical energy density and the power density in the to-be-imaged area accord with the national laser safety standard or not; if the three modules are consistent, the relative positions and angles of the pulse beam, the ultrasonic detection module and the bearing molding module are optimized and relatively stable; if not, continuing to adjust;
step 5: according to the placement position of the to-be-measured body fed back by the carrying shaping module, manually, automatically or adaptively adjusting the relative position of the to-be-measured body and the main body of the photoacoustic tomography system by utilizing the space scanning module, so that the target imaging area of the to-be-measured body overlaps with the effective imaging area;
step 6: and placing a sample to be tested after the test is finished, and finishing illumination excitation, ultrasonic detection, space scanning, data acquisition and image reconstruction based on a dark field photoacoustic tomography system to obtain an image of the body to be tested.
The invention has the beneficial technical effects that:
in photoacoustic tomography, since the light flux of pulsed light generally decays exponentially with the increase in penetration depth after entering the body under test, the ultrasonic signals received by conventional photoacoustic tomography systems from the superficial region of the body under test are generally much stronger than those from the deep region. However, if there is a large difference in the amplitude of the ultrasonic signal in the imaging region, an image reconstruction algorithm such as back projection or delay summation will cause an image of the deep region of the body to be measured to show an artifact from the superficial region signal which cannot be ignored. In addition, the transmission of the stronger ultrasonic signal generated by the stronger luminous flux of the tissue surface area in the tissue with nonuniform acoustic characteristics can experience irregular scattering, and the invalid scattering signal can also generate artifacts in the image of the deep layer area of the object to be detected after being received by the ultrasonic transducer. Because the shape and the position of the surface of the to-be-detected body are generally lack of constraint or limitation, the controllability of the illumination distribution area of the surface of the to-be-detected body is generally poor, and the imaging quality stability of the photoacoustic tomography system is reduced. Therefore, the invention provides a dark-field photoacoustic tomography system and a method, which adopt photoacoustic tomography dark-field illumination to solve the defects in the prior art.
In the invention, the body to be measured is born by the bearing shaping module and restrained by the surface morphology; the irradiation range of the beam expanding pulse light on the surface of the to-be-detected body and the effective ultrasonic detection range of the ultrasonic detection module do not have an overlapping area on the surface of the to-be-detected body, or the area of the overlapping area of the irradiation range of the beam expanding pulse light on the surface of the to-be-detected body and the effective ultrasonic detection range of the ultrasonic detection module is not more than 50% of the irradiation range of the beam expanding pulse light on the surface of the to-be-detected body; the effective imaging area of the body to be detected is an effective ultrasonic detection range of the ultrasonic detection module and covers an area in the body to be detected, the effective imaging area comprises a surface area and a deep area, the surface area is close to the carrying shaping module, and the deep area is far away from the carrying shaping module. And adjusting the relative position and angle of the beam expansion pulse light between the irradiation range of the surface of the to-be-measured object and the effective imaging area of the to-be-measured object, wherein the beam expansion pulse light does not directly irradiate the surface area in the effective imaging area, and the photoacoustic tomography dark field illumination is realized in the surface area of the effective imaging area, so that the beam expansion pulse light is transmitted and attenuated in the to-be-measured object, and then more uniform luminous flux distribution is provided in the effective imaging area than that of the traditional photoacoustic tomography system.
The method can reduce the artifacts of the photoacoustic signals with stronger surface areas in the image, and is also beneficial to reducing the requirements of an imaging system on the data sampling depth, namely the digital resolution, in the data acquisition module. By optimizing the illumination area and the ultrasonic detection range, the position and the form of the object to be detected are standardized, the artifact of an ultrasonic signal generated in a shallow area of the object to be detected in a deep area is greatly reduced, and the image definition and the image quality stability of the photoacoustic tomography system are improved.
Drawings
Fig. 1 is a schematic structural diagram of a photoacoustic tomography system of the present invention.
Fig. 2 is a dark field illumination schematic diagram of the photoacoustic tomography system of the present invention.
Fig. 3 is an illustration of an imaged female mammary gland internal vessel according to the present invention.
Fig. 4 is a schematic view of two sides of an arc-shaped ultrasonic transducer array of the present invention with light guide modules disposed thereon to form a double-sided dark field illumination.
Fig. 5 is a schematic view of a single-sided dark field illumination formed by placing a light guide module on one side of the polygonal ultrasonic transducer array of the present invention.
FIG. 6 is a schematic diagram of a load bearing molding module according to the present invention.
Fig. 7 is a schematic diagram of a hemispherical ultrasound transducer array in combination with annular dark field illumination in accordance with the present invention.
Fig. 8 is a schematic diagram of a polyhedral ultrasonic transducer array in combination with polygonal dark field illumination according to the present invention.
Detailed Description
In order to improve the imaging performance and the image quality of the photoacoustic tomography system, the invention provides a dark-field photoacoustic tomography system; the technical scheme of the invention is further described below with reference to the attached drawings and the specific embodiments.
The dark field photoacoustic tomography system provided by the invention is shown in fig. 1, and comprises a pulse light generating module 1, a light guide module 2, an ultrasonic detection module 3, a bearing shaping module 4, a space scanning module 5, a data acquisition module 6 and an image reconstruction module 7.
The pulse light generating module 1 comprises one or more light sources for generating single-wavelength or multi-wavelength pulse light beams; the pulse light is a single wavelength light beam or a multi-wavelength light beam, and the wavelength range is 0.3 mu m-3 mu m. The pulsed light generation module 1 is a prior art, for example an Nd: YAG nanosecond pulsed laser.
The light guide module 2 comprises a reflecting mirror, a prism, a scattering sheet, a lens, an optical fiber and/or a light guide arm, and is used for expanding and/or shaping the pulse light beam emitted by the pulse light generating module 1 to form an expanded pulse light, the expanded pulse light irradiates the body to be detected, the light absorption component in the body to be detected absorbs the energy of the expanded pulse light and then generates local pressure change, and ultrasonic signals are transmitted to a plurality of directions outside the body to be detected in an ultrasonic mode; the body to be detected can be selected from one or a combination of organisms, biological tissues and abiotic bodies.
The beam-expanding pulse light attenuates in the body to be measured, and the attenuation characteristic of the beam-expanding pulse light is compliant with Beer-Lambert's law, i.e. the luminous flux at the distance z from the body surface in the body to be measuredWherein->For the luminous flux of the surface of the object to be measured, the effective attenuation coefficient of the object to be measured under the wavelength of the pulse light +.>Wherein->For the optical absorption coefficient of the object under test at the wavelength of the pulse light, and (2)>The optical reduced scattering coefficient of the object under test under the pulse light wavelength is obtained.
The ultrasonic detection module 3 comprises a plurality of ultrasonic transducer units which are distributed around the body to be detected, wherein the ultrasonic transducer units form one or a plurality of ultrasonic transducer arrays, and the ultrasonic transducer arrays detect ultrasonic signals which are generated by beam expansion pulse light in the body to be detected and propagate along a plurality of directions in an effective ultrasonic detection range and convert the ultrasonic signals into voltage signals to be output; each transducer unit can select a self-focusing or non-self-focusing shape, and the effective detection range of each transducer unit is subject to an ultrasonic diffraction formula; the effective ultrasound detection range of each ultrasound transducer array or detection matrix is also subject to spatial sampling theorem.
The effective ultrasound detection range of the ultrasound detection module 3 is related to the distribution range, adjacent pitch, and detection ultrasound signal wavelength of the ultrasound transducer units of the ultrasound transducer array. The spatial sampling pitch of the ultrasound transducer array of the ultrasound detection module 3 in the effective detection range is shorter than half the wavelength of the ultrasound signal.
As shown in fig. 4, the ultrasonic detection module 3 includes one or more arc-shaped ultrasonic transducer arrays having an arc range of 10 degrees to 359 degrees, and the arc-shaped ultrasonic transducer arrays are combined to form the ultrasonic detection module 3. Light guide modules 2 are placed on two sides of the arc ultrasonic transducer array to form bilateral dark field illumination.
As shown in fig. 5, the ultrasound detection module 3 includes two or more linear ultrasound transducer arrays arranged to form a polygon or a portion of a polygon. A light guide module 2 is placed on one side of the linear ultrasonic transducer array to form single-side dark field illumination.
As shown in fig. 7, the ultrasonic detection module 3 includes a plurality of ultrasonic transducer units spatially arranged as a part of a sphere to form a spherical ultrasonic transducer array. The edge of the spherical ultrasonic transducer array is provided with a light guide module 2 to form annular dark field illumination.
As shown in fig. 8, the ultrasonic detection module 3 includes a plurality of ultrasonic transducer units spatially arranged as a part of a polyhedron to form a polyhedral ultrasonic transducer array. And a light guide module is arranged in an ultrasonic transducer unit gap of the polyhedral ultrasonic transducer array to form polygonal dark field illumination.
The carrying shaping module 4 carries the object to be detected by installing a shaping groove and constrains the shape and the orientation of the surface 10 of the object to be detected to be the same as or similar to those expected, so that the irradiation range and the incidence angle of the beam expanding pulse light on the surface 10 of the object to be detected are stable and controllable, as shown in fig. 6. The carrying shaping module 4 carries and shapes the body to be detected by installing the shaping groove 401 near the imaging window, and the shaping groove 401 adopts firm or uneasy deformation materials including epoxy resin, plastics, silica gel, rubber and the like. The carrying shaping module 4 leaves a window 402 for the beam expanding pulse light and/or ultrasonic signals to pass through near the effective imaging area 9, the window is covered by materials which are easy to pass through by light and/or ultrasonic, and the materials comprise glass, acrylic, transparent resin, transparent plastic and the like, so that the irradiation of the beam expanding pulse light to the to-be-detected body is not blocked while the shape of the surface 10 of the to-be-detected body is ensured to be restrained, and the detection of the ultrasonic signals by the ultrasonic detection module 3 is not blocked.
The effective imaging area 9 of the to-be-detected body is an area covered by the effective ultrasonic detection range of the ultrasonic detection module 3 in the to-be-detected body, and is a section with a certain thickness of the to-be-detected body or a three-dimensional space of the to-be-detected body. The effective imaging area 9 includes a surface area that is close to the carrying molding die 4 and a deep area that is far from the carrying molding die 4. The vertical distance between the surface area of the effective imaging area 9 and the surface 10 of the object to be measured is 0 to 1mm, and the vertical distance between the deep layer area of the effective imaging area 9 and the surface 10 of the object to be measured is more than 1mm and less than 100 mm.
The relative position and angle of the beam expansion pulse light between the irradiation range of the surface 10 of the object to be measured and the effective imaging area 9 of the object to be measured are adjusted through the light guide module 2, so that an overlapping area does not exist on the surface 10 of the object to be measured between the irradiation range of the beam expansion pulse light on the surface 10 of the object to be measured and the effective ultrasonic detection range of the ultrasonic detection module 3, or the area of the overlapping area is not more than 50% of the irradiation range of the beam expansion pulse light on the surface 10 of the object to be measured, and therefore photoacoustic tomography dark field illumination is realized in the surface area of the effective imaging area 9. As shown in fig. 2;
the irradiation direction of the beam expansion pulse light is directed or approximately directed to the central position of the effective imaging area 9, the straight line distance from the irradiation area of the surface 10 of the object to be measured to the central position of the effective imaging area 9 is not more than 5cm, and after the beam expansion pulse light propagates and attenuates in the object to be measured, the luminous flux distribution intensity of the effective imaging area is at least 1/1000 higher than the highest luminous flux on the surface 10 of the object to be measured.
The irradiation range of the beam expansion pulse light on the surface 10 of the object to be measured is matched with the size and shape of the effective imaging area 9, so that the light flux distribution in the object to be measured after the beam expansion pulse light propagates in the object to be measured and is scattered by the object to be measured covers the deep layer area and the surface area of the effective imaging area 9, and the relationship between the strongest light flux in the effective imaging area 9 and the weakest light flux in the effective imaging area 9 is as follows: the ratio of the strongest light flux to the weakest light flux is 200 or less.
The space scanning module 5 comprises a motion module and a guide rail, and is used for adjusting the relative positions of the to-be-detected body and the ultrasonic detection module 3, so that an effective imaging area 9 in the to-be-detected body is overlapped with an area which an operator hopes to observe, and the imaging range of the photoacoustic tomography system is enlarged. The relative position or angle of the body to be detected and the photoacoustic tomography system is fed back through a positioning lens or a marked positioning point.
The data acquisition module 6 amplifies, acquires, processes, transmits and stores the voltage signal output by the ultrasonic detection module 3, and outputs signal data, wherein the amplitude of the signal data is proportional to the amplitude of the ultrasonic signal and also proportional to the amplitude of local pressure change in the body to be detected. The data acquisition module 6 is a prior art, e.g. a LEGION ADC of a PST.
The image reconstruction module 7 performs image reconstruction of the object to be detected according to the time information and the amplitude information contained in the signal data of the data acquisition module 6, and calculates the local pressure variation amplitude in the effective imaging area 9Further calculating the distribution of the concentration of each light absorbing color group in the object to be detected, and generating an image of the object to be detected.
As shown in fig. 3, which is an illustration of female mammary gland internal blood vessel imaging, the image reflects that a certain blood vessel signal is still not interfered by a body surface signal at a depth of approximately 4cm, so that a clearer blood vessel image is formed; however, the conventional photoacoustic tomography device can be seriously interfered by a strong signal of the body surface at the depth of 4cm, so that the exact source of the ultrasonic signal at the position cannot be confirmed.
The local pressure change amplitude is proportional to the optical absorption coefficient of the light-absorbing componentThe product of the local luminous flux F, the optical absorption coefficient of the light-absorbing component +.>Can characterize the concentration of each light-absorbing color group in the object to be measured in order to be based on the local pressure variation amplitudeFinally obtaining the optical absorption coefficient of the light absorption component in the object to be measured>It is desirable to provide a relatively uniform or controllable light flux F distribution to the effective imaging area 9.
In this embodiment, each data acquisition channel of the data acquisition module 6 corresponds to each ultrasound transducer unit of the ultrasound transducer array 8 one by one, so that imaging of a two-dimensional cross section in the body to be tested can be completed after each illumination pulse. The space scanning module 5 can manually, automatically or adaptively move or rotate the object to be detected or the photoacoustic tomography device according to the placement position of the object to be detected fed back by the positioning lens or the marked positioning point, so that a larger imaging range is provided in the three-dimensional space.
Specifically, under the action of the space scanning module 5, the hemispherical ultrasonic transducer array 8 can provide dense space sampling for a to-be-detected body in a three-dimensional space, realizes uniform spatial resolution in all directions in the three-dimensional effective imaging area 9, and can also receive ultrasonic signals which propagate along multiple directions in the three-dimensional space.
The dark-field photoacoustic tomography method of the embodiment is realized based on the dark-field photoacoustic tomography system, and comprises the following steps:
step 1: the effective ultrasonic detection range of the ultrasonic detection module 3 is designed and tested. In the design process, if the acoustic characteristics of the ultrasonic transducer array 8 are calculated and simulated by means of theoretical calculation, sound field simulation software or finite element analysis under the simulation condition, parameters such as sound field distribution and the like of the ultrasonic transducer array are analyzed, so that an effective ultrasonic detection range of the ultrasonic transducer array is determined; if under the experimental condition, the sound field characteristics of the ultrasonic transducer array 8 can be measured by using testing tools such as a single-channel ultrasonic transducer, an ultrasonic microphone and the like, and the effective ultrasonic detection range is determined;
step 2: installing a carrying shaping module 4 according to the effective ultrasonic detection range of the ultrasonic detection module 3, and further calibrating the position relation between the pulse illumination area to be implemented and the carrying shaping module 4 of the body to be detected;
step 3: determining the position and the size of a light spot of a pulse illumination area to be implemented according to the type of the object to be detected and the size of an effective imaging area 9;
the diffusion sheets with different characteristics are selected according to requirements, and specifically: selecting the size of a diffusion sheet according to the light spot size of a pulse light beam emitted by the pulse light generating module 1, selecting the shape of the diffusion sheet according to the installation mode of the light guide module 2, selecting the size of a diffusion angle of the diffusion sheet according to the amplitude of a reconstructed image, and primarily calculating the approximate space distance from the diffusion sheet to an imaging window 402 on the carrying shaping module 4;
by applying law of refractionCalculating an incident angle when the beam expansion pulse light enters the imaging window 402, so that an illumination area of the beam expansion pulse light is positioned in an effective imaging area 9 of the ultrasonic detection module 3, and the illumination direction is directed or approximately directed at the central position of the effective imaging area 9;
according to the spatial distance and the incidence angle calculated by the theory, the light guide module 2 is installed, and the light beam emitted by the pulse light generating module 1 irradiates the area to be illuminated after shaping and beam expansion. Further, by adjusting the optical device of the light guide module 2, the illumination range and angle are adjusted to overlap with the pulse illumination area calibrated in the theoretical calculation, so as to realize the photoacoustic tomography dark field illumination. In the step, optical measuring devices such as laser developing paper, an energy/power meter or a light spot measuring instrument can be placed at the area to be illuminated, and parameters such as the actual illumination range, angle, energy uniformity and the like are determined;
step 4: a bionic prosthesis (such as agar) similar to the acoustic characteristics of a human body is placed in the body to be measured carrying molding module 4, the imaging effect is tested, and the imaging quality is optimized by fine adjustment of the illumination range and angle. After optimization is complete, the optical energy density and power density within the region to be imaged are confirmed to comply with the American national laser safety standards (ANSI, z 136.131-2014). From this, the relative positions and angles of the pulse beam, the ultrasonic detection module 3 and the carrying shaping module 4 are optimized and relatively stable;
step 5: the space scanning module 5 is installed and adjusted, and the relative position of the body to be measured and the photoacoustic tomography system can be manually, automatically or adaptively adjusted according to the placement position of the body to be measured fed back by the bearing molding module 4, so that a target imaging area in the body to be measured overlaps with an ultrasonic imaging detection area;
step 6: placing a sample to be measured, and completing illumination excitation, ultrasonic detection, space scanning, data acquisition and image reconstruction.
Claims (1)
1. The dark-field photoacoustic tomography system is characterized by comprising a light guide module, an ultrasonic detection module and a bearing shaping module;
the light guide module expands and/or shapes the pulse light beam to form expanded pulse light to irradiate a to-be-measured body, wherein components which absorb the expanded pulse light in the to-be-measured body absorb the energy of the expanded pulse light to generate local pressure change, and the local pressure change propagates ultrasonic signals in a plurality of directions outside the to-be-measured body in an ultrasonic mode; the ultrasonic detection module detects ultrasonic signals propagating along a plurality of directions and converts the ultrasonic signals into voltage signals; the bearing molding module bears the body to be measured and constrains the surface form and the direction of the body to be measured through installing the molding groove, so that the irradiation range and the incidence angle of the beam expansion pulse light on the surface of the body to be measured are stable and controllable;
the light guide module adjusts the irradiation range of the beam expansion pulse light on the surface of the to-be-detected body, so that the relative position and the angle between the irradiation range of the beam expansion pulse light on the surface of the to-be-detected body and the effective ultrasonic detection range of the ultrasonic detection module are adjusted, and no overlapping area exists on the surface of the to-be-detected body, or the area of the overlapping area is not more than 50% of the irradiation range of the beam expansion pulse light on the surface of the to-be-detected body, so that dark field illumination is formed;
the body to be detected is one or a combination of a plurality of organisms, biological tissues or non-organisms;
the ultrasonic detection module comprises a plurality of ultrasonic transducer units which are distributed around a body to be detected, wherein the ultrasonic transducer units form one or more ultrasonic transducer arrays, and the ultrasonic transducer arrays detect ultrasonic signals which are generated by beam expansion pulse light in the body to be detected and propagate along a plurality of directions in an effective ultrasonic detection range and convert the ultrasonic signals into voltage signals to be output; each transducer unit can select a self-focusing or non-self-focusing shape, and the effective detection range of each transducer unit is subject to an ultrasonic diffraction formula; the effective ultrasound detection range of each ultrasound transducer array or detection matrix also obeys the spatial sampling theorem;
the ultrasonic detection module can be designed into different forms according to different requirements, and specifically comprises the following components:
(1) The ultrasonic detection module comprises one or more arc-shaped ultrasonic transducer arrays, the radian range of the ultrasonic transducer arrays is 10-359 degrees, and the arc-shaped ultrasonic transducer arrays form an arc-shaped ultrasonic transducer module;
(2) The ultrasonic detection module comprises two or more linear ultrasonic transducer arrays which are arranged to form a polygon or a part of a polygon;
(3) The ultrasonic detection module comprises a plurality of ultrasonic transducer units which are spatially distributed to form a part of a sphere to form a spherical ultrasonic transducer array;
(4) The ultrasonic detection module comprises a plurality of ultrasonic transducer units which are spatially distributed into a part of a polyhedron to form a polyhedral ultrasonic transducer array;
light guide modules are arranged at two sides of the arc ultrasonic transducer array to form bilateral dark field illumination; a light guide module is arranged on one side of the linear ultrasonic transducer array to form single-side dark field illumination; a light guide module is arranged at the edge of the spherical ultrasonic transducer array to form annular dark field illumination; the light guide module is placed in the ultrasonic transducer unit gap of the polyhedral ultrasonic transducer array to form polygonal dark field illumination;
the bearing molding module bears and molds the body to be measured by installing a molding groove near the imaging window, and the molding groove is made of a firm or difficultly deformed material; the bearing shaping module reserves an imaging window for the beam expanding pulse light and the ultrasonic signal to pass through near the effective imaging area, the window is covered by a material which is easy to pass through by light and ultrasonic, the irradiation of the beam expanding pulse light to the to-be-detected body is not blocked, and the detection of the ultrasonic signal by the ultrasonic detection module is not blocked while the surface shape of the to-be-detected body is restrained;
the effective imaging area is an area where the effective ultrasonic detection range of the ultrasonic detection module is covered in the body to be detected, and is a section with a certain thickness of the body to be detected or a three-dimensional space of the body to be detected; the effective imaging area comprises a surface area and a deep layer area, the surface area is close to the carrying shaping module, and the deep layer area is far away from the carrying shaping module; the surface area distance of the effective imaging area is 0 to 1mm close to the surface vertical distance of the to-be-measured body of the carrying shaping module, and the deep area distance of the effective imaging area is more than 1mm and less than 100mm close to the surface vertical distance of the to-be-measured body of the carrying shaping module;
the irradiation direction of the beam expansion pulse light points to or approximately points to the central position of the effective imaging area, the straight line distance from the irradiation area on the surface of the object to be detected to the central position of the effective imaging area is not more than 5cm, and after the beam expansion pulse light propagates and attenuates in the object to be detected, the luminous flux distribution intensity of the deep layer area of the imaging area is at least 1/1000 higher than the maximum luminous flux on the surface of the object to be detected;
the irradiation range and angle of the beam expansion pulse light on the surface of the object to be detected are matched with the size and shape of the effective imaging area, so that the luminous flux distribution in the object to be detected after the beam expansion pulse light propagates and scatters in the object to be detected covers the deep layer area and the surface area of the effective imaging area, and the relationship between the strongest luminous flux in the effective imaging area and the weakest luminous flux in the effective imaging area is as follows: the ratio of the strongest light flux to the weakest light flux is less than or equal to 200;
the dark-field photoacoustic tomography system further includes: the device comprises a pulse light generation module, a space scanning module, a data acquisition module and an image reconstruction module:
the pulse light generating module comprises one or more light sources for generating single-wavelength or multi-wavelength pulse light beams; the space scanning module adjusts the relative position of the to-be-detected body and the photoacoustic imaging system main body; the data acquisition module processes the voltage signal output by the ultrasonic detection module to output signal data; the image reconstruction module calculates the distribution of the concentration of each light absorbing color group in the to-be-detected body according to the signal data, and generates an image of the to-be-detected body;
the space scanning module adjusts the effective imaging area of the to-be-detected body to be overlapped with the area expected to be observed by an operator, and increases the imaging range of the photoacoustic tomography system; the relative position or angle of the body to be detected and the main body of the photoacoustic tomography system is fed back through a positioning lens or a marked positioning point; according to the placement position of the to-be-measured body, moving or rotating the relative position of the photoacoustic imaging system main body and the to-be-measured body in any one or more modes of manual, automatic and self-adaptive modes; the photoacoustic imaging system body includes: the device comprises a pulse generation module, a light guide module, an ultrasonic detection module and a data acquisition module;
the data acquisition module is used for carrying out acquisition, processing, transmission and storage on the voltage signals output by the ultrasonic detection module and outputting signal data, wherein the amplitude of the output signal data is proportional to the amplitude of ultrasonic signals related to the type of the to-be-detected body and also proportional to the local pressure change amplitude in the to-be-detected body;
the image reconstruction module performs image reconstruction of the object to be detected according to time information and amplitude information contained in the signal data of the data acquisition module, and calculates the local pressure variation amplitude p in the effective imaging area 0 Further calculating the distribution of the concentration of each light absorbing color group in the body to be detected, and generating an image of the body to be detected;
the local pressure change amplitude is proportional to the optical absorption coefficient mu of the light absorption component α The product of the local luminous flux F and the optical absorption coefficient mu of the light-absorbing component α Can characterize the concentration of each light-absorbing color group in the object to be measured in order to be based on the local pressure variation amplitude p 0 Finally obtaining the optical absorption coefficient mu of the light absorption component in the body to be measured α Providing relatively uniform or controllable luminous flux F distribution for an effective imaging area according to the types of the pulse light generating module, the light guiding module and the to-be-detected body;
the imaging method based on the dark-field photoacoustic tomography system comprises the following steps of:
step 1: designing and testing an effective ultrasonic detection range of an ultrasonic detection module;
step 2: installing a carrying shaping module according to the effective ultrasonic detection range of the ultrasonic detection module, and fixing the position of the carrying shaping module, so as to further calibrate the position relation between the pulse illumination area and the carrying shaping module;
step 3: determining the initial installation position and angle of the light guide module, installing the light guide module, and guiding the light beam emitted by the pulse light generating module to irradiate the area to be illuminated after shaping and expanding the light beam; adjusting the illumination range and angle by adjusting the optical device of the light guide module, and overlapping the pulse illumination area calibrated in the step 2 to realize photoacoustic tomography dark field illumination;
step 4: placing a bionic prosthesis with the acoustic characteristics similar to those of a human body in a body bearing molding module to be tested to test the imaging effect, and optimizing the imaging quality by fine-adjusting the illumination range and angle; after the optimization is completed, judging whether the optical energy density and the power density in the to-be-imaged area accord with the national laser safety standard or not; if the three modules are consistent, the relative positions and angles of the pulse beam, the ultrasonic detection module and the bearing molding module are optimized and relatively stable; if not, continuing to adjust;
step 5: according to the placement position of the to-be-measured body fed back by the carrying shaping module, manually, automatically or adaptively adjusting the relative position of the to-be-measured body and the main body of the photoacoustic tomography system by utilizing the space scanning module, so that the target imaging area of the to-be-measured body overlaps with the effective imaging area;
step 6: and placing a sample to be tested after the test is finished, and finishing illumination excitation, ultrasonic detection, space scanning, data acquisition and image reconstruction based on a dark field photoacoustic tomography system to obtain an image of the body to be tested.
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