WO2023191083A1 - Dispositif d'imagerie tomographique quantique - Google Patents

Dispositif d'imagerie tomographique quantique Download PDF

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WO2023191083A1
WO2023191083A1 PCT/JP2023/013663 JP2023013663W WO2023191083A1 WO 2023191083 A1 WO2023191083 A1 WO 2023191083A1 JP 2023013663 W JP2023013663 W JP 2023013663W WO 2023191083 A1 WO2023191083 A1 WO 2023191083A1
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light pulse
pulse
sample
quantum
image information
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修一郎 井上
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学校法人日本大学
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B10/00—Other methods or instruments for diagnosis, e.g. instruments for taking a cell sample, for biopsy, for vaccination diagnosis; Sex determination; Ovulation-period determination; Throat striking implements
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01B—MEASURING LENGTH, THICKNESS OR SIMILAR LINEAR DIMENSIONS; MEASURING ANGLES; MEASURING AREAS; MEASURING IRREGULARITIES OF SURFACES OR CONTOURS
    • G01B11/00—Measuring arrangements characterised by the use of optical techniques
    • G01B11/24—Measuring arrangements characterised by the use of optical techniques for measuring contours or curvatures
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01J—MEASUREMENT OF INTENSITY, VELOCITY, SPECTRAL CONTENT, POLARISATION, PHASE OR PULSE CHARACTERISTICS OF INFRARED, VISIBLE OR ULTRAVIOLET LIGHT; COLORIMETRY; RADIATION PYROMETRY
    • G01J11/00—Measuring the characteristics of individual optical pulses or of optical pulse trains
    • G—PHYSICS
    • G01—MEASURING; TESTING
    • G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
    • G01N21/00—Investigating or analysing materials by the use of optical means, i.e. using sub-millimetre waves, infrared, visible or ultraviolet light
    • G01N21/17—Systems in which incident light is modified in accordance with the properties of the material investigated

Definitions

  • the present disclosure relates to a quantum tomography device.
  • OCT optical coherence tomography
  • a biological sample is irradiated with light with a low degree of interference, and a tomographic image is acquired by the interference between the reflected light from inside the living body and a reference light.
  • a tomographic image is acquired by the interference between the reflected light from inside the living body and a reference light.
  • OCT is widely used for biological tomography such as the retina of the eye.
  • a tomographic image is acquired by irradiating light onto an observation object and causing reflected light from inside the observation object to interfere with reference light.
  • Patent Document 1 discloses that in the OCT imaging unit of the OCT device, low coherent light is divided into measurement light and reference light, measurement light is irradiated onto the subject's eye to obtain reflected light, and reference light is directed to a reference mirror. These reflected lights (measurement light and reference light) are combined using a fiber coupler, the combined light (interference light) is separated using a spectrometer, and a line sensor separates each wavelength. It describes measuring the intensity information of (see Patent Document 1). Further, Patent Document 2 describes that the imaging device is a device for quantum tomography (see Patent Document 2).
  • Patent Document 3 describes a correlated superconductor single flux quantum analog-to-digital converter using a quantum pulse gate, but there is no description of its application to quantum tomography (see Patent Document 3). ).
  • the above Patent Documents 1 to 3 do not solve the conventional problems as described above.
  • the above-mentioned issues related to biological tomography can be considered to be similar to issues related to non-living samples, and it is difficult to detect not only the reflected light from the sample but also the Raman scattered light from the sample.
  • a similar problem can be considered when photographing the compositional distribution (distribution of proteins, lipids, etc.) of a sample.
  • the present disclosure has been made in consideration of such circumstances, and an object of the present disclosure is to provide a quantum tomography apparatus that can expand the depth of imaging and obtain images with high contrast (high S/N ratio).
  • the task is to
  • One aspect is a quantum tomography apparatus that acquires desired image information on a sample using an optical element having quantum pulse gate characteristics, the light source section outputting a probe light pulse and a pump light pulse; an optical circulator that irradiates the sample with a light pulse and obtains a corresponding light pulse; a delay section that delays the pump light pulse; and a waveform shaping section that shapes the waveform of the pump light pulse; a pump light pulse generation unit that generates the result of the delay and the waveform shaping as a pump light pulse; and the light pulse obtained by the optical circulator and the pump light pulse generated by the pump light pulse generation unit.
  • a combining unit that generates these combined optical pulses; and inputting the combined optical pulse obtained by the combining unit to the optical element, and using the quantum pulse gate characteristic of the optical element to generate the combined optical pulse.
  • a frequency up-converting unit that outputs an up-converted signal light pulse that is a result of up-converting the frequency of a desired signal light pulse included in a combined light pulse; and the up-converted signal output from the frequency up-converting unit.
  • FIG. 1 is a diagram showing a schematic configuration of a quantum tomography apparatus according to an embodiment.
  • FIG. 1 is a diagram showing an example of a specific configuration of a quantum tomography apparatus according to an embodiment.
  • FIG. 3 is a diagram for explaining an example of time resolution measurement using a quantum pulse gate according to an embodiment.
  • FIG. 2 is a diagram illustrating a schematic example of input and output of a quantum pulse gate according to an embodiment.
  • FIG. 1 is a diagram showing an example of a specific configuration of a quantum tomography apparatus according to an embodiment.
  • FIG. 1 is a diagram showing an example of a specific configuration of a quantum tomography apparatus according to an embodiment.
  • a light pulse is usually used, and the time until the reflected light pulse returns is measured based on the time when the light pulse is irradiated.
  • the accuracy of time measurement until the reflected light pulse returns is determined by the time width of the light pulse used for measurement and the time jitter of the photodetector (time resolution in photodetection). It's decided.
  • this embodiment utilizes frequency upconversion for photodetection.
  • Frequency upconversion converts the frequency of the reflected light pulse to a higher frequency by a second-order nonlinear optical process.
  • the reflected light pulse and the pump light pulse are simultaneously incident on a secondary nonlinear optical crystal (nonlinear element) to generate a third, higher frequency light pulse in which the two pulses are combined.
  • the reflected light pulses returning from different depths inside the biological sample are frequency up-converted and detected. do.
  • the resolution of time-resolved measurement is determined not by the time jitter of the photodetector but by the time width of the reflected light pulse. From the time delay of the pump light pulse, information about where the detected light pulse is reflected inside the sample can be obtained, and from this information a tomographic image of the sample can be obtained.
  • a quantum pulse gate (QPG) is used.
  • Normal frequency up conversion is a multimode conversion process that converts a large number of frequency-time modes that satisfy the phase matching condition (the conditions of energy conservation and momentum conservation required for frequency conversion).
  • the phase matching condition the conditions of energy conservation and momentum conservation required for frequency conversion.
  • the signal light pulse that is reflected once and returned by such a QPG is separated from the noise light pulse that returns with its wavefront, phase, polarization, and pulse width changed due to multiple reflections.
  • the frequency-time mode of the optical pulse reflected from inside the living body is investigated in detail by computer simulation.
  • Full-vector electromagnetic field simulation using a numerical inverse Laplace transform method and a difference method is used to analyze light pulses reflected from inside a living body (single reflection and multiple reflections from different depths). At that time, we perform fully parallel calculations that do not require data communication during the calculation process, and analyze frequency-time responses with ultra-high speed and high accuracy.
  • the waveform of the pump light pulse is shaped based on the results of such simulation, and multiple reflected light is removed by QPG. Furthermore, a single photon detector is used for photodetection of QPG. This makes it possible to detect weak light at the single photon level that is reflected from deep within the biological sample. Furthermore, even for samples whose biological functions change due to strong light irradiation, the original biological functions can be observed by irradiating them with weak light.
  • the reflected light pulse also includes multiple reflected light that is multiple reflected (scattered) and returns at the same time as the signal light pulse. Furthermore, it is impossible to separate and measure the signal light pulse and the multiple reflected light. Therefore, in this embodiment, the waveform of the signal light pulse is predicted by removing the multiple reflection (scattering) component by electromagnetic field simulation. This also applies to the description of the embodiments below.
  • FIG. 1 is a diagram showing a schematic configuration of a quantum tomography apparatus according to an embodiment.
  • the quantum tomography apparatus 1 uses an optical element having quantum pulse gate characteristics to acquire tomographic image information at a desired depth in a biological sample.
  • the quantum tomography apparatus 1 includes a laser 10, a probe light pulse irradiation section 11, a branching section 12, an optical circulator 13, a pump light pulse generation section 14, a combining section 15, a frequency upward conversion section 16, and a single unit. It includes a one-photon detector 17 and an information processing section 18.
  • the information processing section 18 includes a first computer 31, which is an example of a first information processing section, and a second computer 32, which is an example of a second information processing section.
  • the process performed by the first computer 31 and the process performed by the second computer 32 will be described as separate processes, but these processes may be performed, for example, by a common process. It may also be executed by a computer. That is, the first computer 31 and the second computer 32 may be configured as a common computer. Further, the processing performed by the first computer 31 and the processing performed by the second computer 32 may be distributed among three or more computers, for example. In this way, the functions of the information processing section 18 may be configured as one unit, or may be configured as two processing sections (first information processing section, second information processing section), for example. Alternatively, it may be configured as three or more processing units.
  • Laser 10 emits laser light pulses.
  • the branching unit 12 branches the laser light pulse emitted from the laser 10 into two branched laser light pulses.
  • the probe light pulse irradiation section 11 irradiates a probe light pulse.
  • the probe light pulse irradiation section 11 generates a probe light pulse by passing one of the branched laser light pulses branched by the branching section 12 through a frequency filter (wavelength filter).
  • the optical circulator 13 irradiates the biological sample with the probe light pulse irradiated by the probe light pulse irradiation unit 11 and obtains the reflected light pulse.
  • the pump light pulse generation section 14 generates a pump light pulse by passing the other branched laser light pulse branched by the branching section 12 through a frequency filter (wavelength filter).
  • a frequency filter wavelength filter
  • the frequency characteristics of the frequency filter are different from those of the frequency filter of the probe light pulse irradiation section 11. That is, the probe light pulse and the pump light pulse have different wavelengths.
  • the pump light pulse before being delayed and waveform shaped is also referred to as a pump light pulse.
  • the pump light pulse generation unit 14 includes a delay unit that delays the pump light pulse (pump light pulse) generated from the other branched laser light pulse branched by the branching unit 12, and a delay unit that delays the pump light pulse (pump light pulse) generated from the other branched laser light pulse branched by the branching unit It has a waveform shaping section that shapes the waveform of the optical pulse (optical pulse), and generates the result of the delay and waveform shaping as a pump light pulse.
  • the combining unit 15 combines the reflected light pulse acquired by the optical circulator 13 and the pump light pulse generated by the pump light pulse generation unit 14 to generate a combined light pulse.
  • the frequency upward conversion unit 16 inputs the combined optical pulse obtained by the combining unit 15 to the optical element, and uses the quantum pulse gate characteristic of the optical element to increase the frequency of the desired signal optical pulse included in the combined optical pulse.
  • the up-converted signal light pulse which is the result of the conversion, is output.
  • the single photon detector 17 detects the up-converted signal light pulse output from the frequency up-conversion section 16 .
  • the first computer 31 is configured using an FPGA (Field Programmable Gate Array).
  • FPGA Field Programmable Gate Array
  • the FPGA acquires tomographic image information of the biological sample based on the upwardly converted signal light pulse detected by the single photon detector 17.
  • the second computer 32 is configured using, for example, a so-called personal computer.
  • the second computer 32 has a function of controlling the FPGA (for example, starting the FPGA, setting delay time and waveform shaping information), and a function of converting data sent from the FPGA into an image. In this way, the second computer 32 creates a tomographic image based on the data sent from the FPGA.
  • the information processing unit 18 controls the delay by the delay unit and the waveform shaping by the waveform shaping unit so that tomographic image information at a desired depth in the biological sample is obtained, and the depth in the biological sample is controlled depending on the magnitude of the delay.
  • it also uses waveform shaping to generate pump light pulses that correspond to the reflected light pulse waveform at each depth in the biological sample. Get image information.
  • FIG. 2 is a diagram showing an example of a specific configuration of the quantum tomography apparatus 101 according to the embodiment.
  • the quantum tomography apparatus 101 is a specific configuration example of the quantum tomography apparatus 1 shown in FIG.
  • the quantum tomography apparatus 101 includes a light source section 111, an optical circulator 112, an objective lens 113, a biological sample 114, a coupler 115, a frequency upward conversion module 116, a single photon detector 117, and a programmable optical delay device. 131, a programmable optical filter 132, an information processing section 141, and a stage 153.
  • the light source section 111 includes a laser 211, a branching section 212, a wavelength filter 213, and a wavelength filter 214.
  • the information processing unit 141 includes an FPGA 151 and an information processing device 152.
  • the information processing device 152 may be, for example, a so-called personal computer.
  • coupler 115, frequency upconversion module 116, single photon detector 117, and information processing section 141 respectively include the laser 10, branching section 12, and probe light pulse irradiation shown in FIG. section 11, optical circulator 13, pump light pulse generation section 14, synthesis section 15, frequency upward conversion section 16, single photon detector 17, and information processing section 18 (first computer 31, second computer 32).
  • the laser 211 is a mode-locked femtosecond pulse laser in this embodiment.
  • Laser 211 emits laser light pulses.
  • the branching unit 212 branches the light pulse (laser light pulse) irradiated from the laser 211 into two light pulses (branched laser light pulses).
  • the wavelength filter 213 filters one branched laser light pulse and outputs it to the optical circulator 112 via an optical fiber (for example, a dispersion shifted fiber).
  • a 1540 nm probe light pulse P1 is input to the optical circulator 112.
  • the optical circulator 112 irradiates the biological sample 114 with a probe light pulse (probe light pulse P1) and obtains the reflected light pulse P3.
  • a probe light pulse P1 from an optical circulator 112 is irradiated onto a biological sample 114 via an optical fiber (for example, a dispersion shifted fiber) and an objective lens 113. Then, the reflected light pulse P3 from the biological sample 114 returns to the optical circulator 112 via the objective lens 113 and the optical fiber, and is then output to the coupler 115 via the optical fiber.
  • an optical fiber for example, a dispersion shifted fiber
  • the wavelength filter 214 filters the other branched laser light pulse and outputs it to the programmable optical delay device 131 via an optical fiber (for example, a dispersion shifted fiber).
  • an optical fiber for example, a dispersion shifted fiber.
  • a 1565 nm pump light pulse is input to the programmable optical delay device 131.
  • the programmable optical delay device 131 (an example of a delay section) provides a delay to the pump light pulse P11.
  • the programmable optical delay device 131 outputs the delayed pump light pulse to the programmable optical filter 132 via an optical fiber (for example, a dispersion shifted fiber).
  • the programmable optical filter 132 (an example of a waveform shaping section) is configured using a waveform shaping device that shapes a waveform.
  • the programmable optical filter 132 shapes the waveform of the delayed pump light pulse.
  • the programmable optical filter 132 outputs the delayed and waveform-shaped pump light pulse P12 to the coupler 115 via an optical fiber (for example, a dispersion shifted fiber).
  • the pump light pulse generation section (programmable optical delay device 131 and programmable optical filter 132) generates the result of delay and waveform shaping performed on the pump light pulse P11 as the pump light pulse P12.
  • waveform shaping is performed after giving a delay to the pump light pulse
  • a delay is given after giving waveform shaping to the pump light pulse.
  • a configuration may be used that simultaneously delays and shapes the pump light pulse.
  • the coupler 115 combines the reflected light pulse P3 acquired by the optical circulator 112 and the pump light pulse P12 generated by the pump light pulse generation section to generate a combined light pulse.
  • the frequency upward conversion module 116 has a function of SFG (Sum Frequency Generation).
  • the frequency upward conversion module 116 inputs the combined optical pulse obtained by the coupler 115 to an optical element, and uses the quantum pulse gate characteristic of the optical element to convert a predetermined signal optical pulse (desired
  • the up-converted signal light pulse P21 which is the result of up-converting the frequency of the signal light pulse
  • the upwardly converted signal light pulse P21 is input to the single photon detector 117.
  • the single photon detector 117 detects the up-converted signal light pulse P21 output from the frequency up-conversion module 116. Single photon detector 117 outputs the detection result to FPGA 151.
  • the information processing unit 141 uses the FPGA 151 and the information processing device 152 to perform predetermined information processing.
  • the FPGA 151 has a function of controlling the optical system, and the information processing device 152 performs comprehensive control including control of the FPGA 151 and generation of tomographic images.
  • the information processing unit 141 arbitrary functions may be determined as the functions of the FPGA 151 and the functions of the information processing device 152, respectively.
  • the manner in which each function is distributed to a plurality of devices is as follows. It may be arbitrary.
  • the information processing unit 141 is composed of a plurality of devices (in the example of FIG. 2, the FPGA 151 and the information processing device 152), but as another configuration example, the information processing unit 141 is It may also be configured as an integrated device.
  • the information processing unit 141 acquires tomographic image information of the biological sample 114 based on the upwardly converted signal light pulse P21 detected by the single photon detector 117.
  • the information processing unit 141 controls the delay by the delay unit (programmable optical delay device 131) and the waveform shaping by the waveform shaping unit (programmable optical filter 132) so that tomographic image information at a desired depth in the biological sample 114 is obtained. do.
  • the information processing unit 141 can acquire (measure) tomographic image information by temporally decomposing it for each depth in the biological sample 114 according to the magnitude of the delay, and also can acquire (measure) tomographic image information in the biological sample 114 by waveform shaping.
  • a pump light pulse corresponding to the reflected light pulse waveform for each depth is generated and tomographic image information is acquired.
  • the information processing unit 141 can control the programmable optical delay device 131 to variably set the delay time given to the pump light pulse by the programmable optical delay device 131.
  • the information processing unit 141 can control the programmable optical filter 132 to variably set the waveform shaping mode performed on the pump light pulse by the programmable optical filter 132.
  • the information processing unit 141 can control the stage 153 to variably change the position of the stage 153.
  • the stage 153 is, for example, an xyz stage that can move along each coordinate (x, y, z) of an xyz orthogonal coordinate system that is a three-dimensional orthogonal coordinate system.
  • the relationship (relative position) between the irradiation position of the probe light pulse P1 irradiated from the objective lens 113 to the biological sample 114 and the position of the biological sample 114 can be determined in each three-dimensional direction. It is possible to adjust (x, y, z).
  • the direction of the distance between the objective lens 113 and the stage 153 is the z direction, and the xy plane (the plane where the biological sample 114 is placed on the stage 153) perpendicular to the z direction ( There is a plane consisting of the y direction).
  • the stage 153 for example, an xy stage that can move along each coordinate (x, y) of an xy orthogonal coordinate system, which is a two-dimensional orthogonal coordinate system, may be used.
  • the quantum tomography apparatus 1 uses an optical element having quantum pulse gate characteristics (an optical element constituting the frequency upward conversion module 116) to create a tomography at a desired depth in the biological sample 114. Get image information.
  • an optical system is used to perform tomography of a biological sample.
  • a mode-locked pulse laser with a wavelength band of 1550 nm and a pulse width ⁇ 100 femtoseconds is used to generate the light pulses and pump light pulses to irradiate the sample.
  • the wavelength of the laser need not be, but may be.
  • pulse spread can be suppressed and a resolution of about 15 ⁇ m in the sample depth direction can be obtained.
  • a biological probe for example, a wavelength of 1,600 to 1,700 nm, which is less absorbed by lipids or water, is a preferable example.
  • the mid-infrared region 3000 to 4000 nm
  • the longer the wavelength the less scattering, but the more absorption by water.
  • An objective lens is used to irradiate the sample with a light pulse (spatial resolution ⁇ 5 ⁇ m), and the sample is swept by an xyz stage.
  • the reflected light pulse from the sample is sent to the fiber coupler by an optical circulator.
  • a time delay is given to the pump light pulse by an optical delay device, and the waveform is shaped by an optical filter.
  • the reflected light pulse and pump light pulse are combined by a fiber coupler and sent to the frequency up conversion module.
  • the frequency of the reflected light pulse is up-converted to a wavelength of 775.5 nm, and detected by a single photon detector 117 (SPCM: detection efficiency ⁇ 85% at 700 nm, dark coefficient: 100 counts/sec) using a silicon avalanche photodiode.
  • SPCM detection efficiency ⁇ 85% at 700 nm, dark coefficient: 100 counts/sec
  • a photon counter built into the FPGA 151 is used.
  • the FPGA 151 controls the optical delay device, waveform shaper, xyz stage for sample scanning, and acquires data from the single photon detector.
  • a tomographic image of the sample is constructed from the time delay of the pump light pulse and the photon detection results.
  • a periodically poled lithium niobate waveguide (PPLN-WG) with a length of 10 mm is used for second harmonic generation that converts into optical pulses with a wavelength of 775.5 nm.
  • PPLN-WG the group velocities of the signal light pulse and the pump light pulse are almost the same by setting the wavelength of the probe light pulse to 1565 nm and the wavelength of the pump light pulse to 1540 nm.
  • electromagnetic field analysis is performed by computer simulation to optimize QPG, and based on the results, waveform shaping of the pump light pulse and evaluation of QPG are performed.
  • FIG. 3 is a diagram for explaining an example of time resolution measurement using the quantum pulse gate according to the embodiment.
  • FIG. 3 shows a quantum pulse gate 311, a biological sample 331, and a single photon detector 312.
  • the quantum pulse gate 311 is a function of the frequency up-conversion module 116 shown in FIG.
  • the biological sample 331 is an example of the biological sample 114 shown in FIG.
  • the single photon detector 312 is an example of the single photon detector 117 shown in FIG. 2.
  • FIG. 3 shows an example of reflective surfaces d1, d2, and d3 of a biological sample 331. These reflective surfaces d1, d2, and d3 are examples for explanation and are not limited thereto.
  • the reflective surface d1 is the surface of the biological sample 331 (the surface to which the probe light pulse P101 is irradiated).
  • the reflective surface d2 is an internal surface of the biological sample 331.
  • the reflective surface d3 is an internal surface of the biological sample 331, and has a deeper depth (distance from the surface toward the inside) than the reflective surface d2.
  • a probe light pulse P101 (an example of the probe light pulse P1 shown in FIG. 2) is irradiated perpendicularly to the surface of the biological sample 331.
  • FIG. 3 shows, as reflected light pulses obtained by reflecting the probe light pulse P101 from the biological sample 331, a reflected light pulse P111 from the reflective surface d1, a reflected light pulse P112 from the reflective surface d2, and a reflected light pulse from the reflective surface d3.
  • P113 and a reflected light pulse P114 which is multiple reflected light (in this example, it is considered as background noise).
  • the reflected light pulse P112 from the reflective surface d2 compared to the reflected light pulse P111 from the reflective surface d1, the reflected light pulse P112 from the reflective surface d2, the reflected light pulse P113 from the reflective surface d3, and the reflected light pulse P114, which is multiple reflected light, are delayed as quantum pulses. It arrives at gate 311.
  • ⁇ 1 to ⁇ 3 shown in FIG. 3 ⁇ 1 is the earliest (shortest) time (that is, the time that arrives at the quantum pulse gate 311 is early), the next is ⁇ 2, and ⁇ 3 is the latest (longest) time ( In other words, the time of arrival at the quantum pulse gate 311 is late).
  • FIG. 3 shows a pump light pulse P131 input to the quantum pulse gate 311.
  • the quantum pulse gate 311 extracts a signal light pulse whose timing matches the pump light pulse and is determined by the waveform of the pump light pulse.
  • the pump light pulse P131 matches the timing (delay) and waveform of the reflected light pulse P113 from the reflecting surface d3.
  • an up-converted signal light pulse P151 which is a signal light obtained by up-converting the frequency of the reflected light pulse P113 from the reflecting surface d3, is output from the quantum pulse gate 311, and single photon detection is performed.
  • the upwardly converted signal light pulse P151 is an example of the upwardly converted signal light pulse P21 shown in FIG.
  • FIG. 4 is a diagram illustrating a schematic example of input and output of the quantum pulse gate 311 according to the embodiment.
  • FIG. 4 shows a group of reflected light pulses P201 that are input (signals) to the quantum pulse gate 311 and a pump light pulse P211 that is input to the quantum pulse gate 311. Further, FIG. 4 shows an upwardly converted signal light P231 and another signal light group P232 which are outputs (signals) from the quantum pulse gate 311.
  • the reflected light pulse group P201 includes a plurality of reflected light pulses.
  • the signal light group P232 includes a plurality of signal light pulses other than the reflected light pulses whose frequency is up-converted to the up-converted signal light P231 by the quantum pulse gate 311.
  • the quantum tomography apparatus can expand the depth that can be imaged and obtain images with high contrast (high S/N ratio). It can be performed.
  • the effect of improving temporal resolution can be obtained by upward frequency conversion.
  • the resolution of time-resolved measurements is independent of the time jitter of the photodetector.
  • the time resolution is determined by the pulse width of the probe light pulse.
  • the quantum pulse gate can improve the S/N ratio. For example, when the time width of time filtering is 1 ns and the frequency band of frequency filtering is 250 GHz, the number of eigenmodes of the optical pulse that can pass through the time-frequency filter is 392.
  • time filtering in frequency upward conversion is determined by the pulse width of the pump light pulse, and frequency filtering is determined by the phase matching band of the nonlinear crystal used.
  • the pulse width of the pump light is 6 ps and the phase matching band is 90 GHz
  • Quantum pulse gates must satisfy phase matching conditions (energy conservation + momentum conservation), group velocity matching conditions, and band conditions.
  • the group velocity matching condition (the group velocity of the signal light pulse and the pump light pulse are the same) is determined by the wavelength dispersion of the nonlinear optical material and the structural dispersion of the wavelength conversion element. For example, when the wavelength conversion element is a PPLN, when the wavelength of the signal light pulse is 1550 nm and the wavelength of the pump light pulse is 860 nm, the group velocities of the signal light pulse and the pump light pulse match, and the signal light pulse has a frequency of 550 nm. Converted upward.
  • the wavelength conversion element is MgO:PPLN
  • the wavelength of the signal light pulse is 1532.1 nm and the wavelength of the pump light pulse is 1556.6 nm
  • the group velocities of the signal light pulse and the pump light pulse are almost the same, and the signal light pulse is The light pulse is frequency upconverted to a wavelength of 772 nm.
  • the band condition is determined by the crystal length and pulse width. When the crystal length is short, pump light with a wide phase matching band and narrow pulse width is required. If these conditions are met, only the signal light pulse can be converted by shaping the waveform of the pump light pulse.
  • quantum pulse gate by applying quantum technology called quantum pulse gate to time-resolved measurement using optical pulses, we are able to achieve a high S/N ratio that is unattainable with ordinary frequency-time filters, and achieve an imaging depth that exceeds that of OCT. It is possible to provide new tomography technology that enables high image quality. Furthermore, by applying tomography technology as in this embodiment to three-dimensional measurement of cerebral vascular structures and realizing deep brain observation using extremely weak light, we can expand the scope of application of brain activity manipulation using optogenetics. Can be expanded.
  • the background noise that returns after multiple reflections within the observation target is removed by a quantum pulse gate using frequency upward conversion.
  • the signal light is converted into the near-infrared region, which can be used with a highly efficient silicon photodetector, by frequency upward conversion, so Photography is also possible.
  • a single photon detector as a photodetector, it is possible to perform tomography using weak light irradiation, and the depth of imaging can be expanded.
  • a tomographic image is acquired by interference of light, but in this embodiment, a tomographic image is acquired by time-resolved measurement of reflected light from an observation target by frequency upward conversion.
  • OCT optical technology
  • tomography is possible with a high S/N ratio, and by using light in the mid-infrared region as the probe light, it is possible to image strong scatterers, and tomography of living organisms and biological samples by irradiating weak light. becomes possible.
  • a quantum technology called a quantum pulse gate is used for light detection, but the light source and optical components used in tomography can be those used in normal optical communications.
  • the quantum pulse gate makes it possible to image more clearly and deeper than conventional techniques.
  • OCT wavelengths such as 810 nm, 1064 nm, 1310 nm, and 1550 nm can be considered. These wavelengths may be used, for example, in biological tomography (biological/medical applications). Further, 1600 to 1700 nm (low lipid/water absorption) and 3000 to 4000 nm (mid-infrared region) are considered. These wavelengths may be used, for example, for non-erosive and non-destructive testing (industrial applications) of strong scatterers, such as drug coatings, automobile/aircraft painting, paintings (works of art), and the like.
  • the configuration of the light source (axial resolution) when using the SHG crystal for example, two wavelengths can be extracted from a femtosecond laser.
  • a quasi-phase matching wavelength conversion element for example, searching for group velocity matching conditions using PPLN, PPKTP, or SLT can be considered.
  • PPLN group velocity matching conditions
  • PPKTP PPKTP
  • SLT SLT
  • Mg:SLT Mg:SLT
  • by setting the wavelength of the probe light pulse to 3880 nm and the wavelength of the pump light to 850 nm it is possible to construct a quantum pulse gate that up-converts the frequency of the signal light pulse to a wavelength of 697.2516.
  • a mid-infrared light source using an OPO can be considered as the light source of the probe light pulse.
  • sample to be observed is not limited to a biological sample, and any sample may be used.
  • the present invention may be applied to a measurement target such as a retina, an anterior segment of the eye, an esophagus, a laminate package, a tablet, or a semiconductor as a sample to be observed.
  • examples of numerical values in this embodiment are not necessarily limited to the numerical values in this embodiment, and other numerical values may be used.
  • a quantum tomography apparatus includes a probe light pulse irradiation unit that irradiates a probe light pulse to a sample, and a probe light pulse irradiation unit that irradiates a probe light pulse to a sample, and a part that corresponds to a signal light pulse to be detected among the reflected light pulses of the probe light pulse that is irradiated to the sample.
  • a pump light pulse generation unit generates a pump light pulse having a delay and a waveform, and a combined light pulse of the reflected light pulse and the pump light pulse is input, and a quantum pulse gate generates the delay and the waveform of the pump light pulse.
  • the present invention includes a frequency up conversion unit that outputs a signal light pulse after frequency up conversion according to the frequency up conversion unit, and a single photon detector that detects the signal light pulse output from the frequency up conversion unit.
  • a quantum tomography apparatus is a quantum tomography apparatus that uses an optical element having quantum pulse gate characteristics to obtain tomographic image information at a desired depth in a biological sample, and irradiates probe light pulses.
  • an optical circulator that irradiates the biological sample with the probe light pulse irradiated from the probe light pulse irradiation unit and obtains the reflected light pulse, and a delay that delays the pump light pulse.
  • a pump light pulse generation section that has a waveform shaping section that shapes the waveform of the pump light pulse, and generates the result of the delay and waveform shaping as a pump light pulse, and a pump light pulse generation section that generates a pump light pulse obtained by the optical circulator.
  • a synthesizing section that synthesizes the reflected light pulse and the pump light pulse generated by the pump light pulse generating section to generate these synthesized light pulses; input into an optical element, and output an upwardly converted signal light pulse that is a result of upwardly converting the frequency of a desired signal light pulse included in the composite light pulse using the quantum pulse gate characteristic of the optical element.
  • the tomographic image information of the biological sample is acquired based on the upwardly converted signal light pulse detected by the detector, and the delay unit is configured to obtain the tomographic image information of a desired depth in the biological sample.
  • the quantum tomography apparatus includes a light source section.
  • the light source section includes a laser that irradiates a laser light pulse, a branching section that branches the laser light pulse irradiated from the laser, and the probe light pulse irradiation section, and one branched by the branching section.
  • a first filter (in this embodiment, the wavelength filter 213) that generates the probe light pulse from the branched laser light pulse, and the other branched laser light pulse that constitutes the pump light pulse generation section and is branched by the branching section.
  • a second filter (in this embodiment, the wavelength filter 214) that generates the pump light pulse from the wavelength filter 214.
  • FIG. 5 is a diagram showing an example of a specific configuration of the quantum tomography apparatus 501 according to the embodiment.
  • the quantum tomography apparatus 501 images the composition distribution (distribution of proteins, lipids, etc.) of the sample by detecting Raman scattered light from the biological sample 114. Therefore, in the example shown in FIG. 5, compared to the example shown in FIG. 2, a part of the configuration is changed to accommodate such imaging.
  • the quantum tomography apparatus 501 includes a light source section 511 instead of the light source section 111 in the example of FIG.
  • the light source section 511 includes a laser 611, an amplifier system 612, and a wavelength variable TWINOPA 613.
  • Laser 611 irradiates light onto amplifier system 612 .
  • Laser 611 is an 810 nm mode-locked titanium sapphire laser in this embodiment.
  • the amplifier system 612 amplifies the light from the laser 611 and irradiates the wavelength tunable TWINOPA 613 with the amplified light.
  • Amplifier system 612 is a femtosecond amplifier system in this embodiment.
  • the wavelength tunable TWINOPA 613 uses light from the amplifier system 612 to provide two independently variable outputs.
  • one of these two variable outputs is a probe light pulse P501, and the other one is a pump light pulse before delay and waveform shaping (in this embodiment, for convenience of explanation, (Also referred to as pump light pulse P511.)
  • OPA Optical Parametric Amplifier
  • TWIN represents outputting two independent variable outputs.
  • the light source unit 511 outputs two optical pulses (a probe light pulse P501 and a pump light pulse P511) having different wavelengths compared to the example shown in FIG.
  • the probe light pulse P501 is irradiated onto the biological sample 114 via the optical circulator 112.
  • the probe light pulse P501 is, for example, shorter than 100 fs and has a wavelength of 533 nm to 2600 nm.
  • the pump light pulse P511 is input to the programmable optical delay device 131.
  • the pump light pulse P511 is, for example, shorter than 100 fs and has a wavelength of 1160 nm to 9000 nm.
  • the objective lens 113 is schematically shown in the example of FIG. A configuration in which scan lenses are provided one after another may be used.
  • a polarization maintaining fiber may be used as the fiber for transmitting each light.
  • polarization-maintaining and dispersion-compensating fibers may be used between optical circulator 112 and coupler 115 and between coupler 115 and frequency upconversion module 512.
  • the pump light pulse P512 output from the programmable optical filter 132 and the Raman scattered light pulse P503 from the optical circulator 112 are combined by the coupler 115, and these combined light pulses are sent to the frequency upward conversion module. 512.
  • the quantum tomography apparatus 501 includes a frequency up conversion module 512 instead of the frequency up conversion module 116 in the example of FIG.
  • the frequency upward conversion module 512 is configured using a crystal (nonlinear crystal) different from the crystal (nonlinear crystal) of the frequency upward conversion module 116 in the example of FIG.
  • the crystal corresponds to the Raman scattered light from the biological sample 114.
  • the information processing unit 141 performs control (information processing) corresponding to Raman scattered light instead of the control in the example of FIG.
  • the information processing unit 141 controls the delay by the delay unit (programmable optical delay device 131) and the waveform shaping by the waveform shaping unit (programmable optical filter 132) so that desired Raman scattered light image information in the biological sample 114 is obtained.
  • the delay unit programmable optical delay device 131
  • the waveform shaping programmable optical filter 132
  • the example in FIG. 5 is different from the example in FIG. 2 in the following (A1) to (A5).
  • A1 In the example of FIG. 2, reflected light from the biological sample 114 is acquired, but in this embodiment, Raman scattered light when the biological sample 114 is irradiated with probe light is acquired.
  • A2) In order to realize the above (A1), the wavelength of the pump light is changed compared to the example of FIG. 2.
  • A3) In order to realize the above (A2), the wavelength difference between the probe light and the pump light is increased compared to the example of FIG. 2.
  • OPA optical parametric amplifier
  • a configuration using two light sources may be used.
  • the wavelength of the pump light may be switched while keeping the wavelength of the probe light constant.
  • the wavelength of the pump light is determined so that the group velocity within the nonlinear crystal of the Raman scattered light generated by the probe light pulse and the pump light pulse are the same.
  • the wavelength difference between the probe light and the pump light is determined by the material of the nonlinear crystal used in the SFG.
  • a nonlinear crystal (SLT in this embodiment) different from that in the example of FIG. 2 is used in the SFG frequency upward conversion module in the example of FIG.
  • SLT nonlinear crystal
  • manual or automatic control is performed to use different nonlinear crystals (switch crystals) for tomography and imaging of composition distribution by Raman scattered light.
  • the sample does not have to be a biological sample, and can be applied to, for example, an automobile paint or coating sample, a semiconductor sample, or the like.
  • the composition of the sample can be known from the detection result of the single photon detector 117.
  • the wavelength of the probe light constant and switching several wavelengths of the pump light, it is possible to switch the compositional components (for example, proteins, fats, etc.) to be observed in a biological sample.
  • the compositional components for example, proteins, fats, etc.
  • a probe light of 1064 nm and a pump light of 3113 nm are used for samples of objects such as semiconductors that do not contain water.
  • samples of objects such as semiconductors that do not contain water, it is possible to observe deeper parts of the sample using a 3113 nm probe light and a 1064 nm pump light. Noise can be suppressed.
  • the quantum tomography apparatus 501 can expand the imaging depth and obtain images with high contrast (high S/N ratio). By detecting the Raman scattered light, the composition distribution (distribution of proteins, lipids, etc.) of the biological sample 114 can be photographed with high accuracy. Further, in the quantum tomography apparatus 501 according to the present embodiment, it is possible to obtain similar effects not only for the biological sample 114 but also for samples other than the biological sample.
  • the configuration of the optical system (quantum tomography apparatus 101) shown in FIG. 2 and the configuration of the optical system (quantum tomography apparatus 501) shown in FIG. 5 may be implemented independently.
  • the same biological sample 114 may be subjected to tomographic imaging using the optical system shown in FIG. 2 and imaging using Raman scattered light using the optical system shown in FIG. 5.
  • a probe light pulse irradiated onto a biological sample uses a light pulse with a wavelength of 1064 nm, which is known as the "biological window" in which water absorption is minimal.
  • the Mg:SLT crystal as a nonlinear medium
  • a light pulse with a wavelength of 3113 nm in the mid-infrared region as a pump, the group velocity condition required for QPG is satisfied.
  • the frequency band of the pump light pulse becomes wider than the phase matching band, and the second QPG condition can be satisfied.
  • a light pulse with a wavelength of 3113 nm as a probe light and a light pulse with a wavelength of 1064 nm as a pump tomography of a sample with strong light scattering is also possible.
  • black body radiation which becomes background noise in light detection in the mid-infrared region, can also be removed by QPG.
  • ⁇ About the example in Figure 5> when a biological sample is irradiated with a light pulse, spontaneous Raman scattered light is generated that reflects the molecular vibrations of biological molecules.
  • the wavelength of this spontaneous Raman scattered light depends on the wavelength of the probe light pulse irradiated onto the biological sample.
  • a biological sample is irradiated with a light pulse having a wavelength of 1064 nm in order to suppress light absorption and light scattering inside the living body.
  • the Raman shifts due to molecular vibrations constituting lipids and proteins are 2850 cm ⁇ 1 and 2930 cm ⁇ 1 , respectively, and the corresponding wavelengths of spontaneous Raman scattered light are 1526.7 nm and 1545.6 nm.
  • an Mg:SLT crystal with a length of 10 mm is used, and light pulses with wavelengths of 2175 nm and 2145 nm in the mid-infrared region are used as pumps, respectively.
  • Spontaneous Raman scattered light is measured in a time-resolved manner using QPG, and information regarding the molecular structure is added to the tomographic image of the biological sample.
  • an optical system shown in FIG. 5 is constructed to perform tomography of a biological sample.
  • an optical parametric amplifier uses a mode-locked titanium sapphire laser (laser 611) amplified by a femtosecond amplifier system (amplifier system 612) as the pump light. (Wavelength variable TWINOPA613) is used.
  • the wavelength tunable TWINOPA 613 can independently select and output two wavelengths from the wavelength ranges of 533 nm to 2600 nm and 1160 nm to 9000 nm.
  • the pulse width is 40 to 50 fs, and a resolution of 10 ⁇ m or less in the depth direction of the sample is achieved.
  • a two-axis galvanometer mirror is used to irradiate the biological sample 114 with a light pulse.
  • the reflected light pulse from the biological sample 114 is sent to the fiber coupler (coupler 115) by the optical circulator 112.
  • the pump light pulse P511 is given a time delay by an optical delay device (programmable optical delay device 131), and waveform shaped by an optical filter (programmable optical filter 132). (pump light pulse P512) is generated.
  • the reflected light pulse (Raman scattered light pulse P503) and the pump light pulse P512 are combined by a fiber coupler (coupler 115) and sent to the frequency upward conversion module 512.
  • a signal light pulse having a wavelength of 1064 nm (or 3113 nm) is converted to a wavelength of 793 nm. Further, the spontaneous Raman scattered light in the wavelength band of 1550 nm is converted into wavelengths of 896 nm and 898 nm, respectively.
  • These frequency up-converted photons are detected by a single photon detector 117 (SPCM: detection efficiency ⁇ 85%@700 nm, dark coefficient: 100 counts/sec) using a silicon avalanche photodiode.
  • the FPGA 151 controls the optical delay device (programmable optical delay device 131), the optical filter (programmable optical filter 132), and the two-axis galvanometer mirror, and acquires data from the single photon detector 117. For example, information about lipids and proteins obtained by time-resolved measurement of spontaneous Raman scattering light in the wavelength band of 1550 nm is finally superimposed on a tomographic image obtained by time-resolved measurement of signal light pulses with a wavelength of 1064 nm reflected inside the living body. can do. This makes it possible, for example, to visualize amyloid ⁇ accumulation in the brain of Alzheimer's disease model mice without staining.
  • the group velocities of the two optical pulses are matched by a combination of the wavelength and the SLT crystal, in which the optical pulses of 1064 nm and 3113 nm are frequency-up-converted using a nonlinear crystal called SLT, and the background noise is reduced. achieving oppression.
  • a 1064 nm light pulse is used to probe the biological sample 114, Raman scattered light is generated in the 1550 nm band.
  • the group velocities can be matched by using a 2 ⁇ m band optical pulse as pump light. Note that whether the group velocities match is determined by the physical properties of the nonlinear crystal and the wavelength of the optical pulse used, so the combination of wavelength and SLT crystal as in this example has its own characteristics.
  • Quantum tomography device that can switch the imaging target
  • a quantum tomography apparatus may be implemented in which the imaging target can be switched by switching between an optical system as shown in FIG. 2 and an optical system as shown in FIG. 5.
  • FIG. 6 is a diagram showing an example of a specific configuration of the quantum tomography apparatus 701 according to the embodiment.
  • configurations different from the example of FIG. 2 will be explained in detail, and detailed explanations of configurations similar to the example of FIG. 2 will be omitted.
  • FIG. 6 and its explanation the same components as in the example of FIG. 2 will be described with the same reference numerals.
  • the quantum tomography apparatus 701 includes a light source section 711 instead of the light source section 111 in the example of FIG.
  • the light source section 711 includes a wavelength switching section 811.
  • the wavelength switching unit 811 is configured to perform different wavelength tomography for performing quantum tomography using reflected light as in the example of FIG. 2, and for performing quantum tomography using Raman scattered light as in the example of FIG.
  • the wavelength of at least one of the probe light pulse and the pump light pulse is switched so as to match the wavelength of the probe light pulse and the pump light pulse.
  • the wavelength switching unit 811 performs quantum tomography using reflected light as in the example of FIG. 2, and quantum tomography using Raman scattered light as in the example of FIG.
  • the wavelength of the pump pulse light may be switched to match each.
  • the quantum tomography apparatus 701 includes a frequency up conversion module 716 instead of the frequency up conversion module 116 in the example of FIG.
  • the frequency up conversion module 716 includes a crystal switching section 812 .
  • the crystal switching unit 812 includes the crystal in the example of FIG. 2 and the other crystal in the example of FIG. 5, and can be used for quantum tomography using reflected light as in the example of FIG. Depending on whether quantum tomography is performed using Raman scattered light as in the example of FIG. 5, the crystal used for frequency upward conversion is switched to suit each case.
  • the switching of the wavelength switching section 811 in the light source section 711 and the switching of the crystal switching section 812 in the frequency upward conversion module 716 are controlled by the FPGA 151.
  • the FPGA 151 Note that other configurations of the optical system may be different depending on whether quantum tomography is performed using reflected light as in the example in FIG. 2 or quantum tomography is performed using Raman scattered light as in the example in FIG. Parts may be switched.
  • the crystal of the frequency upward conversion module 716 may be used for quantum tomography using reflected light as in the example of FIG.
  • a common crystal may be used when performing quantum tomography.
  • the quantum tomography apparatus 701 according to the example of FIG. 6 can perform quantum tomography using reflected light as in the example of FIG.
  • a tomographic image of the biological sample 114 is obtained in general, and information regarding the composition of the biological sample 114 obtained from the wavelength of the Raman scattered light is added to the tomographic image. Can be superimposed.
  • the quantum tomography apparatus 701 according to the example of FIG. 6 it is possible to grasp which composition exists in which tomographic location of the biological sample 114.
  • the quantum tomography apparatus 701 according to the example of FIG. 6 it is possible to obtain similar effects for samples other than living bodies, for example.
  • ⁇ Configuration Example 1> to ⁇ Configuration Example 5> are shown.
  • ⁇ Configuration example 1> A quantum tomography apparatus that obtains desired image information on a sample using an optical element having quantum pulse gate characteristics, a light source unit that outputs probe light pulses and pump light pulses; an optical circulator that irradiates the sample with the probe light pulse and obtains a corresponding light pulse;
  • a pump light pulse that includes a delay unit that delays the pump light pulse and a waveform shaping unit that shapes the waveform of the pump light pulse, and generates the result of the delay and waveform shaping as a pump light pulse.
  • a generation section a combining unit that combines the optical pulse acquired by the optical circulator and the pump optical pulse generated by the pump optical pulse generating unit to generate a combined optical pulse;
  • the synthesized light pulse obtained by the synthesizer is input to the optical element, and the frequency of the desired signal light pulse included in the synthesized light pulse is upwardly converted by the quantum pulse gate characteristic of the optical element.
  • a frequency up conversion unit that outputs an up converted signal light pulse as a result of the above conversion
  • a single photon detector that detects the up-converted signal light pulse output from the frequency up-conversion section
  • Information processing department Equipped with The information processing unit includes: acquiring the image information of the sample based on the up-converted signal light pulse detected by the single photon detector; Quantum tomography device.
  • a quantum tomography apparatus that uses the optical element to obtain tomographic image information at a desired depth in the sample,
  • the sample is a biological sample
  • the light source section is a laser that emits laser light pulses; a branching part that branches the laser light pulse irradiated from the laser; a first filter that constitutes a probe light pulse irradiation section and generates the probe light pulse from one branched laser light pulse branched by the branching section; a second filter that constitutes the pump light pulse generation section and generates the pump light pulse from the other branched laser light pulse branched by the branching section; including;
  • the optical circulator irradiates the sample with the probe light pulse irradiated from the probe light pulse irradiation unit and obtains the reflected light pulse,
  • the combining unit combines the reflected light pulse obtained by the optical circulator and the pump light pulse generated by the pump light pulse generation unit to generate a combined light pulse
  • the information processing unit includes: acquiring the tomographic image information
  • the tomographic image information by decomposing the tomographic image information, and also to generate the pump light pulse corresponding to the reflected light pulse waveform for each depth in the sample by the waveform shaping, and to obtain the tomographic image information. make it possible to obtain The quantum tomography apparatus described in ⁇ Configuration Example 1>.
  • a quantum tomography apparatus that uses the optical element to obtain desired Raman scattered light image information in the sample,
  • the optical circulator irradiates the sample with the probe light pulse to obtain a Raman scattered light pulse
  • the combining unit combines the Raman scattered light pulse obtained by the optical circulator and the pump light pulse generated by the pump light pulse generation unit to generate a combined light pulse
  • the information processing unit includes: acquiring the Raman scattered light image information of the sample based on the up-converted signal light pulse detected by the single photon detector;
  • the delay by the delay section and the waveform shaping by the waveform shaping section are controlled so that the desired Raman scattered light image information in the sample is obtained, and the time delay is controlled for each depth in the sample depending on the magnitude of the delay.
  • the Raman scattered light image information can be obtained by decomposing the Raman scattered light image information, and the pump light pulse matching the Raman scattered light pulse waveform for each depth in the sample is generated by the waveform shaping. enables the acquisition of optical image information, The quantum tomography apparatus described in ⁇ Configuration Example 1>.
  • ⁇ Configuration example 4> A quantum tomography apparatus that uses the optical element to obtain tomographic image information at a desired depth in the sample and desired Raman scattered light image information,
  • the light source section changes the wavelength of at least one of the probe light pulse and the pump light pulse in a first mode of acquiring the tomographic image information and a second mode of acquiring the Raman scattered light image information. switch, The quantum tomography apparatus described in ⁇ Configuration Example 1>.
  • ⁇ Configuration example 5> The frequency upward conversion unit switches the optical element between the first mode and the second mode.
  • the optical element is configured using SLT, The quantum tomography apparatus described in ⁇ Configuration Example 1>.
  • configuring an optical element having quantum pulse gate characteristics using SLT may be employed in any of the configuration examples ⁇ Configuration Example 1> to ⁇ Configuration Example 5>.
  • SLT by using SLT, it is possible to configure a QPG that can detect mid-infrared probe light.
  • QPG using SLT for photodetection of mid-infrared light, background noise due to black body radiation can be removed.
  • the configuration "using SLT to configure a QPG that can detect mid-infrared probe light” can be applied to any system (or device, etc., regardless of the above embodiments).
  • the configuration "using QPG using SLT for light detection of mid-infrared light" can be applied to any system (or may be called a device), etc., regardless of the above embodiments. This may be applied, and the effect of this is that background noise due to black body radiation can be removed.
  • a program for realizing the functions of any component in any device described above may be recorded on a computer-readable recording medium, and the program may be read and executed by a computer system.
  • the "computer system” herein includes an operating system or hardware such as peripheral equipment.
  • “computer-readable recording media” refers to portable media such as flexible disks, magneto-optical disks, ROMs, CDs (Compact Discs) and ROMs (Read Only Memory), and storage devices such as hard disks built into computer systems. Refers to a device.
  • a "computer-readable recording medium” refers to a volatile memory within a computer system that serves as a server or client when a program is transmitted via a network such as the Internet or a communication line such as a telephone line. This also includes those that hold time programs.
  • the volatile memory may be, for example, RAM (Random Access Memory).
  • the recording medium may be, for example, a non-transitory recording medium.
  • the above program may be transmitted from a computer system storing the program in a storage device or the like to another computer system via a transmission medium or by a transmission wave in a transmission medium.
  • the "transmission medium” that transmits the program refers to a medium that has a function of transmitting information, such as a network such as the Internet or a communication line such as a telephone line.
  • the above-mentioned program may be for realizing a part of the above-mentioned functions.
  • the above-mentioned program may be a so-called difference file, which can realize the above-described functions in combination with a program already recorded in the computer system.
  • the difference file may be called a difference program.
  • any component in any device described above may be realized by a processor.
  • each process in the embodiment may be realized by a processor that operates based on information such as a program, and a computer-readable recording medium that stores information such as a program.
  • the functions of each part may be realized by separate hardware, or the functions of each part may be realized by integrated hardware, for example.
  • a processor includes hardware, and the hardware may include at least one of a circuit that processes a digital signal and a circuit that processes an analog signal.
  • a processor may be configured using one or more circuit devices or one or more circuit elements mounted on a circuit board. An IC (Integrated Circuit) or the like may be used as the circuit device, and a resistor or a capacitor may be used as the circuit element.
  • the processor may be, for example, a CPU.
  • the processor is not limited to the CPU, and various processors such as a GPU (Graphics Processing Unit) or a DSP (Digital Signal Processor) may be used.
  • the processor may be, for example, a hardware circuit using an ASIC (Application Specific Integrated Circuit).
  • the processor may be configured by, for example, a plurality of CPUs or a hardware circuit by a plurality of ASICs.
  • the processor may be configured by, for example, a combination of a plurality of CPUs and a hardware circuit using a plurality of ASICs.
  • the processor may include, for example, one or more of an amplifier circuit or a filter circuit that processes an analog signal.
  • Second computer 111, 511, 711 ...Light source section, 113...Objective lens, 114, 331...Biological sample, 115...Coupler, 116, 512, 716...Frequency upward conversion module, 131...Programmable optical delay device, 132...Programmable optical filter (waveform shaper), 151 ...FPGA, 152... Information processing device, 153... Stage, 213, 214... Wavelength filter, 311... Quantum pulse gate, 612... Amplifier system, 613... Wavelength variable TWINOPA, 811... Wavelength switching section, 812... Crystal switching section

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Abstract

L'invention concerne un dispositif d'imagerie tomographique quantique, qui utilise un élément optique ayant une caractéristique de porte d'impulsions quantiques pour acquérir des informations d'image tomographique à une profondeur souhaitée dans un échantillon biologique; il émet une impulsion de lumière de sondage sur l'échantillon biologique et acquiert une impulsion de lumière réfléchie provenant de celui-ci; il comprend une unité de retard pour communiquer un retard à une impulsion pour le pompage de lumière, et une unité de mise en forme d'ondes pour effectuer une mise en forme d'ondes de l'impulsion pour le pompage de lumière; il produit une impulsion de lumière de pompage suite au retard et à la mise en forme d'ondes; il combine l'impulsion de lumière réfléchie et l'impulsion de lumière de pompage pour produire une impulsion de lumière combinée à partir de celles-ci; il fait entrer l'impulsion de lumière combinée dans l'élément optique; et, en utilisant une caractéristique de porte d'impulsions quantiques de l'élément optique, il utilise un détecteur de photons uniques pour détecter une impulsion de lumière de signal montée en fréquence obtenue suite à une conversion d'élévation de fréquence d'une impulsion de lumière de signal souhaité présente dans l'impulsion de lumière combinée.
PCT/JP2023/013663 2022-03-31 2023-03-31 Dispositif d'imagerie tomographique quantique WO2023191083A1 (fr)

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MINAMI SAEGUSA, SEIYA KISHIMOTO, SHUICHIRO INOUE, SHINICHIRO ONUKI, YU NAKAZAWA: "C-15-5 Optical Pulse Reflection Characteristics in Large-Scale Elliptic Cylinders", PROCEEDINGS OF THE 2021 IEICE ELECTRONICS SOCIETY CONFERENCE; SEPTEMBER 14-17, 2021, IEICE, JP, 31 August 2021 (2021-08-31) - 17 September 2021 (2021-09-17), JP, pages 164, XP009549876 *
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