CN114027802A - Diffusion optical tomography system - Google Patents
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Abstract
The invention discloses a diffuse optical tomography system, which is characterized by comprising a continuous light acquisition module, a time-resolved optical measurement module and a computer system, wherein the continuous light acquisition module adopts near infrared light to scan an object to be measured and records scanned image data; the time-resolved optical measurement module irradiates an object to be measured by adopting near infrared light and acquires a time-resolved signal; the computer system comprises a reconstruction algorithm; and the reconstruction algorithm carries out reconstruction processing on the image data and the time resolution signals. The diffuse optical tomography system disclosed by the invention can quickly provide pathological information directly related to vascular proliferation of cancerous tissues, tissue blood oxygen level and the like, so that the time is saved and the pain of a patient is reduced.
Description
Technical Field
The invention relates to the technical field of medical equipment, in particular to a diffusion optical tomography system.
Background
The detection of optical parameters of biological tissue by using light radiation in the near infrared band is one of the current popular research fields. Compared with the traditional medical diagnosis and imaging technology, the near infrared imaging not only can directly acquire the functional information of the tissue body, but also can realize nondestructive detection and imaging of the living tissue, and can be used for microstructure analysis and characteristic parameter measurement of the living biological tissue and diagnosis and treatment of diseases.
The Diffuse Optical Tomography (DOT) technique irradiates a tissue with near-infrared light, detects diffused light emitted from the tissue, obtains an Optical parameter distribution image of the tissue, and infers physiological conditions and lesion information of the tissue from the Optical parameters, thereby realizing diagnosis of diseases. Among them, breast tumor detection and brain imaging are the most important fields of DOT research application. Depending on the type of laser source used (continuous wave, sine wave or pulse amplitude modulation) and the associated data acquisition system, DOT is divided into three different measurement systems: time Domain (TD), Frequency Domain (FD), and Continuous Wave (CW).
In DOT, tissue absorption is minimized by using light in the Near Infrared (NIR) region (about 650 to 950 nm), resulting in a relatively large tissue penetration depth. After near-infrared light with different wavelengths is incident on human tissues, blood, fat and the like can generate different absorption and scattering effects on the human tissues. The existing DOT system can only collect optical information reflecting tissue absorption effect or scattering effect, the collected optical information is incomplete, which can cause incomplete information for constructing optical parameter distribution images, and the diagnosis accuracy and precision are low; or, although the existing DOT system can simultaneously acquire optical information reflecting tissue absorption effect and scattering effect, it needs to consume a certain time, and brings great discomfort to the patient, for example, when breast tumor detection is performed, breast tissue needs to be extruded, and the pain of the patient can be increased by long-time extrusion.
Disclosure of Invention
In view of the above problems with the prior art, the present invention provides a diffuse optical tomography system and a method of using the same.
The invention aims to solve the problems by the following technical scheme:
a diffuse optical tomography system comprising a continuous light acquisition module, a time-resolved optical measurement module, and a computer system. The continuous light acquisition module scans an object to be detected by adopting near infrared light a and records image data of the object to be detected scanned by the near infrared light, for example, an optical camera is used for carrying out spatial resolution light detection to obtain image data in a projection direction; the time-resolved optical measurement module uses near-infrared light b to irradiate an object to be measured and collects a time-resolved signal, for example, a modulation signal is used to modulate the near-infrared light to obtain high-frequency near-infrared light, and then the object to be measured is irradiated, and simultaneously the collected optical signal is demodulated through a demodulation signal to obtain a time-resolved (TPSF) signal. The computer system comprises a reconstruction algorithm; and the reconstruction algorithm carries out reconstruction processing on the image data and the time resolution signals.
The continuous light acquisition module comprises a transmission type measurement mode and a reflection type measurement mode; the transmission type refers to that a light source (including near infrared light) and a detector (including an optical camera and a probe) are arranged on two sides of an object to be detected, and the reflection type refers to that the light source a and the detector are arranged on the same side of the object to be detected. Similarly, the time-resolved optical measurement module also includes a projection type and a reflection type. The reflective optical imaging depth is low, and the reflective optical imaging depth is generally suitable for superficial imaging such as brain function imaging; the imaging depth of the transmission type is improved compared with the imaging depth of the reflection type, the use is wider, and the research value is higher. Preferably, the continuous light collection module and the time-resolved optical measurement module adopt different measurement modes, so that more comprehensive optical imaging data can be acquired.
In some embodiments, a transmission-type near-infrared optical tomography module is shown in fig. 4, and the module includes a light source a, a two-dimensional scanning platform, an optical camera and an industrial personal computer, two transparent parallel plates, and two high-reflectivity plane coated mirrors;
the imaging process of the module comprises:
(1) placing the object to be measured between the two transparent parallel plates, slightly extruding the object to be measured by the parallel plates to ensure that the surface of the object to be measured is attached to the surfaces of the parallel plates, and respectively placing the two reflectors at two sides of the two parallel plates in 45 degrees;
(2) the two-dimensional scanning platform controls the near infrared light a to irradiate one reflector, be reflected to the object to be measured by the reflector, be scattered or absorbed by the object to be measured, be reflected by the other reflector and be projected to the optical camera. The field of view of the optical camera covers the whole scanning range, and can detect the spatial resolution light and obtain the image data in the projection direction. Preferably, the two-dimensional scanning platform is a high-speed scanning galvanometer; the parallel plates are acrylic plates; the reflector can change the light path, so that the transmission type near-infrared optical tomography module has a more compact structure and is beneficial to the miniaturization of the device. The mirrors may be high reflectivity planar coated mirrors such as aluminum coated mirrors and silver coated mirrors. Furthermore, the two-dimensional scanning platform or the high-speed scanning galvanometer can control the near infrared light generated by the light source a to carry out X, Y two-dimensional scanning in a plane, so that 1-1000 scanning positions are realized.
In some embodiments, the transmissive continuous light collection module is the same as that of patent 201210051377.0 (issued publication No. 102579011B).
The time-resolved optical measurement module comprises a light source b, a modulation circuit, a photoelectric detection unit and a signal processing unit; the light source b is used for generating near infrared light 2; the modulation circuit outputs a modulation signal to modulate the near infrared light b, and simultaneously inputs a demodulation signal to the signal processing unit; the photoelectric detection unit is used for collecting near infrared light signals passing through an object to be detected, converting the light signals into electric signals and transmitting the electric signals to the signal processing unit; the signal processing unit demodulates the received electric signal by using the demodulation signal to obtain a time-resolved signal, and transmits the signal to the computer system.
In some forms, the modulation circuit is shown in fig. 2 and includes a pseudorandom sequence emitter, a radio frequency power splitter, a programmable digital delay line, and an external intensity modulator; the pseudo-random sequence transmitter is used for continuously generating a high-bit-rate pseudo-random sequence signal; the radio frequency power distributor is used for uniformly distributing the pseudo random sequence signals into a branch A and a branch B, and the branch A is input into the signal processing unit to form a demodulation signal; the branch B is step delayed by the programmable digital delay line and further forms the modulated signal through the external intensity modulator.
Preferably, the frequency of the pseudo-random sequence signal is 2.5 Gbps; the step delay time is 40 ps.
Preferably, the photoelectric detection unit comprises a probe, an incident optical fiber, an emergent optical fiber and a photoelectric detector; one end of the probe is connected with the incident optical fiber, and the other end of the probe is connected with the emergent optical fiber; the emergent optical fiber is connected with the photoelectric detector.
Preferably, the photodetector is one or more of an avalanche photodiode, a photomultiplier tube, and a photoresistor.
Preferably, a square wave of a certain frequency is superimposed on the branches a and B, preferably, the frequency is 2.5 kHz.
In some aspects, the generation and superposition of square waves is as described in patent 202001071553.9 (granted publication No. CN 111466874B).
Preferably, the signal processing unit comprises a radio frequency amplifier, a mixer, an operational amplifier and a data acquisition card.
Furthermore, the number of the photoelectric detection units is 1-100; the number of the signal processing units is equal to the number of the photoelectric detection units.
In some embodiments, the time-resolved optical measurement module is the same as that of US8649010B 2.
Further, the wavelength range of the near-infrared light a and the near-infrared light b is 650nm to 950nm, preferably one or a combination of more of 780nm, 785nm, 808nm, 830nm and 850 nm.
Preferably, the near-infrared light a is constant-power continuous near-infrared light; the near infrared light b is near infrared laser modulated at high frequency.
Preferably, the optical camera comprises a CCD camera and a CMOS camera, and the field of view of the optical camera covers the entire scanning range.
Further, the analyte is animal tissue with low density, such as breast tissue and brain tissue.
The invention has the advantages that:
the maximum value and the average value of the optical characteristics of the relevant tissue part, such as the peak value of the hemoglobin concentration, the average value of the hemoglobin concentration and the like, can be obtained through the optical image. Can provide physiological information directly related to the blood vessel hyperplasia of the cancerated tissues and the blood oxygen level of the tissues, directly distinguish the benign and malignant of the parenchymal tumor through the data range of physiological parameters, and has intuitive and readable images and short examination process without depending on the level and experience of an operating physician. The diffusion optical tomography system is noninvasive, painless and radiationless, does not need a contrast medium, has low system cost, can be repeatedly used in a short time, and has wide application range. Compared with the existing diffusion optical tomography system, the system can accurately obtain the diffusion coefficient and scattering coefficient information of the object to be detected to the near infrared light in a short time, thereby saving time and reducing the pain of patients.
Drawings
FIG. 1 is a system block diagram of a diffuse optical tomography system of the present invention;
FIG. 2 is a schematic diagram of a reflective time-resolved optical measurement module;
FIG. 3 is a time-resolved optical measurement apparatus of the present invention;
FIG. 4 is a schematic diagram of a transmissive continuous light collection module;
FIG. 5 is a schematic view of a two-dimensional scan of the continuous light collection module light source shown in FIG. 4;
FIG. 6 is a schematic view of a single row point-by-point scan of the continuous light collection module light source shown in FIG. 4;
FIG. 7 is a continuous optical collection device of the present invention;
FIG. 8 is a graph showing the results of detection of breast cancer patients, (a) molybdenum target images, (b) optically reconstructed images;
in the figure: 1-continuous light collection module, 2-time resolved optical measurement module, 3-computer system (PC), 4-tissue under test, 11-light source a, 12-two-dimensional scanning platform, 13-optical camera, 14-Industrial Personal Computer (IPC), 21-light source b, 22-modulation circuit, 23-photoelectric detection unit, 24-signal processing unit, 221-pseudo random sequence emitter (PRBS transsetter), 222-radio frequency power distributor (Splitter), 223-Programmable Digital Delay Line (PDDLS), 224-external intensity Modulator (Modulator), 231-Probe (Probe), 232-Avalanche Photodiode (APD), 241-radio frequency amplifier (RF Amp), 242-Mixer (Mixer), 243-operational amplifier (Op-Amp), 244-data acquisition card (DAQ), 2311-hand-held probe, 41-phantom, 2211-FPGA development board (Xilinx Spartan-6 SP 605), 2311-hand-held probe, 121-two-dimensional high-speed scanning galvanometer (Galvo Scanner), 131-CMOS, 5-parallel plate, 6-Reflector (Reflector), 141-upper computer program.
Detailed Description
The invention is further described with reference to the following figures and examples.
As shown in FIG. 1, the present invention provides a diffuse optical tomography system comprising a continuous light acquisition module 1, a time-resolved optical measurement module 2, and a computer system 3.
The continuous light collection module 1 comprises a light source a11, a two-dimensional scanning platform 12, an industrial personal computer 14 and an optical camera 13; the light source a11 generates near infrared light and provides continuous near infrared light with constant power. Light source a11 is coupled to two-dimensional scanning platform 12 by an optical fiber. The two-dimensional scanning platform 12 controls the near-infrared laser generated by the light source a11 to perform two-dimensional point-by-point scanning on the surface of the measured tissue 4 (i.e. the object to be measured). The two-dimensional scanning platform 12 is used for achieving X, Y two-dimensional scanning of the light source in a plane, can reach 1-1000 scanning positions, and the two-dimensional scanning platform 12 is connected with the industrial personal computer 14. The industrial personal computer 14 includes an upper computer program 141 that controls the movement of the two-dimensional scanning platform 12 and the image acquisition by the optical camera 13, and can transmit the acquired image or image set to the computer system 3. The optical camera 13 is positioned at the exit surface of the measured tissue 4 and is capable of recording the intensity of the diffused light. Under the control of the industrial personal computer 14, the optical camera 13 records the near infrared light emitted from each position to obtain a picture; after the complete scanning of the tissue 4 under test is achieved under the action of the two-dimensional scanning platform 12, a complete image set of all positions can be obtained.
The time-resolved optical measurement module 2 includes a light source b21, a modulation circuit 22, a photodetection unit 23, and a signal processing unit 24. The light source b21 is a high-frequency modulated near-infrared laser and is connected to the modulation circuit 22. The modulation circuit 22 contains a high frequency signal and a low frequency signal for modulation and demodulation of the amplitude/phase of the near infrared light signal. The light source b21 is amplitude or phase modulated by the modulation signal generated by the modulation circuit 22, and the modulated light source is coupled to the surface of the object to be measured through the optical fiber. The photo-detection unit 23 may be one or more of avalanche photo-diodes (APDs), photomultiplier tubes, and photo-resistors, and the number thereof is one to one hundred. The photo detection unit 23 is connected to a signal processing unit 24. The signal processing unit 24 includes a signal demodulation circuit, a signal amplification circuit, data acquisition, and the like. The number of signal processing units 24 is the same as the number of photodetecting units 23. The photoelectric detection unit 23 collects near-infrared light passing through the tissue 4 to be detected, converts the light signal into an electrical signal, and transmits the electrical signal to the signal processing unit 24. The signal processing unit 24 demodulates the collected photoelectric signal by using the reference signal of the modulation circuit to obtain a TPSF signal, and transmits the TPSF signal to the computer system 3 for image reconstruction processing.
The computer system 3 comprises a reconstruction algorithm. The reconstruction algorithm comprises a forward model and a backward model, wherein the forward model starts from a light diffusion principle, calculates a Jacobian matrix according to detection conditions (such as mold size, substrate parameters, boundary conditions and the like) and is used for reconstructing an image by the backward model; the backward model links the original data with the three-dimensional structure of the biological tissue through the Jacobian matrix according to the perturbation theory, and reconstructs a three-dimensional image by adopting a proper algorithm. The whole process comprises data preprocessing, data sampling and algorithm reconstruction of a three-dimensional image. Compared with the traditional method, the reconstruction algorithm has higher operation speed and higher reconstruction accuracy for the calculation of the same mass under the same operation environment. The three-dimensional optical image of the detected tissue 4 obtained by the reconstruction algorithm is not less than 5 layers. The maximum value and the average value of the optical characteristics of the relevant tissue part, such as the peak value of the hemoglobin concentration, the average value of the hemoglobin concentration and the like, can be obtained through the optical image. After the signals collected by the continuous light collection module 1 and the time-resolved optical measurement module 2 are transmitted to the computer system 3, the reconstruction algorithm performs reconstruction processing by using the data provided by the two modules to obtain an optical image of the measured tissue 4 and the optical characteristics of the tissue. The tissue 4 to be measured includes a breast tissue and a brain tissue, and the optical characteristics thereof include a hemoglobin concentration and an oxygen saturation level.
Fig. 2 is a schematic diagram of a theoretical structure of a reflective time-resolved optical measurement module according to the present invention. The reflection type time-resolved optical measurement module utilizes a high-frequency signal to modulate a near-infrared light source for irradiating an object to be measured, and can recover TPSF signals very quickly by demodulating through a reference signal.
In fig. 2, a pseudo-random sequence (PRBS) transmitter 221 may continuously generate a high bit rate PRBS signal with a signal frequency of 2.5 Gbps. A Radio Frequency (RF) power Splitter (Splitter) 222 evenly distributes the PRBS signal to branch a and branch B. Branch a remains as the reference signal for demodulation (demodulated signal). Branch B is step delayed by a programmable digital delay line (PDDL 5) 223 with a step delay time of 40 ps. An external intensity Modulator (Modulator) 224 intensity modulates light source B21 with the PRBS signal carried by branch B, light source 21 being NIR light at 780nm wavelength with a power of 1 mW. The modulated NIR light is multiplexed into an Optical fiber (Optical fiber) and is incident into b the tissue under test 4 (Target) through the Probe (Probe) 231. The probe 231 is used for fixing the optical fiber (incident optical fiber) and the optical fiber bundle (emergent optical fiber), and one end of the probe is the incident optical fiber and is connected with the NIR light source; the other end is a fiber bundle connected to a photodetector, which is an Avalanche Photodiode (APD) 232. The fiber bundle on probe 231 collects the NIR light that passes through the test object and couples to APD 232. The APD232 converts the collected optical signal into an electrical signal, and feeds the electrical signal back to the Mixer (Mixer) 242 after being amplified by the radio frequency amplifier (RF Amp) 241. The mixer 242 demodulates the electrical signal from the reference signal (branch a). Since mixer 242 is not an ideal multiplier in practice, the Intermediate Frequency (IF) signal contains not only the desired demodulated signal but also unwanted dc offset and system noise. In order to eliminate the dc offset and reduce the system noise level, a square wave of a certain frequency is superimposed on the PRBS modulation signal and input to the intensity modulator, the square wave frequency being 2.5 kHz. The demodulation result thus produces an IF signal corresponding to the square wave frequency, which is further amplified by 60dB by a series of operational amplifiers (Op-Amp) 243. The amplitude of the IF signal is indicative of the intensity of light detected at a particular time delay in response to the pulsed illumination. The computer system 3 collects this signal via a data acquisition card (DAQ) 244, and by correlating this signal with another square wave of the same frequency, the dc offset can be completely eliminated and the system noise level significantly reduced.
The PRBS signal and the detected photo-electric signal are cross-correlated to produce a time spectrum of the time resolved signal (TPSF). Therefore, TPSF can be obtained directly through a hardware circuit, and is obtained without recording a large amount of time spectrum data and carrying out numerical operation, so that the data acquisition time is greatly shortened.
It should be noted that the wavelength of NIR is not limited to 780nm, but may be 785nm, 808nm, 830nm and 850nm or a combination of two or more wavelengths, and NIR of different wavelengths may be time-division multiplexed into an optical fiber by an optical switch. The power of the NIR light source is not limited to 1mW and can be 0.5-2 mW. The number of the probes of the time-resolved optical measurement module is one to more. The probe can be a fiber or a fiber bundle consisting of a plurality of fibers. The NIR is coupled to the one or more probes through one or more fiber couplers, respectively. The fiber optic bundle on each probe collects NIR that passes through the test object and couples into a corresponding photodetector. The number of photodetectors is the same as the number of probes. The high frequency modulation signal may be a high bit rate signal greater than 1 Gb/s; the low frequency modulation signal may be a square wave signal greater than 1 KHz. The photodetector may be any one of an avalanche photodiode, a photomultiplier tube, and a photo resistor.
Fig. 3 shows a reflective time-resolved optical measurement device (including the reflective time-resolved optical measurement module shown in fig. 2) whose pseudo-random sequence is generated by an FPGA development board (Xilinx Spartan-6 SP 605) 2211, and the probe is a handheld probe 2311. The FPGA development board 2311 can generate two paths of 2.5GHz high-frequency signals. The light source 21 adopts a near infrared light source with the wavelength of 850nm and the power is 1.5 mW. The handheld probe 2311 includes a multimode optical fiber and a fiber bundle. The multimode fiber is connected to a light source 21 and the fiber bundle is connected to an APD 232. The signal collected by the APD232 is collected by the DAQ (NI 6251) 244 after passing through the signal processing unit 24, and the DAQ (NI 6251) 244 provides a 10kHz square wave and transmits the collected TPSF signal to the computer system 3. In the figure, the dummy 41 is used for replacing an object to be measured, and the tissue to be measured and the like are placed at the position of the dummy 41, so that the optical information can be acquired through the device.
Fig. 4 is a schematic diagram of a transmissive continuous light collection module according to the present invention. The module can obtain a large amount of transmission data of projection directions passing through the object to be measured by combining the scanning of the continuous point light source with the optical camera to detect the transmission intensity of each scanning position.
In FIG. 4, the tissue 4 is placed between two transparent parallel plates 5, and the parallel plates 5 lightly press the tissue 4 to make the tissue surface adhere to the surfaces of the parallel plates. Two high-reflectivity plane coated mirrors (reflectors) 6 are respectively arranged at two sides of the two parallel plates 5 at an angle of 45 degrees. The parallel plate 5 here may be a acrylic Plate (PMMA) and the mirror 6 may be an aluminized or silvered mirror. The light source a is a high-power NIR laser light source, can continuously emit NIR light, and has the wavelength of 808nm and the optical power of 100 mW. The NIR continuous light is coupled through an optical fiber into a two-dimensional scanning platform, which is a two-dimensional high-speed scanning galvanometer (Galvo Scanner) 121. Galvo Scanner121 is connected to an industrial control computer (IPC) 14, and IPC14 comprises an upper computer program which can control Galvo Scanner121 to move at a high speed, so that NIR light can scan line by line on the surface of the parallel plate point by point, after one line of scanning is finished, line feed is performed in Y direction, and point by point scanning of a new line is started, and the operations are repeated in sequence (as shown in FIG. 5).
As shown in fig. 6, during the point-by-point scanning, due to scattering and absorption of the object to be measured, the NIR light enters the object to be measured, diverges and propagates in various directions, like a cone beam emitted from each scanning point (incidence point). A CMOS (an optical camera) is located on the other side of the object to be measured, and can perform data acquisition once for each incidence point of NIR light. The CMOS has infrared response capability, the effective pixel is no less than 200 ten thousand, and is connected with IPC 14.
Referring back to fig. 4, NIR light is irradiated to the tissue 4 to be measured via the Galvo Scanner121, and after the light is scattered and absorbed by the tissue 4 to be measured, the light is reflected by the reflecting mirror 6 and recorded by the CMOS 131. For each scan site of NIR light, CMOS131 records to produce an image, and CMOS131 transmits the acquired image data to IPC14 in real time. The IPC14 is connected to the computer system (PC) 3 via a network cable. After the scan is completed, IPC14 sends the obtained image set, which includes hundreds of original two-dimensional images, containing multi-position, multi-angle optical projection measurement data, to PC 3. The PC3 performs reconstruction processing on these images, and finally obtains a three-dimensional image of the tissue 4 to be measured.
It should be noted that the detection depth of the continuous light collection module shown in fig. 4 is greater than 5cm, the maximum optical collection time is less than 120s, and the data collection time can be further reduced by reducing the scanning range and reducing the exposure time of the optical camera during collection. The two-dimensional scanning platform can be an optical fiber array which is uniformly distributed and arranged in a two-dimensional mode, and NIR light is sequentially time-division multiplexed into optical fibers which are arranged in the two-dimensional mode, so that the two-dimensional scanning function is achieved. The optical camera may also be a CCD camera, in addition to a CMOS camera.
FIG. 7 shows a transmission-type continuous light collection device (including the transmission-type continuous light collection module shown in FIG. 4), the light source 11 is a near infrared light source with MLDP-808-MM, the center wavelength is 808 + -5 nm, the spectral width (FWHM) is 2nm, and the maximum output light power is 150 mW. The Galvo Scanner121 is SG7110 in model number, the linearity reaches 99.9%, the small step response time is less than or equal to 0.5ms, the maximum scanning angle is +/-15 degrees, the resolution is 12 mu Rad, and the input aperture is 10 mm. The Galvo Scanner121 is connected with an industrial personal computer through a self-contained servo driving board, and an upper computer program 141 of the industrial personal computer controls the two lenses in the Galvo Scanner121 to move, so that the NIR light moves point by point on the lower surface of the parallel plate 5 (the parallel plate is an acrylic plate here). The light source 11 position point is set to 5mm at each movement interval. The reflector 6 has high reflectivity of two aluminized films with oxidation-resistant protective films, and has a size of 260mm × 185mm, and the average reflectivity of near-infrared band is greater than 90%. The optical camera 13 adopts a 200-ten-thousand low-light-level high-sensitivity sCMOS camera with the model number of Dhyana 201DS, the size of the camera is 1', the resolution is 2048 multiplied by 1152, the effective pixels are 200 thousand, the pixel size is 6.5 mu m multiplied by 6.5 mu m, the data bit depth is 16bit, and the exposure time is 0.013 ms-10 s. The industrial computer (IPC) has model number of GK3000, memory capacity of 8GB, hard disk capacity of 240GB, and CPU of Intel core I5-7200U. In the figure, the dummy 41 is used for replacing an object to be measured, and the tissue to be measured and the like are placed at the position of the dummy 41, so that the optical information can be acquired through the device. As shown in figure 8, the device is used for carrying out data acquisition and image reconstruction on the left mammary gland of a breast cancer patient, and comparing the image reconstruction result with the molybdenum target image result. The results show that: the characteristics of the pathological change area in the visible optical reconstruction image are consistent with those of the molybdenum target image through comparison.
After the near infrared light is incident on the tissue to be detected, absorption and scattering effects can be generated. Although a single continuous light acquisition system can complete information acquisition in a short time, the scattering coefficient of the tissue to be detected cannot be quantified generally, and certain deviation is caused on the reconstruction of the absorption coefficient, so that the detection accuracy is not high. For example: when mammary tissue measurement is carried out, dense mammary tissue often has higher scattering and absorption effects than non-sensitized mammary tissue, and the adoption of a continuous light acquisition system can only use the roughly estimated integral scattering coefficient to carry out three-dimensional reconstruction of an absorption coefficient, so that an image reconstruction result is inaccurate.
Although the time-resolved optical measurement system can accurately obtain the scattering coefficient and the absorption coefficient at the same time, the information acquisition time is long, and the clinical application is not facilitated. In order to obtain the absolute value of the optical related physiological parameters of the tested tissue and the three-dimensional distribution of the space, taking the collection of the breast tissue of a B cup as an example, the collection range is 140 multiplied by 65mm, the collection step length is 5mm, and 406 position points are required to be scanned in one collection. A single acquisition of TPSF signal using the time resolved optical measurement device shown in fig. 3 measured about 3.1s for a single acquisition and a total time to acquire 406 position points of about 20.97min (1258.6 s). The B-cup breast tissue examination was performed using the continuous light collection device described in fig. 7, collecting 406 location points for a total of 32 seconds of required use. If the devices shown in fig. 3 and fig. 7 are combined, the diffuse optical tomography of the breast tissue of the B-cup is performed according to the diffuse optical tomography system shown in fig. 1, the time-resolved optical measurement module only needs to acquire TPSF signals of 1-5 position points, and the required maximum time is 3.1s 5; the time required by the continuous light acquisition module is 32s, and the maximum total time for the system to acquire data is as follows: 32s +3.1s 5=47.5 s. In clinical application, medical care operating personnel carry out 1~5 position time resolution optical measurement to the tissue of being surveyed through handheld probe in order to obtain the distribution of tissue absorption coefficient and scattering coefficient, and reuse continuous light collection device to gather optical data fast to improve the spatial resolution who reconstructs the image, make the result more accurate.
In conclusion, the diffuse optical tomography system can complete the data acquisition work of the optical measurement system needing to be completed within 20.97min, which is time-resolved within 47.5s, so that a large amount of time is saved, and particularly for breast cancer patients, the system greatly relieves the pain of the patients during detection.
The above embodiments are only used for illustrating the technical ideas and features of the present invention, and the scope of the present invention should not be limited thereby, and any modifications made based on the technical ideas and features of the present invention are within the scope of the present invention. The technology not related to the invention can be realized by the prior art.
Claims (23)
1. A diffuse optical tomography system, the system comprising a continuous light acquisition module, a time-resolved optical measurement module, and a computer system;
the continuous light acquisition module scans the object to be detected point by adopting near infrared light a and records image data of the object to be detected scanned by the near infrared light a;
the time-resolved optical measurement module adopts near-infrared light b to irradiate the object to be measured and acquires a time-resolved signal;
the computer system comprises a reconstruction algorithm; and the reconstruction algorithm carries out reconstruction processing on the image data and the time resolution signals.
2. The system of claim 1, wherein the continuous light acquisition module comprises a light source a, a two-dimensional scanning platform, an optical camera, and an industrial personal computer;
the light source a is used for generating near infrared light a and is coupled to the two-dimensional scanning platform through an optical fiber; the two-dimensional scanning platform controls the near infrared light a to scan point by point on the surface of the object to be detected; the industrial personal computer comprises an upper computer program which controls the two-dimensional scanning platform to move, controls the optical camera to collect images and transmits collected image data to the computer system.
3. The system of claim 1, wherein the time-resolved optical measurement module comprises a light source b, a modulation circuit, a photodetection unit and a signal processing unit;
the light source b is used for generating near infrared light b; the modulation circuit outputs a modulation signal to modulate the near infrared light b, and simultaneously inputs a demodulation signal to the signal processing unit; the photoelectric detection unit is used for collecting near infrared light signals after irradiating the object to be detected, converting the light signals into electric signals and transmitting the electric signals to the signal processing unit; the signal processing unit demodulates the received electric signal by using the demodulation signal to obtain a time-resolved signal, and transmits the signal to the computer system.
4. The system of claim 1 or 2, wherein the continuous light collection module and the time-resolved optical measurement module are transmissive or reflective; preferably, when the continuous light scanning module is a transmissive type, the time-resolved optical measurement module is a reflective type; when the continuous light scanning module is of a reflective type, the time-resolved optical measurement module is of a transmissive type.
5. The system of claim 2, wherein the continuous light acquisition module further comprises two transparent parallel plates and two mirrors; placing the object to be detected between two transparent parallel plates, and slightly extruding the object to be detected by the parallel plates to ensure that the surface of the object to be detected is attached to the surfaces of the parallel plates; preferably, the two mirrors are placed at 45 ° on both sides of the two parallel plates, respectively.
6. The system of claim 5, wherein the process of controlling the near-infrared light a generated by the light source a to scan the surface of the object point by the two-dimensional scanning platform comprises: the two-dimensional scanning platform controls the near infrared light a to irradiate one reflector, the near infrared light a is reflected to the object to be measured by the reflector, and then the near infrared light a is reflected to the optical camera by the other reflector after being scattered or absorbed by the object to be measured.
7. The system of claim 5, wherein the parallel plates are acrylic plates.
8. The system of claim 5, wherein the mirror is a high reflectivity planar coated mirror, including an aluminum coated mirror and a silver coated mirror.
9. The system of claim 2, wherein the two-dimensional scanning platform is a high-speed scanning galvanometer.
10. The system of claim 2, wherein the two-dimensional scanning platform controls the near infrared light generated by the light source a to perform X, Y two-dimensional scanning in a plane, and 1-1000 scanning positions can be realized.
11. The system of claim 3, wherein the modulation circuit comprises a pseudorandom sequence emitter, a radio frequency power divider, a programmable digital delay line, and an external intensity modulator;
the pseudo-random sequence transmitter is used for continuously generating a high-bit-rate pseudo-random sequence signal;
the radio frequency power distributor is used for uniformly distributing the pseudo random sequence signals into a branch A and a branch B, and the branch A is input into the signal processing unit to form a demodulation signal; the branch B is step delayed by the programmable digital delay line and further forms the modulated signal through the external intensity modulator.
12. The system of claim 11, wherein the frequency of the pseudo-random sequence signal is 2.5 Gbps; the step delay time is 40 ps.
13. The system of claim 3, wherein the photodetection unit comprises a probe, an incident optical fiber, an exit optical fiber, and a photodetector;
one end of the probe is connected with the incident optical fiber, and the other end of the probe is connected with the emergent optical fiber;
the emergent optical fiber is connected with the photoelectric detector.
14. The system of claim 13, wherein the photodetector is one or more of an avalanche photodiode, a photomultiplier tube, and a photo resistor.
15. System according to claim 11, characterized in that a square wave of a certain frequency is superimposed to the branches a and B, preferably the frequency is 2.5 kHz.
16. The system of claim 3, wherein the signal processing unit comprises a radio frequency amplifier, a mixer, an operational amplifier, and a data acquisition card.
17. The system of claim 3, wherein the number of the photodetecting units is 1-100.
18. The system of claim 3, wherein the number of signal processing units is equal to the number of photo detection units.
19. The system of claim 1, wherein the near-infrared light a is constant power continuous near-infrared light, and the near-infrared light b is high frequency modulated near-infrared laser light.
20. The system of claim 1, wherein the wavelengths of the near-infrared light a and the near-infrared light b are one or more of 780nm, 785nm, 808nm, 830nm and 850 nm.
21. The system of claim 1, wherein the optical camera comprises a CCD camera and a CMOS camera, and wherein the field of view of the optical camera covers the entire scan range.
22. The system of claim 1, wherein the test objects include breast tissue and brain tissue.
23. A method of imaging using a diffuse optical tomography system, the diffuse optical tomography system comprising a continuous light acquisition module, a time resolved optical measurement module, and a computer system;
the continuous light acquisition module comprises a light source a, a two-dimensional scanning platform, an optical camera and an industrial personal computer;
the time-resolved optical measurement module comprises a light source b, a modulation circuit, a photoelectric detection unit and a signal processing unit;
the computer system comprises a reconstruction algorithm;
the method comprises the following specific steps:
(1) the light source a generates near infrared light a and is coupled to the two-dimensional scanning platform through an optical fiber; the industrial personal computer controls the two-dimensional scanning platform to move, so that the near infrared light a scans the surface of the object to be detected point by point; the industrial personal computer controls the optical camera to acquire images and transmits acquired image data to the computer system;
(2) the light source b generates near infrared light b; the modulation circuit modulates the near infrared light b and simultaneously inputs a demodulation signal to the signal processing unit; irradiating the modulated near-infrared light b to an object to be detected; the photoelectric detection unit collects near infrared light signals passing through an object to be detected, converts the light signals into electric signals and transmits the electric signals to the signal processing unit; the signal processing unit demodulates the received electric signal by using the demodulation signal to obtain a time resolution signal and transmits the signal to a computer system;
(3) the reconstruction algorithm performs reconstruction processing on the image data and the time-resolved signal.
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