WO2015015557A1 - Dispositif de mesure biophotonique - Google Patents

Dispositif de mesure biophotonique Download PDF

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Publication number
WO2015015557A1
WO2015015557A1 PCT/JP2013/070521 JP2013070521W WO2015015557A1 WO 2015015557 A1 WO2015015557 A1 WO 2015015557A1 JP 2013070521 W JP2013070521 W JP 2013070521W WO 2015015557 A1 WO2015015557 A1 WO 2015015557A1
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pressure
unit
subject
measurement device
light
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PCT/JP2013/070521
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English (en)
Japanese (ja)
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司 舟根
洋和 敦森
木口　雅史
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株式会社日立製作所
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Priority to PCT/JP2013/070521 priority Critical patent/WO2015015557A1/fr
Priority to JP2015529245A priority patent/JP5997384B2/ja
Publication of WO2015015557A1 publication Critical patent/WO2015015557A1/fr

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/40—Detecting, measuring or recording for evaluating the nervous system
    • A61B5/4058—Detecting, measuring or recording for evaluating the nervous system for evaluating the central nervous system
    • A61B5/4064—Evaluating the brain
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00—Measuring for diagnostic purposes; Identification of persons
    • A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence

Definitions

  • the present invention relates to a technique for measuring an oxygenated state of a biological tissue or a hemodynamic change in the tissue, particularly in a biological optical measurement device using visible light or near infrared light.
  • a brain function measurement device (see Patent Document 1) using near-infrared spectroscopy (see NIRS) is used as a medical and research device, or for confirming educational and rehabilitation effects, home health management, It can be used for market research such as merchandise monitors. Moreover, it can be used for tissue oxygen saturation measurement and oxygen metabolism measurement of muscle tissue by the same method. Furthermore, it can be used for general absorption spectroscopy equipment, such as sugar content measurement of fruits.
  • Non-Patent Document 2 3
  • quantification of the signal contribution derived from the surface tissue is an issue.
  • the degree of influence of the surface layer signal changes depending on the skin-brain distance (brain depth)
  • the acquisition of tissue structure parameters is an important issue.
  • a short light source that transmits only the surface tissue, and a probe arrangement for the distance between the detectors are used to measure the change in blood volume in the surface tissue, and a long irradiation-detector distance (A method of removing the influence of the surface structure by subtracting from the signal acquired by (SD distance) has been proposed.
  • spatially resolved spectroscopy that quantifies the optical properties of the tissue after measuring multiple points with long irradiation, the distance between detectors, where the relative influence of the surface tissue can be ignored, and assuming the uniformity of the biological tissue. is there.
  • anatomical structure information when anatomical structure information is not assumed or unknown, a technique that enables measurement of oxygenation state or blood volume change in the deep part and shallow part using optimum analysis parameters in each condition is required.
  • anatomical structure information cannot be used or is unknown in ordinary NIRS measurement, and it is desirable to use optimum values for each subject and each part without assuming anatomical structure information in advance.
  • One method is to eliminate the influence of surface tissue by making the scalp close to ischemia using a tourniquet, but it is necessary to pressurize the scalp at the light irradiation position and the detection position. In the past, it has been difficult to perform such measurements efficiently and with good reproducibility.
  • Non-Patent Document 4 describes a method for acquiring information on the SD distance dependency of the NIRS signal in a state in which the scalp is pressurized with a probe and the surface layer signal is suppressed. There is no description about the device for pressurizing. When the scalp is pressed through a probe, particularly in the case of manual operation, it is difficult to apply pressure stably in time, and there is a problem that a portion where compression is unnecessary is also pressed.
  • anatomical data In order to realize high-precision measurement even in measurement parts and subjects with different degrees of influence of surface tissue in a biological optical measurement device that measures oxygen saturation or hemodynamic change in deep tissue and shallow tissue, anatomical data And means for obtaining parameters, particularly parameters related to brain depth. In addition, a means for efficiently compressing the skin of the subject is provided.
  • the biological light measurement device of the present invention has a pressure measurement unit, a pressure receiving unit that receives pressure, and a pressurization unit that pressurizes the subject at the irradiation and detection position of light in the subject.
  • the irradiation-detector distance dependence of the blood volume change derived from the deep part, which is the internal information of the subject, is calculated. Furthermore, using the dependency, the signal at the time of non-pressurization is separated into a deep part signal and a shallow part signal, and the contribution ratio of the shallow part signal is quantified.
  • one or a plurality of light irradiation means for irradiating the subject with light, and a predetermined irradiation point on the subject is irradiated from the light irradiation means.
  • One or a plurality of light detection means for detecting light propagating in the subject at a predetermined detection point on the subject, and an analysis unit for analyzing a signal obtained by the light detection means A pressure receiving unit for receiving an applied pressure, a pressure control unit for controlling the pressure applied to the pressure receiving unit, and the light receiving unit and the light detecting unit.
  • a pressure unit that transmits the pressure received in step 1 to the surface tissue of the subject, a state confirmation unit for confirming the hemostatic state, ischemic state, or vascular occlusion state of the subject, and the analysis unit includes As a result of analysis and the state confirmation means A display unit that can display a result of the analysis, and a storage unit that can store a result analyzed by the analysis unit and a result of the state confirmation unit, and the analysis unit applies a predetermined pressure to the pressure receiving unit.
  • information on the inside of the subject is obtained from a signal at the time of pressurization obtained by calculating a signal obtained by the light detection means when the subject is pressurized at a predetermined pressure in the pressurizing unit.
  • a non-obtained value obtained by calculating a signal acquired by the light detection means when no pressure is applied to the subject from the pressurizing unit or when the pressure is not applied is obtained.
  • a deep signal mainly derived from a deep tissue and a shallow signal mainly derived from a shallow tissue, which are included in the signal at the time of pressurization, are respectively obtained.
  • the present invention it is possible to easily determine in-vivo internal information, tissue structure information, or analysis parameters for accurately measuring an oxygenation state of a living tissue or a hemodynamic change in the tissue.
  • the body tissue is compressed with good reproducibility and efficiency, and the surface tissue is in a state close to hemostasis or ischemia. You can get sex.
  • the flowchart showing the procedure of the measurement and analysis according to Example 1 of this invention.
  • the flowchart which shows the procedure which acquires a subject internal information.
  • the flowchart which shows the procedure which acquires the deep part signal and shallow part signal which are contained in the non-pressurization signal from the non-pressurization signal and the subject internal information.
  • FIG. 1 an example of the apparatus structure of the biological light measuring device of this invention is shown.
  • a biological light measurement device capable of detecting light incident on a living body and detecting the light that is scattered / absorbed and propagated in the living body and emitted to the outside of the living body
  • the light is irradiated from one or a plurality of light sources 101 included in the apparatus main body 20.
  • the light 30 is incident on the subject 10 through the waveguide 40 for propagating the light.
  • the light 30 enters the subject 10 from the irradiation point 12, passes through and propagates through the subject 10, and then passes through the waveguide 40 from the detection point 13 at a position away from the irradiation point 12. It is detected by one or more photodetectors 102.
  • the SD distance is defined by the distance between the irradiation point 12 and the detection point 13 as described above.
  • the one or more light sources 101 are a semiconductor laser (LD), a light emitting diode (LED) or the like, and the one or more photodetectors are an avalanche photodiode (APD), a photodiode (PD), a photoelectron amplifier, or the like.
  • a double tube (PMT) or the like may be used.
  • the waveguide 40 may be any medium that can propagate the wavelength used, such as an optical fiber, glass, or light guide.
  • the light source 101 is driven by a light source driving device 103, and the multiplication factor and gain of one or a plurality of photodetectors 102 are controlled by a control / analysis unit 106.
  • the control / analysis unit 106 also controls the light source driving device 103 and receives an input of conditions and the like from the input unit 107.
  • the electrical signal obtained by photoelectric conversion by the photodetector 102 is amplified by the amplifier 104, converted from analog to digital by the analog-digital converter 105, sent to the control / analysis unit 106, and processed.
  • a method for detecting a minute signal and separating a plurality of signals a method of driving a plurality of light sources by an intensity modulation method, detecting a lock-in of a signal detected by a photodetector, and performing analog-to-digital conversion, There is a method of performing a lock-in process digitally after amplifying and analog-to-digital conversion of the signal from the signal.
  • the present invention is not limited to this, and for example, a time division method for discriminating a plurality of lights by shifting the timing of irradiating a plurality of lights in time, or a spread spectrum modulation method can be used.
  • the light source 101 and the photodetector 102 may be integrated with the waveguide 40.
  • the light source elements such as LD and LED, and light detection elements such as PD and APD in the probe, there are effects such as reduction of light loss, downsizing of equipment, cost reduction, and reduction of power consumption. is there.
  • the control / analysis unit 106 performs analysis based on the signal detected by the photodetector 102. Specifically, based on the method described in Non-Patent Document 1, for example, based on the received digital signal obtained by conversion by the analog-digital converter 105, the detected light amount change or absorbance From the changes, oxygenated and deoxygenated hemoglobin changes (oxy-Hb, deoxy-Hb) are calculated.
  • oxygenated and deoxygenated hemoglobin change is a value corresponding to a change amount of a product of the hemoglobin concentration and the effective optical path length.
  • the amount of change in hemoglobin concentration may be calculated by substituting the effective optical path length.
  • control / analysis unit 106 has been described on the assumption that the driving of the light source 101, the gain control of the photodetector 102, and the signal processing from the analog-digital converter 105 are all performed. And having the means for integrating them can also realize the same function.
  • the measurement data and the calculation result of the hemoglobin change are stored in the storage unit 108, and the measurement result can be displayed on the display unit 109 based on the analysis result and / or the stored data.
  • the light transmitter 50 includes, for example, a waveguide 40 on the light source 101 side, and is installed in contact with or close to contact with the subject 10.
  • the light receiver 60 includes, for example, the waveguide 40 on the light detector 102 side, and is placed in contact with or close to contact with the subject 10.
  • the living body optical measurement device of the present invention includes a pressure receiving portion 14 for receiving an applied pressure, a pressurizing portion 15 for transmitting the pressure received by the pressure receiving portion 14 to the subject 10, and the subject.
  • the pressure sensor 16 for confirming the state of hemostasis or ischemia in 10 surface tissues is provided.
  • the pressure control unit 11 includes means for efficiently applying pressure to the pressure receiving unit 14 and controlling the pressure to be applied.
  • the pressurization control unit 11 may be manually controlled or automatically controlled by an electromagnetic method.
  • the pressurization control unit may be detachable. Since the pressurization control unit is not necessary when performing measurement at the time of non-pressurization, the probe can be reduced in weight without changing the performance by removing the pressurization control unit. Reducing the weight of the probe reduces the burden on the subject.
  • the control / analysis unit 106 applies a predetermined pressure to the pressure receiving unit 14 to calculate the signal obtained by the photodetector 102 when the subject 10 is pressurized by the pressurizing unit 15. Information on the inside of the subject is acquired from the pressure signal.
  • the display unit 109 preferably displays pressure information at the time of measurement or notifies by sound. As a result, the operator can check whether the pressure is stably applied. At this time, if the pressure sensor 16 is installed inside the holding portion 17, it is possible to form a flat surface in which the unevenness of the pressurizing portion is reduced.
  • the holding unit 17 that comes into contact with the subject 10 the light transmitter 50 and the light receiving unit 60 that are held by the holding unit 17, and components including peripheral components are called probes.
  • the light transmitter 50 and the light receiver 60 may be the light source 101 and the photodetector 102, respectively.
  • the pressure sensor 16 is installed on the surface or inside of the holding unit 17 or the probe, and measures the pressure between the pressurizing unit 15 and any one of the irradiation point 12 and the detection point 13.
  • the pressure sensor 16 is for the purpose of confirming the hemostatic state, ischemic state, or occlusion state of the blood vessel in the surface tissue of the subject 10 by measuring the pressurization state. It is only necessary that the parameters to be acquired can be acquired.
  • the method using the pressure sensor 16 was demonstrated here, by analyzing a frequency component using biological signals, such as a pulse oximeter and a laser Doppler blood flow meter, in addition to a pressure sensor, specifically, May be a method of confirming the hemostatic state, ischemic state, or vascular occlusion state in the surface tissue of the subject 10 by confirming that the pulse wave signal is small. Further, these methods may be used in combination with the pressure sensor 16. In this way, by separately acquiring biological signals having different measurement principles or independent, there is a possibility that the blood state can be measured with higher accuracy than in the case of measuring with only the pressure sensor.
  • biological signals such as a pulse oximeter and a laser Doppler blood flow meter
  • step S201 pressure is applied from the pressurization unit 15 to the subject 10 by applying pressure to the pressure receiving unit 14 by the pressurization control unit 11 (step S201).
  • step S202 a pressurization signal is acquired (step S202).
  • the visual (color lamp) or auditory means You may alert
  • step S203 subject internal information is acquired from the signal at the time of pressurization (step S203).
  • step S204 the pressure from the pressurizing unit is released (step S204).
  • a non-pressurization signal is acquired (step S205), and a deep signal and a shallow signal included in the non-pressurization signal are acquired from the non-pressurization signal and the subject internal information (step S206). ).
  • a deep signal and a shallow signal included in the non-pressurization signal are acquired from the non-pressurization signal and the subject internal information (step S206).
  • the pressurization signal may be acquired after acquiring the non-pressurization signal. Since the signal at the time of pressurization is for the purpose of acquiring the internal information of the subject, that is, the structural parameter, if it has already been acquired, it may be determined that it is unnecessary to acquire the signal at the time of pressurization again. Furthermore, although the acquisition of the signal at the time of pressurization and the acquisition of the signal at the time of non-pressurization are described here as separate measurements, the pressure is released after acquiring the signal at the time of pressurization during one measurement, An unpressurized signal may be acquired.
  • the signal derived from the surface tissue is expected to show a transient response at the time of change between the pressurized state and the non-pressurized state. Need to spend some time. For example, about 10 seconds is considered necessary. Even in the procedure of obtaining both the signal at the time of pressurization and the signal at the time of non-pressurization by this single measurement, the procedure of obtaining the signal at the time of pressurization and then obtaining the signal at the time of pressurization may be used.
  • step S301 the method of using independent component analysis as the signal separation method has been described.
  • methods such as principal component analysis and factor analysis may be used.
  • a method using a detected light amount or a representative amplitude of hemoglobin change may be used.
  • the subject internal information (Xi gr ) obtained in step S304 is a value corresponding to the intercept of the SD distance axis in the SD distance-dependent line of the mean effective optical path length of the gray matter, and the photon reaches the gray matter ( Minimum SD distance for sensitivity to light absorption changes in gray matter).
  • the subject internal information may be other parameters related to the subject head structure, such as a parameter depending on the thickness of each layer of the head tissue, a parameter proportional to the gray matter depth, and the like.
  • the slope of the regression line may be extracted as the internal information.
  • the slope of the regression line represents amplitude information and depends on the task performed by the subject. By combining with the task information, it can be an effective database for knowing the characteristics of the task (effects on changes in cerebral blood volume and skin blood volume, etc.).
  • FIG. 4 is a diagram showing the irradiation-detector (SD) distance dependency of the average effective optical path length of skin and gray matter in the human head.
  • the horizontal axis is the SD distance
  • the vertical axis is the average effective optical path length or partial optical path length.
  • the average effective optical path length (74) in the skin does not change much at the SD distance of 10 to 40 mm, but the average effective optical path length (75) in gray matter increases linearly with the SD distance. To do. Therefore, as the SD distance increases, the gray matter-derived component in the NIRS measurement signal increases, but the skin-derived component is not expected to change.
  • the average distance of the gray matter effective optical path length is obtained by using the SD distance axis (70) as the intersection of the linear regression line (72) and the SD distance axis (70) obtained by linear regression using the data of the SD distance of 10 mm to 40 mm.
  • An x-axis intercept (denoted Xi gr ) (73) can be obtained.
  • the value is about 10 mm.
  • This Xi gr is an analysis parameter for brain and skin separation.
  • the bio-internal information obtained here is used as an analysis parameter for removing deep and shallow signals, but if already acquired, the acquired data stored in the storage unit 108 or the memory is read and the control / analysis unit 106 is read out. May be used.
  • the SD contribution axis intercept 73 is necessary for the deep part contribution rate calculation formula, but since it differs depending on the measurement site in an individual or even in the same individual, it is analyzed that the optimum value for each subject and the measurement site is extracted from the memory. It is effective for improving the accuracy of results.
  • step S501 independent component analysis is applied to multi-distance measurement data (voltage data detected as a detected light quantity or hemoglobin change converted from voltage data) measured at the time of non-pressurization (step S501).
  • step S501 the signal contribution at each SD distance is calculated from the independent components and their weights (step S502).
  • step S503 An intercept (Xi ex ) is calculated (step S503).
  • step S504 the deep contribution rate of each independent component is calculated from Xi gr and Xi ex and the SD distance (x) for calculating the contribution rate (step S504).
  • step S504 when calculating the deep contribution ratio and the shallow contribution ratio of each independent component, for example, the expressions shown in Table 1 are used (see Non-Patent Document 4).
  • the deep signal and the shallow signal are reconstructed from the independent components and the respective contribution ratios of the deep part and the shallow part using, for example, Equation 1 (step S505).
  • r dp Ci is the depth contribution ratio of the independent component i
  • W Ci Pj is the weight of the independent component i at the measurement point m
  • u Ci is the time series data of the independent component i
  • ⁇ CL is hemoglobin (oxygenation, (Or deoxygenation) deep signal.
  • the shallow portion signal can be obtained by using the shallow portion contribution ratio or subtracting the deep portion signal from the original signal.
  • the shallow signal thus obtained is effective for examining the task dependency of the blood volume change in the surface tissue and for examining the influence of individual differences on the blood volume change of the surface tissue. Further, by examining in advance the contribution of the shallow signal to the NIRS signal, there is an effect that an effective guideline can be obtained for data interpretation by a method other than the multi-distance arrangement.
  • FIG. 6 is a diagram showing a probe cross section in the case of an arrangement having a plurality of irradiation-detector distances (multi-distance arrangement) for performing measurement according to the first embodiment of the present invention.
  • the holding unit 17 for holding the light transmitter 50 and the light receiver 60 is installed so as to provide a gap 18 between the holding unit 17 and the subject 10.
  • the material of the holding portion 17 it is desirable to use hard rubber, plastic, or the like that hardly generates internal stress (not easily deformed).
  • the gap 18 is effective in concentrating the pressure applied to the subject 10 from the pressurizing unit 15 directly under the pressurizing unit 15 or the probe. Furthermore, the space
  • gap 18 has a role as a space which escapes the biological tissue pressed and pressed by the pressurization part 15. FIG. Thereby, it is effective in efficiently transmitting the pressure 21 applied from the pressurization control unit 11 to the pressure receiving unit 14 from the pressurization unit 15 to the subject 10. That is, there is an effect that a larger pressure can be applied with a smaller force. When there is no gap 18, the applied pressure is dispersed and the applied pressure needs to be increased. The gap does not transmit the pressure and has an effect of limiting the pressurizing region. However, in order to realize the same effect, the pressure from the pressure receiving unit 14 may be replaced with a material that is difficult to transmit to the pressurizing unit 15.
  • the holding unit 17 checks whether the subject can be pressurized with a predetermined pressure, that is, confirms the hemostatic state, ischemic state, or vascular occlusion state in the surface tissue of the subject 10.
  • a pressure sensor 16 is installed. Since the temporal change of the pressure applied to the subject 10 via the pressurizing unit 15 affects the NIRS signal, it is necessary to always monitor it.
  • the pressure sensor 16 is preferably installed inside the probe. Since the pressure sensor 16 is not installed on the surface of the pressurizing unit 15, the planarity of the living tissue contact portion can be maintained. Therefore, there is an effect that pressure can be uniformly applied to the subject 10.
  • the hemostatic state in the surface tissue of the subject 10, the ischemic state, or the vascular occlusion state may be confirmed by the absence of the heartbeat pulse.
  • the pulsation of the heartbeat the presence or absence of the pulsation of the NIRS waveform may be visually checked, the output value of the pressure sensor, or an optical measurement system installed in the immediate vicinity of the NIRS probe may be used.
  • the optical measurement system here may be based on a technique such as a pulse oximeter or a photoelectric volume pulse wave measuring device (photoplethysmography). From the measurement result by the optical measurement system, the pressure is determined based on the presence or absence of a pulsation (pulse wave) component.
  • reporting means such as visual (color lamp) or an auditory means (sound).
  • a visual signal color lamp
  • informing means such as auditory means (sound).
  • a configuration may be used in which one detector is added and one 5 mm measuring point is added. Furthermore, this measurement point with an SD distance of 5 mm can be used for evaluation of separation performance after separation of brain and skin-derived signals. Further, when it is assumed that the skin blood flow is uniform in the measurement range of interest, the measurement point with an SD distance of 5 mm can be used as a reference signal and used for analysis for separating the skin blood flow component.
  • the pressure receiving unit 14 receives a pressure from the outside and transmits the pressure to the subject 10 via the pressurizing unit 15.
  • the pressure receiving unit 14 has a pressure in the holding unit 17 or the probe.
  • the generating means it may be configured to include the pressure receiving portion inside.
  • NIRS device such as a brain oxygen monitor, a tissue oxygen monitor device, and an optical brain function measuring device such as optical topography.
  • the pressurization region at the time of pressurization is arranged so as to surround the irradiation point or the detection point at the time of installation on the subject. It is configured to include a circle having a radius of 5 mm, preferably a circle having a radius of 10 mm, centered on the center point of each of the irradiation point and the detection point. If a circle with a radius of 5 mm is used, the pressurizing unit 15 has a relatively small area, and there is an effect that the surface blood immediately below the probe can be suppressed to some extent. When the radius is 10 mm, it is necessary to increase the pressure applied to the pressure receiving portion 14 during pressurization, but this has a more remarkable effect in suppressing blood changes in the surface tissue.
  • enlarging the pressurizing region requires the application pressure to be increased in order to transmit the predetermined pressure to the subject 10, and is not a practical means especially when assuming that the pressurization is performed manually. It is important to find the minimum applied pressure that can sufficiently suppress the surface tissue-derived signal by using information from the pressure sensor 16 or the like.
  • FIG. 7 is a diagram showing the configuration of the holding portion having a gap and the surroundings.
  • the upper figure shows the cross section AA and the lower figure shows the cross section BB.
  • a contact fixing unit 24 is provided around the space 18.
  • the pressurizing unit 15 includes a light source 101 and a light detector 102.
  • the light source 101 and the detector 102 transmit pressure.
  • a configuration that does not transmit pressure may be used.
  • the living body contact portion 24 is provided with the living body contact portion 24 in addition to the pressurizing portion 15 and has the gap 18, the living body contact portion is configured to be difficult to apply pressure.
  • the gap 18 is effective for concentrating the pressure on the pressurizing unit 15 and reducing the force applied to the pressure receiving unit.
  • the light source 101 and the detector 102 are configured to transmit pressure to the subject 10
  • an optical fiber bundle curved and bent in an L shape is used as the waveguide 40, and the periphery of the fiber is made of metal or plastic. This can be realized by covering with a covering and further integrating with the covering and the holding portion 17.
  • it is possible to transmit the pressure to the subject 10 via the housing of the optical element by arranging the elements of the light source and the photodetector in contact with the holding unit and transmitting the pressure applied to the pressure receiving unit. is there.
  • FIG. 8 is a cross-sectional view of a probe having a circular pressure part and a contact fixing part having a curvature.
  • the pressurizing portion is flat, and the living body contact portion located below the place where the holding band 26 is connected has a curvature that matches the curved surface of the living body surface.
  • the pressure is dispersed.
  • the material constituting the biological contact portion 25 having a curvature may be an elastic body such as a rubber material or plastic.
  • a configuration having a gap or a member that hardly transmits pressure may be used.
  • FIG. 9 is a diagram showing an effective optical path length distribution in the scalp obtained by a photon propagation simulation.
  • the effective optical path length is expressed in shades. The darker the color, the greater the effective optical path length.
  • the 100 photon paths are weighted and averaged according to the detected light quantity, and the surface layer
  • the effective optical path length is calculated for each voxel (2 mm ⁇ 2 mm ⁇ 3 mm mm (skin thickness)) located in the tissue.
  • the diameter of the irradiation / detection point was assumed to be 1.5 mm.
  • the distribution of the surface layer tissue (scalp) optical path length is concentrated around the irradiation point 12 and the detection point 13 and in a straight line connecting the irradiation point 12 and the detection point 13.
  • it is concentrated in a circle having a radius of 5 mm with the irradiation point 12 and the detection point 13 as the centers. Therefore, if this region is pressurized, it is possible to effectively suppress changes in blood volume in the surface tissue that contribute to changes in the detection light.
  • it is effective to compress a blood vessel for flowing blood flowing into this region, so it is important to simultaneously compress the region around this region. Therefore, in practice, the radius may be set to about 10 to 15 mm in consideration of the stability when the pressure unit is fixed.
  • the optimal pressure area varies depending on conditions. If the burden at the time of pressurization is not taken into consideration, it is considered that pressing a sufficiently wide range is effective in suppressing the blood volume of the surface tissue.
  • the photon propagation simulation result on the assumption of the head structure and the optical characteristic distribution it is possible to determine a region where pressurization can be performed efficiently with a minimum.
  • By creating a simulation model of the head structure using the results of MRI, X-ray CT, etc. it is possible to determine the optimum pressure region for each subject.
  • the shape of the pressurizing unit 15 is not limited to a circle, and it is more effective that the shape preferably covers the shape of the effective optical path length distribution. That is, the pressurizing unit 15 is configured to include a region that covers a predetermined ratio (for example, 95%) or more of the total effective optical path length in the surface tissue in the distribution of the effective optical path length in the surface tissue of the detection light. That's fine.
  • FIG. 10 is a view showing a probe having a pressurizing region adjusting means 28. Since the optimal pressurization region varies depending on the subject, the measurement site, and the possible pressurization range, it is effective to adjust the pressurization region according to the conditions.
  • a probe having a pressurizing region adjusting means will be described.
  • the pressurizing region adjusting means 28 is for adjusting the area of the pressurizing unit 15 that is a region for transmitting the pressure 21 applied from the pressurizing control unit 11 to the pressure receiving unit 14 to the surface of the living body.
  • it is a member that can be attached to and detached from the probe (or the holding portion 17), and may be any member that can be inserted into a groove installed in the inner wall of the holding means constituting the gap 18.
  • the area of the pressure unit 15 can be increased.
  • the probe can be configured according to various conditions (examinee, measurement site, possible pressurization range). There is an effect that it is possible to reduce the trouble of exchanging probes with different parts.
  • the effective optical path changes according to the SD distance
  • the appropriate pressure area changes, so even when measuring multiple SD distances, the pressure area can be changed according to the SD distance. .
  • head structure data is acquired from an MRI, an X-ray CT image, probe position information, an eyelid database, etc. (step S1101).
  • an absorption coefficient and a scattering coefficient are assumed with reference to documents and the like (step S1102).
  • the photon propagation path is calculated by the photon propagation simulation using the scattering coefficient and the absorption coefficient according to the algorithm (step S1103). For example, a Monte Carlo simulation or a method of solving a light diffusion equation by a finite element method may be used.
  • the effective optical path length distribution in the surface tissue is calculated in consideration of the absorption coefficient distribution (step S1104).
  • the ratio to the total detected power (and the margin of the pressurizing area) is set (step S1105).
  • the margin here is a certain margin width from a region including a predetermined ratio with respect to the total detection power. By giving a margin width and designating a wider range as the pressurization region, it becomes possible to sufficiently compress the blood vessel under the region necessary for pressurization.
  • a pressurization area is calculated (step S1106).
  • the pressure area is adjusted using the pressure area adjusting means 28 (step S1107).
  • the procedure from step S1101 to step S1106 described above may be performed by the control / analysis unit 106 or may be performed offline by the user.
  • FIG. 12 is a view showing a holding unit having a pressed position guide means.
  • the holding unit 17 that holds the light transmitter 50 and the light receiver 60 includes a pressing position guide unit 80.
  • the pressed position guide means 80 is displayed at a place where pressure can be applied to the subject 10 from the pressurizing unit 15 most effectively. For example, it is arranged at the midpoint between the light transmitter 50 and the light receiver 60 set to an SD distance of about 30 mm.
  • the pressure receiving unit 14 is not shown in the drawing, it is in the same position as the position of the pressed position guide means 80 here. As a result, when pressure is applied manually, it serves as a guide for the location of pressing, so there is an effect that measurement can be performed easily with good reproducibility.
  • FIG. 13A is a view showing a cross section of a holding portion having a pressure receiving portion with a recess.
  • the holding portion 17 that holds the light transmitter 50 and the light receiver 60 includes a pressure receiving portion 81 having a recess. Since the holding portion 17 has the concave portion in the pressure receiving portion 14, it becomes effective for concentrating manual pressure on the pressure receiving portion 14 as well as being a tactile guide.
  • FIG. 13B is a view showing a cross section of the holding portion having the protrusion-like slip stopper.
  • FIG. 14 is a view showing a holding unit having a bent or curved waveguide.
  • the light transmitter 50 and the light receiver 60 held in the holding unit 17 have a waveguide 41 having a bend or a curve.
  • the light transmitter 50 and the light receiver 60 have an effect of reducing physical and spatial obstacles and transmitting the pressure efficiently. That is, there is an effect of eliminating spatial interference with the pressurization control unit 11.
  • the light transmitter 50 and the light receiver 60 are configured by an optical fiber or the like, the possibility that the light transmitter 50 and the light receiver 60 will break due to contact during manual pressure application is reduced.
  • an optical element such as a light source element and a detector element may be arranged directly in a positional relationship close to contact with the subject.
  • FIG. 15 (a) is a view showing a cross section of a holding portion having a handle.
  • a handle 22 is connected to the holding unit 17 as the pressurization control unit 11 for applying pressure to the pressure receiving unit 14.
  • the handle 22 may be removable.
  • FIG. 15 (b) is a view showing a cross section of a holding portion having a handle and an elastic mechanism.
  • the probe module including the pressure receiving unit 14 and the pressurizing unit 15 is fixed to the subject 10 by the holding unit 17 via the elastic mechanism 29.
  • the handle 22 as the pressurizing control unit 11 to the pressure receiving unit 14 on the probe module so as not to interfere with the holding unit 17, the handle 22 can be moved even when the holding unit 17 has the elastic mechanism 29.
  • the pressure can be directly applied to the pressure receiving unit 14 via the pressure sensor 14.
  • FIG. 16A is a view showing a cross section of the holding portion 17 having a pressurizing mechanism.
  • the pressure mechanism 23 applies pressure to the pressure receiving unit 14.
  • the pressurizing mechanism 23 may be mechanical, electromagnetic, hydraulic, or the like. In particular, a gas or liquid pressure may be used, or an elastic body may be pressed against the subject 10 by pressing the pressurizing portion by screwing. Or the structure which adjusts the pressure just under the said member by screwing a bolt-shaped member in the belt wound around a head may be sufficient.
  • the pressurizing mechanism 23 may be fixed to the subject 10, and thereby, a configuration may be adopted in which pressure is effectively applied to the contact portion of the subject 10 with the pressurizing unit 15.
  • the pressurizing mechanism 23 may be removable.
  • FIG. 16B is a diagram showing a cross section of the probe when the pressure receiving portion 14 is pressurized with an air bag.
  • An air bag 27 is used as a pressurizing mechanism. As the air bladder 27 expands, pressure is applied to the pressure receiving portion 14. Then, the pressure applied to the pressure receiving unit 14 is transmitted to the surface of the living body via the pressurizing unit 15.
  • By controlling the air pressure of the air bag by electromagnetic means it is possible to adjust the pressure applied to the surface of the living body with high accuracy and good reproducibility. Thereby, it becomes possible to pressurize a living body surface with high reproducibility using automatic control, and it becomes possible to solve the subject that a pressurization pressure may change with the date of measurement or an individual so far. Further, when the applied pressure is controlled by the air pressure from an external pump and the air pressure is measured and monitored by an external device, a configuration in which the pressure sensor is not provided in the holding unit 17 is possible.
  • the storage unit 108 stores and stores the pressure information, the measurement data, and the internal structure information in which the surface blood flow is sufficiently suppressed for each subject and for each part, so that the same subject can measure again. In doing so, automatic compression can be efficiently performed by reading the corresponding pressure information and internal structure information from the storage unit 108. Alternatively, when it is not necessary to remeasure the internal structure information, it is possible to omit the measurement during pressurization.
  • the surface layer is sufficiently obtained by using a means for confirming the hemostatic state, ischemic state, or occlusion state of the blood vessel in the surface tissue of the subject 10 such as the pressure sensor 16.
  • the pressure can be automatically adjusted to suppress the influence of blood flow in the tissue.
  • the probe arrangement having a plurality of irradiation-detector (SD) distances has been described above, an example of an application example in the case of one SD distance arrangement will be described.
  • the flow of estimating the absorption contribution of the surface layer component when using the probe with the normal SD distance arrangement according to the second embodiment will be described with reference to the flowchart shown in FIG.
  • the normal SD distance arrangement refers to, for example, a probe arrangement with a light source-detector distance of 30 mm.
  • step S1701 by applying a pressure 21 to the pressure receiving unit 14, the pressure is applied from the pressurizing unit 15 to the subject 10, and a signal at the time of pressurization is acquired (step S1701).
  • step S1702 the pressure from the pressurizing unit 15 is released, and a non-pressurization signal is acquired (step S1702).
  • step S1703 the absorption contribution ratio of the surface layer component is calculated (step S1703).
  • FIG. 18 is a diagram showing a cross section of the probe when the irradiation-detector (SD) distance is about 30 mm.
  • the light transmitter 50 and the light receiver 60 are held by the holding unit 17, and light is incident on the subject 10 to detect the light (light path distribution: 31) that has propagated through the subject 10.
  • the holding part 17 has a gap 18, and a low reflector 19 is disposed on the inner wall of the gap 18.
  • the pressure 21 applied from the pressurization control unit 11 to the pressure receiving unit 14 is transmitted from the pressurization unit 15 to the subject 10 via the holding unit 17.
  • the pressure applied to the subject 10 is detected by the pressure sensor 16.
  • the pressurization method the method described in Embodiment 1 may be used.
  • the light detected by the light receiver 60 is attenuated in both the surface tissue and the deep tissue, absorption by blood or the like in the surface tissue is reduced by the pressure on the surface tissue of the subject 10. Thereby, the absorption contribution rate by the blood of a surface layer component can be estimated.
  • the absorption contribution ratio of the surface layer component By quantifying the absorption contribution ratio of the surface layer component by blood, for example, there is an effect that it can be used to select a measurement point having a small influence of the surface layer component in NIRS measurement.
  • tissue oxygen saturation measurement and muscle oxygen metabolism measurement by similar methods Used as a means to improve spatial resolution in biological measurement devices that can be used for radiology, especially devices that use probes with multiple irradiation-detector distances (SD distances) to separate surface and deep components, etc. it can.
  • SD distances irradiation-detector distances

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Abstract

La présente invention permet d'obtenir une mesure hautement précise, même pour un sujet ou une position de mesure pour lequel/laquelle le degré d'impact sur le tissu de surface varie. L'invention concerne un moyen d'acquisition d'un paramètre destiné à ce qui précède et est associé à la profondeur cérébrale. Un dispositif de mesure biophotonique comprend : une unité de mesure de la pression ; une unité de réception de la pression pour recevoir la pression ; une unité de pression pour mettre sous pression un sujet à une position d'émission et de détection de lumière dans le sujet ; et une section de régulation de la pression pour réguler la pression appliquée à la section de réception de la pression. On calcule, à partir des mesures réalisées pendant la mise sous pression, la dépendance de la distance, entre un émetteur et un détecteur, des changements de quantité de sang qui sont une information interne du sujet et proviennent d'une zone profonde. À l'aide de cette dépendance, un signal au moment de non mise sous pression est divisé en signaux provenant des régions profondes et en signaux provenant des régions peu profondes et la contribution des signaux provenant des régions peu profondes est quantifiée.
PCT/JP2013/070521 2013-07-29 2013-07-29 Dispositif de mesure biophotonique WO2015015557A1 (fr)

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US11089969B2 (en) * 2013-12-05 2021-08-17 Veriskin, Inc. Skin perfusion monitoring device
EP3895607A4 (fr) * 2018-12-14 2022-09-28 Sony Group Corporation Appareil de mesure de signaux biologiques

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JP4896874B2 (ja) * 2004-05-11 2012-03-14 コーニンクレッカ フィリップス エレクトロニクス エヌ ヴィ 非侵襲血液分析用の測定ヘッド
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Cited By (3)

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Publication number Priority date Publication date Assignee Title
US11089969B2 (en) * 2013-12-05 2021-08-17 Veriskin, Inc. Skin perfusion monitoring device
US11826130B2 (en) 2013-12-05 2023-11-28 Veriskin, Inc. Skin perfusion monitoring device
EP3895607A4 (fr) * 2018-12-14 2022-09-28 Sony Group Corporation Appareil de mesure de signaux biologiques

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