CN104665770A - Self-guidance diffused light tomography method for near-infrared brain function research - Google Patents

Self-guidance diffused light tomography method for near-infrared brain function research Download PDF

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CN104665770A
CN104665770A CN201510070110.XA CN201510070110A CN104665770A CN 104665770 A CN104665770 A CN 104665770A CN 201510070110 A CN201510070110 A CN 201510070110A CN 104665770 A CN104665770 A CN 104665770A
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brain function
dot
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predetermined search
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CN104665770B (en
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赵会娟
刘明
高峰
贾梦宇
戚彩霞
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Tianjin University
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    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Measuring for diagnostic purposes; Identification of persons
    • A61B5/0033Features or image-related aspects of imaging apparatus classified in A61B5/00, e.g. for MRI, optical tomography or impedance tomography apparatus; arrangements of imaging apparatus in a room
    • A61B5/004Features or image-related aspects of imaging apparatus classified in A61B5/00, e.g. for MRI, optical tomography or impedance tomography apparatus; arrangements of imaging apparatus in a room adapted for image acquisition of a particular organ or body part
    • A61B5/0042Features or image-related aspects of imaging apparatus classified in A61B5/00, e.g. for MRI, optical tomography or impedance tomography apparatus; arrangements of imaging apparatus in a room adapted for image acquisition of a particular organ or body part for the brain
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
    • A61B5/0082Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes

Abstract

The invention discloses a self-guidance diffused light tomography method for near-infrared brain function research. The self-guidance diffused light tomography method comprises the following steps: firstly, obtaining the light intensity of a detection point position corresponding to each source point; obtaining a two-dimensional topological image of which a detection area absorption coefficient is changed for the light intensity of the detection point position according to MLBL-OT, and performing image segmentation to achieve the effective positioning of an absorption coefficient change area, and generating an area positioning template matrix K; solving according to a DOT reconstruction method by adopting a Newton-Raphson iteration method, calculating a Jacobi matrix J of a node to obtain an OT-DOT reconstruction equation; calculating to obtain absorption coefficient change in predetermined detection, and drawing an OT-DOT reconstruction image. According to a near-infrared brain function self-guidance imaging method, the DOT inverse problem under-determinedness can be improved in a near-infrared optical modal measuring mode according to an MLBL-OT positioning brain function change area, so that the reconstruction speed is increased.

Description

A kind of bootstrap diffused light chromatography imaging method near infrared light brain function research
Technical field
The invention belongs to functional near-infrared imaging method in biomedicine, particularly relate to bootstrap diffused light chromatography imaging method in a kind of near infrared light brain function research.
Background technology
People's cerebration can cause blood flow and blood oxygen metabolism activity change in grey matter, changes the tissue optical parameter of corresponding region in cerebral gray matter.Because biological tissue of human body is less at the absorbing incident light of 650-900nm scope to wavelength, therefore cerebral cortex can be arrived through scalp and skull.Near-infrared Brain functional study utilizes the near infrared light incident illumination of this wave band, carries out reflective measurement to human body quiescent condition and the predetermined search coverage of cerebration state head portion, obtains the optical field distribution at the scalp place under two states.By effectively rebuilding the absorptance change of dominant absorbers in grey matter tissue, obtain tissue oxygen and close the important informations such as hemoglobin, deoxyhemoglobin, blood oxygen saturation, and then research brain function changes blood flow and the blood oxygen metabolism situation of the associative brain regions caused.Near infrared light cerebral function imaging has noinvasive, radiationless, higher temporal resolution, the inexpensive feature such as removable, for neonate and Adult Human Brain thinking or consciousness research provide objective basis.
At present, the main topological formation method (MLBL-OT) adopted based on revising Lambert-Beer in functional near-infrared imaging.MLBL-OT supposes that between source-spy point be the uniform organizer of optical property, and sampled point supposes the central area be positioned between source-spy point, can obtain the two-dimensional topology image of brain blood oxygen change.MLBL-OT has the advantages that calculating is simple, strong robustness, temporal resolution are high, be applicable to realtime imaging.But the spatial resolution of MLBL-OT is limited by source-spy Distance geometry source-spy distribution density, in algorithm there is individual variation and uncertain thus affect quantitative in the head differential path factor (DPF).Although MLBL-OT obtains image spatial resolution and degree of quantization is lower, there is the advantage change of brain blood oxygen region of variation being realized to quick position.
In order to improve spatial resolution and the quantitation capabilities of the imaging of Near-infrared Brain merit, the Near-infrared Brain imaging system theoretical based on diffusion chromatography imaging (DOT) obtains more concerns.DOT mode calculates predetermined search coverage optical field distribution in direct problem based on photon transport theory, adopts successive ignition strategy to rebuild tissue optical parameter in inverse problem.Compared with MLBL-OT mode, DOT mode has mathematical model more accurately, without the need to considering the DPF of individuality or diverse location, and achieves the three-dimensional imaging of reconstruction regions.Although DOT mode improves spatial resolution and the quantitative rate of image, discretization causes measuring number much smaller than reconstruction parameter number, causes the less qualitative speed having a strong impact on reconstruction of inverse problem.
In recent years, along with subject progress multiple in brain research field and development, multi-modal technology is progressively adopted and is achieved certain achievement in brain research.On the one hand, in brain structural research, the segmented extraction of Cranial Computed Tomography/MRI image is quite ripe, the brain construction geometry information that physiological brain can be provided to organize aspect for brain function research.On the other hand, multi-modal the phase mutual designation such as brain function research midbrain electricity, brain magnetic, function nuclear-magnetism, near-infrared functional imaging, evidence and supplement.But also there is the obvious deficiency that many measuring systems adopt brought instrument expense and measuring operation difficulty to increase in the multi-modal technology of brain function simultaneously.Meanwhile, the registration between the multi-modal measurement result of brain function and the suitable difficulty of fusion bring challenges to algorithm aspect.
Summary of the invention
Consider the advantage in prior art in Near-infrared Brain functional study and deficiency, in view of the feature that change is located and DOT degree of quantization is high of MLBL-OT, the present invention adopts the same measurement data research MLBL-OT of Near-infrared Brain function modes to guide DOT, provide a kind of bootstrap diffused light chromatography imaging method near infrared light brain function research, under same light modality, DOT inverse problem can be improved according to MLBL-OT location brain function region of variation less qualitative, thus improve the bootstrap formation method of reconstruction speed.
In order to solve the problems of the technologies described above, a kind of bootstrap diffused light chromatography imaging method near infrared light brain function research that the present invention proposes, comprises the following steps:
Step one, press diffusion chromatography imaging detection mode in the predetermined search coverage of head, with adjacent nearest 2 between distance for 10mm and according to rectangular array arrangement source-spys location point, each position point placement optical fiber; During detection, one of them location point is source point, and all the other each points are for visiting point; First, a wherein location point is specified to be source point, obtain the light intensity of spy point position corresponding to this source point, the rest may be inferred, until using each position point all as till source point, measure the detector intensity measurements vector M a and the human body quiescent condition intensity measurements vector M r that obtain predetermined search coverage cerebration state respectively;
The thickness of step 2, scalp and skull layer is h, selects the spy point position light intensity being more than or equal to 2h with source point distance, obtains head predetermined search coverage absorptance change △ μ according to correction Lambert-Beer topology formation method atwo-dimensional topology image;
Step 3, Iamge Segmentation is carried out to two-dimensional topology image, realizes absorptance region of variation effective location, and generate described predetermined search coverage by the pattern matrix K revising the imaging of Lambert-Beer topology and guide diffusion chromatography imaging, comprise the following steps:
To correction Lambert-Beer topology imaging results with absorptance change △ μ ain minima carry out Region dividing as threshold value, obtain the brain function region of variation ROI under two-dimensional topology image and brain function region of variation n-ROI do not occur;
Three-dimensional nodes coordinate (x, y, z) and quiescent condition simulation light intensity distribution vector Fr in adopting Finite Element Method to calculate to the predetermined search coverage mathematical model of head;
Whether belong to brain function region of variation ROI according to (x, the y) of three-dimensional nodes coordinate (x, y, z) in the predetermined search coverage of head or brain function region of variation n-ROI does not occur, generating a pattern matrix K computing formula is:
In formula (1): k---be the element in pattern matrix K;
Nr aLL---be the line number of pattern matrix K, represent the call number of three-dimensional nodes in predetermined search coverage interior nodes in brain function region of variation ROI;
Nr rOI---be the row number of pattern matrix K, represent the call number of three-dimensional nodes in brain function region of variation ROI in brain function region of variation ROI;
Step 4, adopt Newton-Raphson solution by iterative method according to diffusion chromatography imaging reconstruction mode, calculate the Jacobi matrix J of predetermined search coverage interior nodes, generate according to matrix K and J and guide diffusion chromatography imaging OT-DOT Reconstructed equation by the imaging of correction Lambert-Beer topology;
Represent that OT-DOT mode computing formula is according to dispersive tomography inverse problem math equation when solving three-dimensional optical parameter distribution in organizer:
Ma · Fr Mr - F ( μ a ) = J · KΔ μ a ROI - - - ( 2 )
In formula (2): F (μ a)---be the boundary sensing point light intensity vector solved by direct problem; △ μ a rOI---be absorptance change in ROI region after pattern matrix screening;
Step 5, absorptance change is calculated in predetermined search coverage to OT-DOT Reconstructed equation, and utilize MATLAB Software on Drawing OT-DOT to rebuild image.
Compared with prior art, the invention has the beneficial effects as follows:
Formation method of the present invention adopts same measurement data under near infrared light mode metering system, before DOT rebuilds, adopt MLBL-OT to generate pattern matrix, pattern matrix is applied to the bootstrap that DOT process of reconstruction realizes near-infrared functional imaging, thus reduce the less qualitative of DOT inverse problem, improve reconstruction speed.
Accompanying drawing explanation
Fig. 1 (a) is flat plate model under predetermined search coverage quiescent condition, and wherein, stain is depicted as source-spy point;
Fig. 1 (b) is flat plate model under predetermined search coverage cerebration state, and wherein, cylinder is absorptance region of variation;
Fig. 2 is MLBL-OT mode imaging in the present invention;
Fig. 3 is absorption region network for location after MLBL-OT Iamge Segmentation in the present invention;
Fig. 4 (a) adopts traditional DOT to rebuild image;
Fig. 4 (b) utilizes MLBL-OT of the present invention to guide DOT to rebuild image, and wherein, dotted line is Change of absorption region actual position.
Detailed description of the invention
Be described in further detail technical solution of the present invention below in conjunction with the drawings and specific embodiments, described specific embodiment only explains the present invention, not in order to limit the present invention.
The present invention is used for the bootstrap diffused light chromatography imaging method of near infrared light brain function research, and concrete steps are as follows:
For the predetermined search coverage of functional near-infrared imaging, can Rational Simplification be two layers of flat plate model upper strata be scalp and skull layer 10mm, lower floor is stratum 20mm, as shown in Fig. 1 (a), DOT detection mode is pressed in the predetermined search coverage of head, source-spy distribution adopts DOT highly dense detection mode point-to-point transmission beeline to be 10mm, and according to rectangular array arrangement source-spy location point, the present embodiment is 4 × 4 rectangular arrays, optical fiber is placed at each position point, during detection, when 1 location arrangements light source, detector is all arranged in other 15 positions, obtain the light intensity of spy point position corresponding to this source point, the rest may be inferred, until using each position point all as till source point, then the detector intensity measurements vector M a and the human body quiescent condition intensity measurements vector M r that obtain predetermined search coverage cerebration state is measured respectively, it is the brain function region of variation (ROI) adopting mathematical model simulation cerebration state to cause in the present embodiment, as shown in the cylindrical region in Fig. 1 (b), if cylindrical region radius is 5mm, height is 10mm, and the upper surface center of circle is positioned at dull and stereotyped lower floor's upper surface center.Obtain all participations reconstruction node coordinate by carrying out uniformly subdivision to Fig. 1 (a) and Fig. 1 (b) model, and FEM calculation (FEM) is carried out to DOT direct problem, obtain Mr, Ma.In computational process, the upper strata absorption of quiescent condition drag each subdivision joint and reduced scattering coefficient vector are μ a twith μ ' s t, lower floor absorbs and reduced scattering coefficient vector is μ a bwith μ ' s b.Obtain (see document Yaroslavsky by reference to human brain section's optical measurement in forefathers' document, A.N., Schulze, P.C., Yaroslavsky, I.V., Schober, R., Ulrich, F., and Schwarzmaier, H.J, " Optical properties of selected native and coagulated human brain tissues in vitro in the visible and near infrared spectral range; " Physics in medicine and biology, 47 (12), 2059 (2002) .).
Select the spy point position light intensity being more than or equal to 20mm with source point distance, obtain head predetermined search coverage absorptance change △ μ according to MLBL-OT method atwo-dimensional topology image; Detailed process is as follows:
Organizing the first approximation of internal diffusion based on MLBL-OT as light, be used for describing the attenuation process of luminous energy in high scattering tissue, computing formula is:
ΔOD = - ln Ma Mr = Δ μ a BL
In formula: △ OD---for by quiescent condition to cerebration state detection position light intensity change vector;
△ μ a---be absorptance change vector;
B, L---be respectively the spacing of the differential path factor (DPF) and optical light source and detector;
When adopting MLBL-OT to calculate absorptance change in predetermined search coverage, sampled point thinks the region be in the middle of source point and sensing point, and supposing that the tissue between source-spy is uniform, the two-dimensional topology image of acquisition, shown in Fig. 2 is the average effect that under sampled point, each layer absorptance changes.Therefore the absorptance result of variations obtained can much smaller than actual value;
Iamge Segmentation is carried out to two-dimensional topology image, realizes absorptance region of variation effective location, and generate described predetermined search coverage by the pattern matrix K of OT-DOT, comprise the following steps:
To MLBL-OT result with absorptance change △ μ ain minima carry out Region dividing as threshold value, obtain the ROI under two-dimensional topology image and brain function region of variation (n-ROI) do not occur; All pixel point values ROI region be designated as in " region 1 " region are designated as 1, n-ROI region and are designated as " area 0 " all pixel point values and are designated as 0, the Two Dimensional Thresholding Region dividing result on X-Y plane, as shown in Figure 3.Three-dimensional nodes coordinate (x, y, z) and quiescent condition simulation light intensity distribution vector Fr in adopting Finite Element Method to calculate to the predetermined search coverage mathematical model of head; Whether belong to ROI or n-ROI according to (x, the y) of three-dimensional nodes coordinate (x, y, z) in the predetermined search coverage of head, generating a pattern matrix K computing formula is:
In formula (1): k---be the element in pattern matrix K;
Nr aLL---be the line number of pattern matrix K, represent the call number of three-dimensional nodes in predetermined search coverage interior nodes in ROI;
Nr rOI---be the row number of pattern matrix K, represent three-dimensional nodes call number in the roi in ROI;
Except ranks call number is (nr aLL, nr rOI) outward, other element values in K are all 0.Pattern matrix K achieves the Region dividing to FEM nodes all in the predetermined search coverage of three-dimensional according to two-dimentional ROI and n-ROI region.
Because the resolution of MLBL-OT mode imaging is lower, therefore the ROI scope obtained according to MLBL-OT can slightly larger than true ROI, and pattern matrix K is by the conversion of two dimensional surface region to 3 D stereo region, the node that absorptance change does not occur for some in three-dimensional ROI region, must be comprised.But pattern matrix K can reach and filter out in predetermined search coverage according to the resolution of MLBL-OT imaging the node that absorptance change does not occur.
Traditionally three-dimensional DOT reconstruction mode, in predetermined search coverage, participation is all rebuild by all nodes.But during DOT rebuilds direct problem and inverse problem calculating in need to carry out node to imaging space discrete, three-dimensional reconstruction will cause measurement data far less than reconstruction parameter number, and therefore the less qualitative of inverse problem very seriously, will affect reconstruction speed.In order to effectively reduce the node number of participation reconstruction thus improve less qualitative, under OT-DOT mode: the Jacobi matrix obtained through Newton-Raphson solution by iterative method in pattern matrix K and DOT mode being rebuild does matrix multiplication operation.Matrix obtained like this comprises the reconstruction node in true ROI region and fraction n-ROI region, all participates in reconstruction mode and is optimized, reach the object of the reconstruction nodes reducing n-ROI region to all nodes in conventional three-dimensional DOT reconstruction; Represent that OT-DOT mode computing formula is according to DOT inverse problem math equation when solving three-dimensional optical parameter distribution in organizer:
Ma · Fr Mr - F ( μ a ) = J · KΔ μ a ROI
In formula: F (μ a)---be the boundary sensing point light intensity vector solved by direct problem;
J---under traditional DOT mode through Jacobi matrix that Newton-Raphson iteration Method obtains;
△ μ a rOI---be absorptance change in ROI region after pattern matrix screening;
Although the more traditional DOT mode of n-ROI regional reconstruction node significantly reduces in OT-DOT mode inverse problem, this equation remains deficient fixed, therefore needs to take the regular method of algebraic reconstruction technique (ART) to solve to this equation.Here DOT and the OT-DOT mode provided respectively is rebuild analog imaging outcome measurement value to ROI and is calculated generation, background optical μ by the FEM of direct problem a tbe set to 0.015mm -1, μ ' s tbe set to 2.0mm -1, μ a bbe set to 0.02mm -1, μ ' s bbe set to 1.2mm -1, ROI absorptance is set to 0.03mm -1.B=6.3, L=20 during MLBL-OT calculates.Because FEM calculates the reconstructed value of discrete point, doing the interpolating function that have employed MATLAB in figure process, drawing X-Y cross section, z=12.5mm place and rebuild figure, X-Z cross section, y=30mm place rebuilds figure as shown in Fig. 4 (a) He Fig. 4 (b).In an iterative process, stopping criterion for iteration be set to iteration error change be less than 0.01.Be 28 times reaching DOT mode iterations in identical stopping criterion for iteration situation, OT-DOT iterations is 9 times, show OT-DOT mode comparatively DOT mode significantly improve reconstruction speed.
Although invention has been described by reference to the accompanying drawings above; but the present invention is not limited to above-mentioned detailed description of the invention; above-mentioned detailed description of the invention is only schematic; instead of it is restrictive; those of ordinary skill in the art is under enlightenment of the present invention; when not departing from present inventive concept, can also make a lot of distortion, these all belong within protection of the present invention.

Claims (1)

1., for a bootstrap diffused light chromatography imaging method near infrared light brain function research, it is characterized in that, comprise the following steps:
Step one, press diffusion chromatography imaging detection mode in the predetermined search coverage of head, with adjacent nearest 2 between distance for 10mm and according to rectangular array arrangement source-spys location point, each position point placement optical fiber; During detection, one of them location point is source point, and all the other each points are for visiting point; First, a wherein location point is specified to be source point, obtain the light intensity of spy point position corresponding to this source point, the rest may be inferred, until using each position point all as till source point, measure the detector intensity measurements vector M a and the human body quiescent condition intensity measurements vector M r that obtain predetermined search coverage cerebration state respectively;
The thickness of step 2, scalp and skull layer is h, selects the spy point position light intensity being more than or equal to 2h with source point distance, obtains head predetermined search coverage absorptance changes delta mu according to correction Lambert-Beer topology formation method atwo-dimensional topology image;
Step 3, Iamge Segmentation is carried out to two-dimensional topology image, realizes absorptance region of variation effective location, and generate described predetermined search coverage by the pattern matrix K revising the imaging of Lambert-Beer topology and guide diffusion chromatography imaging, comprise the following steps:
To correction Lambert-Beer topology imaging results with absorptance changes delta mu ain minima carry out Region dividing as threshold value, obtain the brain function region of variation ROI under two-dimensional topology image and brain function region of variation n-ROI do not occur;
Three-dimensional nodes coordinate (x, y, z) and quiescent condition simulation light intensity distribution vector Fr in adopting Finite Element Method to calculate to the predetermined search coverage mathematical model of head;
Whether belong to brain function region of variation ROI according to (x, the y) of three-dimensional nodes coordinate (x, y, z) in the predetermined search coverage of head or brain function region of variation n-ROI does not occur, generating a pattern matrix K computing formula is:
In formula (1): k---be the element in pattern matrix K;
Nr aLL---be the line number of pattern matrix K, represent the call number of three-dimensional nodes in predetermined search coverage interior nodes in brain function region of variation ROI;
Nr rOI---be the row number of pattern matrix K, represent the call number of three-dimensional nodes in brain function region of variation ROI in brain function region of variation ROI;
Step 4, adopt Newton-Raphson solution by iterative method according to diffusion chromatography imaging reconstruction mode, calculate the Jacobi matrix J of predetermined search coverage interior nodes, generate according to matrix K and J and guide diffusion chromatography imaging OT-DOT Reconstructed equation by the imaging of correction Lambert-Beer topology;
Represent that OT-DOT mode computing formula is according to dispersive tomography inverse problem math equation when solving three-dimensional optical parameter distribution in organizer:
Ma · Fr Mr - F ( μ a ) = J · KΔμ a ROI - - - ( 2 )
In formula (2): F (μ a)---be the boundary sensing point light intensity vector solved by direct problem; Δ μ a rOI---be absorptance change in ROI region after pattern matrix screening;
Step 5, absorptance change is calculated in predetermined search coverage to OT-DOT Reconstructed equation, and utilize MATLAB Software on Drawing OT-DOT to rebuild image.
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