JP2013244122A - Spectroscopic measurement device - Google Patents

Abstract

PROBLEM TO BE SOLVED: To solve the problem that photoacoustic waves of energy proportional to optical absorptance are not generated and measurement accuracy declines when the size of a heat generation part (photoacoustic wave generation part) is below the pulse length of the photoacoustic waves, in a spectroscopic measurement device which irradiates a specimen with the selected heating pulse light of a specific wavelength and measures the energy of the photoacoustic waves generated inside a living body.SOLUTION: A spectroscopic measurement device includes: a light source for generating pulse light to be radiated to a specimen; an ultrasonic probe for receiving ultrasonic pulses generated inside the specimen; and a signal processing part for calculating the generation part and intensity of the ultrasonic pulses generated inside the specimen on the basis of signals received in the ultrasonic probe. By irradiating the specimen with the pulse light before and after irradiating the specimen with light generated in the light source or a different light source, the density distribution of a desired component can be more highly accurately measured.

Description

  The present invention relates to a spectroscopic measurement apparatus that measures the light absorption characteristics of an inspection object and a measurement method thereof.

  The spectroscopic measurement device that measures the light absorption characteristics inside the living tissue can measure the concentration distribution of various components using different light absorption characteristics (relationship between the wavelength of light and the absorption rate) for each substance. It is used in various fields for medical diagnosis. For example, it is possible to measure the concentration distribution of oxygenated hemoglobin and deoxygenated hemoglobin in the body, determine the formation of new blood vessels associated with tumor growth, oxygen saturation of hemoglobin, etc., and use it for diagnosis. Moreover, the density | concentration of the fat contained in the plaque in a blood vessel can be measured, and it can also utilize for the characteristic (fat degree) of a plaque.

  Such an apparatus uses near-infrared light having a wavelength of about 600 to 1500 nm, which has high transmission characteristics for living tissue. However, the light transmitted through the living tissue propagates while repeating strong scattering by cells of several tens of μm size constituting the living body, and thus becomes multiple scattered light (diffused light). With this diffused light, it is difficult to obtain local light absorption characteristics in the living tissue because all the paths through which the light propagates cannot be specified.

  For this reason, in the conventional inspection apparatus, the following apparatuses have been developed as a method for measuring the local light absorption characteristics in the living tissue.

  In an apparatus as shown in Patent Document 1, the light absorption rate of each part is obtained by irradiating a living tissue with light of a specific wavelength and obtaining a change in sound velocity in the living body between irradiation and non-irradiation. By obtaining the absorption rate of light of a plurality of wavelengths by the same method, it is possible to obtain the absorption spectrum distribution (absorption characteristics) of each region in the living body.

  FIG. 2 is a schematic diagram of an ultrasonic diagnostic apparatus (spectral measurement apparatus) using the spectral characteristics disclosed in Patent Document 1.

  The spectroscopic measurement apparatus in FIG. 2 includes at least a light source 101 and an ultrasonic measurement apparatus 102.

  The operation will be described below.

  (1) Ultrasonic velocity measurement process (first time): The internal structure of the living body 104 is measured using the ultrasonic measurement device 102. The ultrasonic measurement device 102 includes an ultrasonic probe 102a, a measurement device main body 102b, and a cable 102c that connects the two. The measurement apparatus main body 102b transmits an electric signal for vibrating the ultrasonic probe 102a via the cable 102c. The ultrasonic pulse generated by the ultrasonic probe 102a is applied to the living body 104, and the ultrasonic pulse reflected by each part in the living body 104 is converted again into an electric signal in the ultrasonic probe 102a and the measurement apparatus main body. (The reflection of the ultrasonic pulse occurs at the boundary between the parts having different densities and sound speeds). In the measurement apparatus main body 102b, an electrical signal from the ultrasonic probe 102a is stored.

  (2) Selection light heating process start: The selective heating light 105 is irradiated toward the living body 104 using the light source 101 including the laser light source 101a and the optical fiber 101b that guides the laser light generated by the laser light source 101a to the living body.

  (3) Ultrasonic sound velocity measurement step (second time): Again, similarly to (1), the internal structure of the living body 104 is measured using the ultrasonic measurement device 102.

  (4) Sound velocity change calculation step: The ultrasonic pulse waveforms (electrical signals) reflected from the living body 104 obtained in (1) and (3) are compared, and each part in the living body 104 before and after the step (2) is compared. Obtain the amount of change in sound speed.

  Here, the selective heating light 105 selects light having an optimum wavelength according to the application.

  For example, when it is desired to measure the concentration of fat contained in the plaque 106 in the blood vessel, selective heating light having a wavelength of about 1200 nm having a high fat absorption rate is used.

  The higher the fat concentration, the higher the absorption rate of the selective heating light and the greater the amount of change in the sound speed. Therefore, by comparing the sound speed before and after irradiation of the selective heating light of the plaque 106, the fat concentration distribution can be obtained. It becomes.

  However, as described above, the spectroscopic measurement apparatus that heats the specimen with the selective heating light having a specific wavelength and measures the change in the sound speed of each part has a measurement accuracy that is affected by the contraction of the specimen due to pulsation or the like.

  Therefore, as shown in Patent Document 2, by irradiating a living tissue with pulsed light and instantaneously heating the living tissue, the photoacoustic wave generated by the photoacoustic effect generated based on the light energy is locally generated. A method for measuring light absorption characteristics in a typical region has been proposed.

  The apparatus of Patent Document 2 includes a pulse light source 301 and an ultrasonic measurement apparatus 102 as schematically shown in FIG.

  The operation will be described below.

  (1) Photoacoustic wave generation step: The selective heating pulsed light 302 is directed to the living body 104 using the pulsed light source 301 including the pulsed laser light source 301a and the optical fiber 101b that guides the pulsed laser light generated by the pulsed laser light source 301a to the living body. Irradiate. Thereby, instantaneous heat generation occurs at a portion where the light absorption rate with respect to the selective heating pulse light 302 is high, and the instantaneous expansion accompanying the temperature rise generates an ultrasonic wave (photoacoustic wave).

  (2) Photoacoustic wave measurement step: The photoacoustic wave in the living body 104 is received by the ultrasonic measuring device 302 provided with the ultrasonic probe 102a, and the generation location and the generated energy are obtained, whereby the light in the living body is obtained. The part with a high absorption rate is obtained.

  As in the case of Patent Document 1 (in the case of FIG. 2), when pulse light with a wavelength of, for example, 1200 nm is used as the selective heating pulse light 302, the intravascular blood vessel with high fatiness is determined from the photoacoustic wave energy and the generation position. It is possible to determine the position and fatness of the plaque 106.

  Further, the spectroscopic measurement apparatus can be applied to applications other than living body applications (gas component analysis and inspection of foreign matters mixed in food). Further, as shown in Patent Documents 1 and 2, in addition to the example using ultrasonic waves, an example in which a temperature increase due to light heating is measured by a thermocouple, a radiation thermometer, or the like has been studied.

US Patent Application Publication No. 2010/0043557 US Pat. No. 5,843,0023

  However, in the spectroscopic measurement device that measures the energy of photoacoustic waves generated in the living body by irradiating the specimen with selective heating pulsed light having a specific wavelength as described above, the above-described heat generation points (photoacoustics) such as cancer and plaque are used. When the size of the wave generation location is smaller than the pulse length of the photoacoustic wave, the photoacoustic wave having energy proportional to the light absorption rate is not generated, and the measurement accuracy is lowered.

  The present invention solves the above-mentioned conventional problems, and maintains a proportional relationship between the energy of the photoacoustic wave and the light absorptivity generated even in a heat generating portion whose size is smaller than the pulse length of the photoacoustic wave, thereby achieving high accuracy. Another object of the present invention is to provide a spectroscopic measurement apparatus capable of measuring the light absorption characteristics in a specimen and measuring the component concentration with high accuracy.

  In order to solve the above-described conventional problems, a spectroscopic measurement device according to the present invention includes a light source that generates pulsed light that irradiates a specimen, an ultrasonic probe that receives ultrasonic pulses generated in the specimen, and an ultrasonic probe. Is a spectroscopic measurement apparatus including a signal processing unit that calculates the generation location and intensity of an ultrasonic pulse generated inside the specimen based on the signal received in step 1, and the light generated by the light source or another light source. Before and after irradiating the specimen, the specimen is irradiated with pulsed light.

  Further, the specimen may be irradiated with a plurality of pulse lights having different waveforms.

  The light source may irradiate the specimen with both short pulse light and CW light having a pulse width on the order of nanoseconds at different timings.

  Further, the CW light and the pulsed light that irradiate the specimen may be generated from one light source.

  The spectroscopic measurement apparatus may further include means for absorbing part of the thermal energy of the specimen and reducing the temperature of the specimen.

  Further, the means for absorbing a part of the thermal energy of the specimen and lowering the temperature of the specimen includes a heat absorption section in contact with at least the specimen, and the heat absorption section transmits light generated by the light source. The specimen may be made of a material, and the specimen may be irradiated with light generated by the light source through the heat absorption unit.

  The spectroscopic measurement apparatus may further include means for pressing the specimen.

  The specimen may be irradiated with a plurality of lights having different wavelengths.

  The specimen may be a living body, and light having a wavelength of 1100 nm or more and 1300 nm or less may be irradiated to the living body, and the fat concentration at a desired location in the living body may be measured.

  The spectroscopic measurement apparatus may further include a radiation thermometer that measures a change in the surface temperature of the specimen.

  The spectroscopic measurement apparatus further includes means for heating or cooling the specimen to a temperature distribution different from the heating by the light, the specimen contacting section having at least a specimen contact section in contact with the specimen, wherein the specimen contact section is the light source. It is comprised with the material which permeate | transmits the light produced | generated by (4), The light produced | generated by the said light source may be irradiated to the said specimen through the said specimen contact part.

  Further, photoacoustic waves in the specimen may be measured at least during the light irradiation from the light source to the specimen and after the light irradiation.

  Further, after the light irradiation is completed, pulse light may be irradiated to the same portion of the specimen a plurality of times, and a photoacoustic wave generated in the body may be received.

  In the spectroscopic measurement device of the present invention, the energy of the generated photoacoustic wave changes due to the temperature change before and after the sample is irradiated with light, and the rate of change is proportional to the temperature change regardless of the size of the heat generation point. It is possible to provide a spectroscopic measurement device capable of measuring the distribution of the light absorption rate in the specimen with high accuracy and measuring the concentration distribution of a desired component with higher accuracy even when the heat generation location is smaller. .

The figure which shows schematic structure of the spectroscopic measurement apparatus shown in Embodiment 1. The figure which shows schematic structure of the conventional spectroscopic measuring device The figure which shows schematic structure of another conventional spectroscopic measuring device. The figure which shows schematic structure of another spectroscopy measuring apparatus shown in Embodiment 1. FIG. The figure which shows schematic structure of another spectroscopy measuring apparatus shown in Embodiment 1. FIG. The figure which shows schematic structure of another spectroscopy measuring apparatus shown in Embodiment 1. FIG. The figure which shows schematic structure of the light irradiation apparatus shown in Embodiment 2. The figure which shows schematic structure of another light irradiation apparatus shown in Embodiment 2. FIG. The figure which shows schematic structure of another spectroscopy measuring apparatus shown in Embodiment 1. FIG. The figure which shows schematic structure of the spectroscopic measurement apparatus shown in Embodiment 3. The figure which shows schematic structure of the spectroscopic measurement apparatus shown in Embodiment 4. The figure which shows schematic structure of the spectroscopic measurement apparatus shown in Embodiment 5. Diagram showing the temperature change of the specimen of a conventional spectroscopic measurement device The figure which shows the temperature change of the test substance of the spectroscopic measurement apparatus shown in Embodiment 5. Another diagram showing the temperature change of the specimen of the spectroscopic measurement apparatus shown in the fifth embodiment The figure which shows schematic structure of the component concentration distribution measuring apparatus shown in Embodiment 6.

  In a spectroscopic measurement device that heats the specimen with light of a specific wavelength and measures the difference in temperature rise due to the difference in the light absorption characteristics of each part as a change in sound velocity or photoacoustic wave energy, and evaluates the light absorption rate in the specimen. Since the relationship with the physical quantity (the amount of change in sound speed and the energy of the photoacoustic wave) varies depending on the state of the specimen, the measurement accuracy decreases.

  For example, although the light absorption characteristics (light absorption rate) and the heat generation amount of each part are proportional, the light absorption rate and the temperature rise amount are not necessarily uniquely determined. Since the heat capacity and the thermal conductivity are different depending on the structure and material composition of the specimen, the amount of heat transferred from the portion with high heat generation to the portion with low heat generation is different. That is, even if there is a part where the amount of heat generation is particularly large (the light absorption rate is high), if the heat transfer to the surroundings is large, the temperature difference from the surroundings is reduced.

  In addition, since the rate of change in the temperature of sound varies depending on the material composition of the specimen, in a spectroscopic measurement device that calculates the light absorption rate from the amount of change in sound speed as in Patent Document 1, the measurement accuracy is reduced.

  Furthermore, since the volume expansion coefficient, the heat capacity, and the sound speed differ depending on the material composition of the specimen, the relationship between the photoacoustic wave energy and the temperature rise amount cannot be uniquely determined.

  In the present invention, a highly accurate spectroscopic measurement apparatus is realized by the following method.

  -Measure high accuracy by providing a function for obtaining at least one of the above-mentioned relationships that cause a decrease in measurement accuracy.

  -Measure high accuracy by suppressing at least one of the above-mentioned relationships that cause a decrease in measurement accuracy (variation between samples, position variation, etc.).

  Embodiments of the present invention will be described below with reference to the drawings. In addition, the same reference numerals are used for the same components, and the description may be omitted.

(Embodiment 1)
In this embodiment, a living body such as a human body or an animal is used as a specimen, and the relationship between the light absorption rate and the temperature rise is suppressed by suppressing the movement of heat due to blood flow, and the light absorption rate in the specimen is more accurately determined. A spectroscopic measurement apparatus for obtaining the distribution will be described.

  FIG. 1 is a schematic diagram showing an example of a spectroscopic measurement apparatus according to Embodiment 1 of the present invention.

  The spectroscopic measurement apparatus in FIG. 1 includes at least a light source 101, an ultrasonic measurement apparatus 102, and a specimen contact unit 103.

  Below, an example of operation | movement of the spectroscopic measurement apparatus of this Embodiment is demonstrated.

(1) Start of living body cooling process: The temperature of the living body 104 is lowered by bringing the specimen contact portion 103 in a state of lower temperature than the living body into contact with the living body 104.
(2) Ultrasonic sound velocity measurement process (first time)

  (3) Selective light heating process started

  (4) Ultrasonic sound velocity measurement process (second time)

  (5) Sound velocity change calculation process

  In the present embodiment, first, a living body that is a specimen is cooled to suppress heat transfer due to blood flow.

  After the living body has been sufficiently cooled, the results of measuring the sound velocity in the specimen with and without selective heating light are compared, and the light absorption rate of each part is obtained from the change in sound velocity due to light irradiation. Distribution measurement is possible.

  Further, here, as in the conventional example, the biological measurement is performed by irradiating the living body 104 with the selective heating light 105 having a wavelength of about 1200 nm (1100 nm or more and 1300 nm or less), and measuring the fat degree (fat concentration) of the intravascular plaque 106. The apparatus will be described.

  Adipose tissue has a high light absorptance at a wavelength of about 1200 nm, and a portion with a high fat concentration in the living body 104 absorbs a large amount and shows a larger temperature rise than a portion with a low fat concentration. Since the propagation speed of the sound wave including the ultrasonic wave changes according to the temperature change of the medium, as shown above, the ultrasonic pulse received by the ultrasonic probe 102a when the selective heating light is irradiated and when not irradiated. By comparing the signals, the light absorption rate can be obtained from the change in sound speed inside the living body 104, and the fat concentration can be obtained.

  However, in the conventional spectroscopic measurement apparatus as shown in FIG. 1, heat generated in the intravascular plaque 106 having a particularly high light absorption rate of the selective heating light 105 is propagated to the surroundings by the blood flow. For this reason, the temperature rise amount (sound speed change amount) of the plaque 106 changes depending on the blood flow, and it is difficult to obtain an accurate light absorption rate.

  However, in this embodiment, by cooling the living body, the blood flow rate is suppressed, and the propagation of heat due to the blood flow is suppressed, thereby suppressing the variation in the relationship (proportional coefficient) between the light absorption rate and the temperature increase amount. Is possible.

  That is, it is possible to provide a spectroscopic measurement apparatus that can measure the light absorption rate distribution with higher accuracy than the conventional configuration and can measure the concentration of the component with higher accuracy.

  Hereinafter, the configuration of the spectroscopic measurement apparatus according to the present embodiment will be described in more detail.

  First, an optical fiber is used as means for guiding laser light emitted from the laser light source 101a to a living body, but an optical system using a lens or a mirror may be used. However, it is desirable to use an optical fiber because the light guide means becomes smaller and lighter.

  In addition to the laser light source, the light source 101 can be a light source that generates light of a specific wavelength, such as an LED or a lamp with a wavelength filter. However, when an optical fiber is used as the light guide, It is desirable to use a laser light source. A spectroscopic measurement apparatus with lower power consumption can be realized.

  In addition, it is desirable to use a multimode fiber as the optical fiber, and it is desirable that the optical fiber includes at least one winding portion 101c. As a result, more uniform light irradiation is possible, so that a spectroscopic measurement apparatus capable of measuring a component distribution in a living body with high accuracy can be obtained.

  Further, the specimen contact portion 103 is desirably a material having high thermal conductivity such as metal such as iron, aluminum, copper, diamond, graphite, and the temperature of the living body 104 can be lowered more quickly. For this reason, since it becomes possible to improve a measurement speed as a spectroscopic measurement apparatus, it is desirable.

  In addition, in order to increase the contact area with the living body 104, the specimen contact unit 103 preferably has an uneven shape that matches the living body, and further enables high-speed measurement.

  The sample contact unit 103 includes a heat exchanging unit 107 such as a Peltier or a compressor, a driving power source 108 that drives the heat exchanging unit 107, and a heat dissipating unit 109 that dissipates heat absorbed from the sample contact unit 103 by the heat exchanging unit 107. It is good also as a structure provided.

  In the case of the configuration using the specimen contact unit 103 having a large heat capacity without the heat exchanging unit 107, a greater cooling effect can be obtained without providing a member such as a heat exchanging unit, a driving power source, and a heat radiating unit, so that it is less expensive. This configuration is desirable in that a spectroscopic measurement apparatus can be realized.

  On the other hand, the heat exchange unit 107 driven by the drive power supply 108 moves the heat of the specimen contact unit 103 to the heat radiating unit 109 that combines fins, fans, and fins, so that it is lighter and more accurate. It is desirable because it becomes possible to realize.

  In addition, it is desirable to install a temperature measuring means 110 such as a thermistor in the specimen contact portion, and to control the drive power supply 108 using information on the temperature of the specimen contact portion measured by the temperature measurement means 110, so that the living body 104 is more optimal. And since it becomes possible to suppress that the temperature of the biological body 104 varies for every measurement, measurement with higher reproducibility becomes possible.

  In addition, as shown in FIG. 4, the configuration may be such that the specimen heating unit 401 having a high light transmittance is used to irradiate the living body 104 with the selective heating light 105 through the specimen contact unit 401.

  In the spectroscopic measurement apparatus of FIG. 1, since the specimen contact portion 103 is not required to have high light transmittance, it is possible to select an inexpensive material with high thermal conductivity such as copper or aluminum, and an inexpensive apparatus can be selected. The configuration was desirable in that it was possible.

  On the other hand, in the spectroscopic measurement apparatus shown in FIG. 4, in order to remove the heat of the living body from the irradiation surface of the selective heating light 105, which is a portion where the light intensity is high and the temperature is likely to increase and the blood flow is likely to increase, It can be reduced. For this reason, it becomes possible to uniformly reduce the blood flow volume in the entire region from the vicinity of the light irradiation surface to the deep part of the living body. That is, it is possible to measure the component concentration in a wider range and with high accuracy.

  In the configuration of FIG. 4, the specimen contact portion 401 is preferably made of a material such as quartz or diamond that has high thermal resistance and high transmittance for the selective heating light 105. In particular, diamond has a high thermal conductivity and is a desirable material for the specimen contact portion in the present embodiment.

  Further, in the configuration of FIG. 4, similarly to the configuration of FIG. 1, measurement with high reproducibility is possible by including the temperature measurement unit 110.

  Moreover, when cooling from the selective heating light irradiation surface, a transparent temperature measuring means is more desirable, and it is more desirable to use a radiation thermometer. As a result, the surface temperature of the living body can be measured regardless of the contact between the living body and the specimen contact portion (contact thermal resistance), and the response speed is also fast. Become.

  Since it is possible to irradiate the living body with the selective heating light 105 more uniformly, it is possible to measure the distribution of the component concentration with higher accuracy.

  In addition, as shown in FIG. 5, the configuration in which the specimen contact portion 501 is inserted between the ultrasonic probe 102 a and the living body 104 can cool the inside of the living body 104 more uniformly than the configuration of FIG. 4. Therefore, it is more desirable to cool the entire area more uniformly, so that a spectroscopic measurement apparatus capable of high-precision measurement is obtained.

  Further, in the configuration of FIG. 5 as well, in the same way as the configuration of FIG. 1, measurement with high reproducibility is possible by providing temperature measurement means such as a thermistor.

  However, in the configuration of FIG. 5, it is more desirable to install the sonic heat change member 502 whose sound speed changes due to a temperature change in an area through which an ultrasonic pulse radiated from the ultrasonic probe 102a passes.

  As a result, the temperature of the specimen contact portion 501 can be obtained simply by measuring the time during which the ultrasonic pulse passes through the sonic heat change member 502 with the ultrasonic measurement device 102.

  As an example of the sonic heat change member 502, a material having a large change in sound speed due to a temperature change is desirable, and an inexpensive and lightweight ultrasonic probe can be obtained by using a material such as rubber or resin.

  In addition, it is desirable to use a material having a glass transition point close to room temperature because the change in sound velocity due to a temperature change is large and more accurate measurement is possible.

However, when the sonic heat change member is provided between the living body and the ultrasonic probe, it is desirable that the material has an acoustic impedance different from that of the living body or the ultrasonic probe, in particular, 1.4 × 10 ⁶ kg / m ² s or less, Alternatively, the material is preferably 1.6 × 10 ⁶ kg / m ² s or more.

  As a result, a larger ultrasonic pulse is reflected at the boundary surface between the sonic heat change member and the living body and the boundary surface between the ultrasonic probe and the temperature can be measured with high accuracy.

Moreover, it is desirable to suppress reflection to a certain extent, and the acoustic impedance of the sonic heat change member is 1.0 to 1.4 × 10 ⁶ kg / m ² s, or 1.6 to 2.25 × 10 ⁶ kg / m ² s is more desirable, and a more sensitive ultrasonic probe is possible.

  For example, polyethylene or a mixture of silica and acrylic can be used as the sonic heat change material.

  This is desirable because an inexpensive temperature measurement means can be realized and an inexpensive spectroscopic measurement device can be provided, compared to the case where a thermistor or a radiation thermometer is used.

  More desirably, as shown in FIG. 6, it is desirable to provide an optical fiber including a fiber grating 601 in a region where the selective heating light 105 is irradiated.

  The fiber grating 601 can be designed so that the reflectance of light of an arbitrary wavelength is high depending on the grating period. Further, since the refractive index of the grating portion changes as the temperature of the fiber grating 601 changes, the wavelength of the reflected light changes.

  That is, it can be used as a temperature measuring means by monitoring the wavelength of the reflected light.

  Further, by using the fiber grating 601 as the temperature measuring means, it is possible to install the temperature measuring means in a portion through which light and ultrasonic waves pass, so that the temperature can be adjusted with higher accuracy. That is, it is possible to further reduce the occurrence of measurement variations due to temperature variations for each measurement.

  4 to 6, the heat exchange unit 107 driven by the driving power source 108 moves the heat of the specimen contact unit to the heat radiating unit 109 that combines the fins, the fan, and the fins. This is desirable because it makes it possible to implement the device.

  In addition, a configuration including a heat exchanging unit made of Peltier and a heat dissipating unit including only fins is desirable, and a spectroscopic measurement apparatus that can perform measurement with less vibration and high accuracy can be realized.

  Furthermore, it is desirable to install a temperature measurement means such as a thermistor in the specimen contact portion, and to control the drive power supply 108 using information related to the temperature of the specimen contact portion measured by the temperature measurement means. And since it becomes possible to suppress that the temperature of the biological body 104 varies for every measurement, measurement with higher reproducibility becomes possible.

  Further, in the spectroscopic measurement apparatus of the present embodiment, it is more desirable to include a means for monitoring the drive current of the laser light source 101a and the output of the selective heating light 105, and after starting the light heating to the living body, the heat exchange unit It is desirable to increase the drive current to 107 and increase the cooling effect. As a result, it is possible to irradiate the living body 104 with the selective heating light 105 having a larger output, and thus it is possible to realize a more accurate spectroscopic measurement apparatus.

  Moreover, it is desirable that the temperature of the specimen contact portion at the time of measuring the internal structure of the living body by the ultrasonic measurement device is −4 ° C. or higher, which can prevent skin frostbite.

  Moreover, it is more desirable that the temperature is 15 ° C. or higher, and it is possible to supply necessary oxygen to the cells. Therefore, even if measurement is performed for a long time, it is difficult to feel fatigue due to a decrease in body temperature.

  In addition, the temperature is preferably 25 ° C. or lower, and the living body can be cooled without being affected by individual differences in body temperature.

  In addition, as shown in FIG. 4, when the selective heating light 105 is irradiated through the specimen contact portion 401, it is desirable that the temperature is room temperature or higher. It becomes possible to prevent dew condensation from occurring in the specimen contact portion, and it is possible to suppress non-uniformity of irradiation of the selective heating light 105 to the living body 104 due to dew condensation. That is, light irradiation with high reproducibility is possible, and variation in accuracy for each measurement can be suppressed.

  Further, as shown in FIG. 4, when the selective heating light 105 is irradiated through the specimen contact portion 401, 30 ° C. or lower is desirable. Since it is possible to suppress the nonuniformity of irradiation of the selective heating light 105 to the living body 104 due to sweating on the skin surface, it becomes possible to perform light irradiation with high reproducibility and to suppress variation in accuracy for each measurement. Become.

  In addition, in order to prevent the influence of individual differences in sweating temperature due to race, sex, humidity, etc., the temperature of the specimen contact unit 401 is measured so as not to exceed the temperature after measuring the sweating temperature of a living body as a subject. Is most desirable.

  In addition, an ultrasonic probe using a transparent piezoelectric material can irradiate a living body with both light and ultrasonic waves from the same location. By using an ultrasonic probe using a bulk type transparent piezoelectric material such as crystal, lithium niobate, and lithium tantalate, which are transparent piezoelectric materials, light irradiation at the contact surface between the ultrasonic probe and the living body can be performed at low cost. It becomes possible. This is desirable because the light intensity in the vicinity of the ultrasonic probe of the living body becomes more uniform and strong, and more accurate and sensitive measurement is possible.

  In addition, it is desirable to use a transparent piezoelectric material using a single crystal thin film technology such as ZnO or AIN because a smaller spectroscopic measurement becomes possible.

  In addition, it is more desirable to use an ultrasonic probe that applies a voltage to a piezoelectric material using a transparent electrode such as ITO having excellent light transmission characteristics, and it is possible to measure a component concentration with higher sensitivity and accuracy.

  Further, it is more desirable to use a transparent electrode made of zinc oxide or magnesium, and it is possible to measure the component concentration with low cost, high sensitivity and high accuracy.

  Further, as shown in FIG. 9, water 902 is put into a water tank 901, and the living body 104 placed therein is irradiated with the selective heating light 105 and ultrasonic waves from the ultrasonic probe 102 a, and the inside of the living body 104. It is good also as a spectroscopic measurement apparatus which measures again the ultrasonic wave reflected in by the ultrasonic probe 102a.

  In the configuration of FIG. 9, the living body 104 can be cooled by adjusting the temperature of the water 902.

  Moreover, in order to adjust the temperature of the water 902, it is desirable to provide a temperature adjustment mechanism (107 to 110) as shown in FIG. It becomes possible to adjust to a more free temperature, and it becomes possible to suppress variation in measurement.

  In addition, the temperature of the water 902 is more preferably 15 ° C. or higher, and a blood flow rate capable of supplying oxygen necessary for cells in the living body is maintained. It becomes difficult to feel tiredness due to a decrease in body temperature.

  Further, the temperature of the water 902 is preferably 25 ° C. or less, and the living body can be cooled without being affected by the individual difference in body temperature.

  Moreover, although water was used here, it does not necessarily need to be water. However, it is desirable that the liquid has a relatively low viscosity, and it is possible to cool the living body effectively by the movement of heat by convection, so that it is possible to measure the component concentration with high accuracy.

  In addition to water, for example, ethanol may be used. Since ethanol has a high bactericidal effect, it is not necessary to mix a preservative, and furthermore, since the heat released into the atmosphere by the heat of vaporization is large, it can be adjusted to a low temperature with less energy.

  Further, when water is used, an inexpensive spectroscopic measurement device can be realized. Further, water is desirable because it has a refractive index and an acoustic impedance that are comparable to those of a living body, and can irradiate both light and ultrasonic waves with high efficiency. It is also possible to perform measurement without directly pressing the ultrasonic probe 102a against the living body, and the shape of the living body is not deformed by pressing the ultrasonic probe, and even higher in comparison with past measurement results. It is desirable to be able to compare with accuracy.

  However, when water is used, it is desirable to use water mixed with an antiseptic, and component concentration can be measured with high reproducibility.

  Moreover, it is more desirable to use water mixed with a surfactant, and it is possible to suppress the generation of bubbles on the surface of the living body and to measure the component concentration with higher accuracy.

  In addition, when the in-vivo component concentration measurement is performed with the spectroscopic measurement apparatus of the present embodiment, it is more preferable to perform the measurement under the following conditions.

  For example, ingestion of nicotine can further reduce blood flow, so it is more desirable to perform spectroscopic measurement in the state of ingestion of nicotine, thereby enabling more accurate measurement. Become.

  More preferably, when nicotine is ingested by smoking or passive smoking, it is desirable to perform spectroscopic measurement using the spectroscopic measurement device of the present invention within one and a half hours after ingesting nicotine. Since measurement is possible in a state where the flow rate is reduced, highly accurate component concentration measurement is possible.

  In addition, by taking nicotine using a nicotine patch, it is possible to lower blood flow more locally, so it is possible to measure component concentrations with high accuracy with a smaller amount of nicotine, so minors It becomes a more desirable method in the application to young people such as.

  Moreover, you may use the method of reducing a blood flow rate by an anti-inflammatory analgesic, electrical stimulation, etc.

  Blood flow reduction due to smoking or passive smoking is a cheaper means of realization, but it is difficult to adjust the blood flow reduction, and it is possible to measure the concentration of components with higher accuracy by using methods using analgesics and electrical stimulation. Therefore, it is desirable, and more accurate measurement is possible.

  Also, since caffeine has a function to increase blood flow, it is more desirable to perform spectroscopic measurement within 15 minutes after ingestion of caffeine, or 30 minutes or more after ingestion of caffeine. Accurate component concentration measurement is possible.

  In addition, it is desirable to perform component concentration measurement in a state in which the portion where the component concentration is measured and the peripheral portion are pressurized. Since the blood flow can be suppressed by pressurization, the component concentration can be measured with high accuracy.

  As described above, in the present embodiment, the spectroscopic measurement apparatus that obtains the light absorptance from the amount of change in the temperature of sound speed has been described. However, the light absorptance is obtained from the photoacoustic wave energy as shown in FIG. Similarly, in the spectroscopic measurement apparatus, by measuring the component concentration in a state where the living body as the specimen is cooled, the movement of heat due to the blood flow can be suppressed, and the component concentration can be measured with higher accuracy.

  In addition, by replacing the laser light source 101a of the spectroscopic measurement apparatus shown in FIG. 1 and FIGS. 4 to 6 with a pulse laser light source 301a, a spectroscopic measurement apparatus for obtaining the light absorption rate from the photoacoustic wave energy is possible. The same effect can be obtained with this configuration.

  Although not shown, in a spectroscopic measurement device having a light source capable of driving both pulsed light and CW light and a spectroscopic measurement device having two light sources (pulse light source and CW light source), the temperature rises due to light heating. It is desirable because a spectroscopic measurement apparatus capable of measuring the amount by both sound velocity change and photoacoustic wave energy becomes possible, and more accurate component concentration measurement is possible.

  Further, it is more desirable to use a pulsed light source that can adjust the light intensity of the pulsed light, and it is also possible to obtain a non-linear light absorption characteristic, so that the component concentration can be measured with higher accuracy.

  In the present embodiment, an example of a spectroscopic measurement apparatus that measures the concentration of fat has been described. However, it goes without saying that the present invention can be applied to all component concentration measurements to which the light heating phenomenon is applied. Yes. For example, a spectroscopic measurement device that measures the oxygen saturation of hemoglobin (ratio of oxidized hemoglobin concentration to deoxygenated hemoglobin concentration) using light having a wavelength of 650 nm to 800 nm is also possible, and determination of cancer and benign tumor is possible. It is also possible to apply to diagnosis of burn depth.

  In any case, such as when measuring fat concentration, when measuring hemoglobin concentration or oxygen saturation, etc., using a light source that generates light of multiple wavelengths, the absorption rate of light of multiple wavelengths It is desirable to obtain the component concentration, and the component concentration measurement can be performed.

  In addition, in the application of measuring hemoglobin oxygen saturation for cancer property diagnosis from photoacoustic wave energy, it is desirable that the pulse width of the pulsed light (full width at half maximum of output) is 0.33 μs or less, which is useful for cancer property diagnosis. The required resolution can be obtained.

  Moreover, in the application which measures the fat degree of an intravascular plaque from photoacoustic wave energy, it is desirable that the pulse width of pulsed light is less than 0.07 microseconds, and the resolution required for the diagnosis of the characteristic of an intravascular plaque is obtained.

  In addition, it is desirable that the pulse width is 0.2 ns or more, and it is possible to generate an ultrasonic wave having a higher biological transmittance, so that it is possible to measure a component concentration in a deeper part.

  Further, the present embodiment may be applied to a spectroscopic measurement device intended for other than a living body.

  For example, the present invention can be applied to an example of measuring foreign matters mixed in food.

  Further, in the present embodiment, the spectroscopic measurement apparatus that measures the heating by light with ultrasonic waves has been described, but the spectroscopic measurement apparatus of the present invention does not necessarily need to be a spectroscopic measurement apparatus using ultrasonic waves.

  For example, the same effect can be obtained with a similar configuration in a spectroscopic measurement apparatus that measures temperature change by light heating using a thermocouple or a radiation thermometer.

  The use of a thermocouple is desirable because it enables more inexpensive component concentration measurement.

  In addition, it is desirable to use a radiation thermometer because component concentration can be measured in a non-contact manner.

  In addition, as shown in the present embodiment, a spectroscopic measurement device that uses a change in sound velocity due to a temperature rise measures heating by light using ultrasound, which is an inexpensive means that is excellent in straightness in a living body. Therefore, it is desirable because it enables inexpensive component concentration (distribution) measurement with excellent position resolution even inside the living body.

  In addition, the spectroscopic measurement device that measures the expansion due to temperature rise as photoacoustic wave energy is a spectroscopic measurement device that can detect the difference in light absorption rate (difference in expansion rate) more significantly, and is inexpensive and has high contrast. This is desirable because it enables accurate component concentration (distribution) measurement.

  In the present embodiment, the configuration in which the sample contact portion is provided between the ultrasound probe and the sample (living body) is shown in FIGS. 5 and 6, but the contact surface itself of the ultrasound probe with the living body is the sample. It is good also as a structure which absorbs the heat | fever of a biological body as a contact part.

(Embodiment 2)
As described in the first embodiment, the present invention is effective in a spectroscopic measurement apparatus using a light heating phenomenon, but also exhibits an effect in another apparatus using light heating.

  Here, an example of a light irradiation device (hyperthermia) for the purpose of cancer treatment that heats and kills cancer tissue will be described.

  First, hyperthermia will be described.

  It has been found that cancer tissue is weaker than heat compared to normal tissue, and can be killed in a few minutes by heating to 46 ° C., for example. However, at 46 ° C., part of the normal tissue is also killed.

  For this reason, it is more desirable to selectively heat only the cancer tissue. For example, if the normal tissue can be suppressed to 41 ° C. and only the cancer tissue can be heated to 46 ° C., only the cancer tissue can be killed without damaging the normal tissue.

  Below, the light irradiation apparatus which raises the temperature of only cancer tissue more selectively is demonstrated.

  FIG. 7 is a schematic view showing an example of a light irradiation apparatus according to Embodiment 2 of the present invention.

  The light irradiation apparatus of FIG. 7 includes at least a light source 101 and a specimen contact unit 103, as in the spectroscopic measurement apparatus of the first embodiment. As in the first embodiment, the specimen contact unit 103 absorbs the heat of the living body 703 and lowers the temperature of the living body 703 to irradiate the living body 703 with the selective heating light 702 generated by the light source 101. . Here, in the present embodiment, the living body 703 is a part including a cancer tissue 701 such as a breast or a prostate.

  As the light source 101, a light source that generates light whose light absorption rate of cancer tissue is higher than that of normal tissue is used. For example, a laser light source or an LED that generates selective heating light 702 from 600 nm to 800 nm is used.

  As a result, the selective heating light 702 can selectively heat the cancer tissue 701 in the living body 703.

  Usually, since a lot of heat is carried from the cancer tissue 701 by the blood flow flowing toward the periphery thereof, the temperature of the periphery also rises. However, the light irradiation apparatus using the light irradiation apparatus of the present invention has an effect of suppressing blood flow by reducing the temperature of the living body, and can increase the temperature of only the cancer tissue 701 more selectively. It becomes. As a result, when the cancer tissue 701 is killed, the normal tissue that has been killed can be reduced.

  FIG. 8 is a schematic configuration diagram showing an example of another light irradiation apparatus according to Embodiment 2 of the present invention.

  The light irradiation apparatus in FIG. 8 is also a light irradiation apparatus for cancer treatment similar to the light irradiation apparatus in FIG.

  The light irradiation apparatus in FIG. 8 includes at least a light source 101 and a specimen contact unit 401. The specimen contact unit 401 irradiates the living body 703 with the selective heating light 702 generated by the light source 101 while absorbing the heat of the living body 703 and lowering the temperature of the living body 703.

  Here, unlike FIG. 7, in the light irradiation apparatus of FIG. 8, the selective heating light 702 is irradiated to the living body 703 through the specimen contact portion 401. Therefore, in this configuration, it is desirable that the specimen contact unit 401 is configured by a member that transmits the selective heating light 702. For example, by using a material having a high light transmittance such as an acrylic resin or a quartz substrate as the specimen contact portion 401, the living body 703 can be efficiently irradiated with the selective heating light 702. It becomes a light irradiator with high power consumption.

  In addition, since the specimen contact portion 401 is made of a transparent material having a high thermal conductivity, such as diamond, the cooling effect on the living body 703 can be further enhanced. Can be reduced.

  Similarly to FIG. 7, it is desirable that the specimen contact unit 401 includes the heat exchanging unit 107, the drive power supply 108, and the heat radiating unit 109, which can further reduce normal tissues to be killed.

  In the light irradiation apparatus of FIG. 7, since the specimen contact portion 401 is not required to have high light transmittance, it is possible to select an inexpensive material having high thermal conductivity such as aluminum or copper, and thus inexpensive light irradiation. This configuration is desirable in that the apparatus can be used.

  On the other hand, in the light irradiation apparatus of FIG. 8, since the heat of the living body is taken away from the light irradiation surface where the light intensity is high and the temperature easily rises in the living body, the temperature in the living body can be made more uniform. For this reason, it is possible to reduce the blood flow volume in the entire region from the vicinity of the light irradiation surface to the deep part of the living body, and this is particularly desirable when killing cancer tissue near the light irradiation surface. In addition, since the surface to be irradiated with light and the surface to be cooled by the specimen contact unit 401 are in the same direction, it can be applied to a thick (large) living body part, which is desirable.

  Needless to say, the light irradiation device of the present embodiment is more selectively configured by the same configuration as that of the spectroscopic measurement device of the first embodiment for controlling the blood flow in the living body. This is desirable because it allows cancer tissue to be killed.

(Embodiment 3)
In the present embodiment, in a spectroscopic measurement apparatus that heats a specimen with light of a specific wavelength and measures a difference in temperature increase due to a difference in light absorption characteristics of each part as a change in sound velocity, depending on the material composition and composition ratio of each part, It aims at suppressing the fall of the measurement accuracy by the proportionality coefficient between temperature change and sound speed change differing.

  For example, the sound speed and the proportionality coefficient between the temperature change and the sound speed change (sound speed temperature change coefficient) vary depending on the substance.

  The speed of sound propagating in water is 1483 m / s at 24 ° C., 1530 m / s at 37 ° C., and the sound speed temperature change coefficient is 3.6 m / s / ° C. On the other hand, for example, the speed of sound propagating in the adipose tissue is 1476 m / s at 24 ° C., 1412 m / s at 37 ° C., and the sound speed temperature change coefficient is −4.9 m / s / ° C.

  Also, for various organs in the living body, the sound velocity and the sound velocity temperature change coefficient differ depending on the concentration of moisture, fat, and the like.

  Therefore, for example, for the purpose of measuring the fat concentration distribution in the living body, a configuration in which the living body is irradiated with light having a wavelength of about 1200 nm as in the first embodiment, and the change in the sound speed of each part is measured by the ultrasonic probe. Even if the temperature change is proportional to the fat concentration distribution, the sound speed change is not proportional to the temperature change. Depending on the composition ratio of components other than fat, the sonic temperature change coefficient is affected differently depending on the location.

  For this reason, in this embodiment, it is possible to obtain the light absorption rate with higher accuracy by obtaining the sonic temperature change coefficient in the specimen, and to measure the desired component concentration distribution with higher accuracy. A possible spectroscopic measurement device will be described.

  FIG. 10 shows a schematic configuration of the spectroscopic measurement apparatus of the present embodiment.

  The spectroscopic measurement apparatus in FIG. 10 includes at least a light source 101, an ultrasonic measurement apparatus 102, a specimen contact unit 1001, a heat conversion unit 107, and a drive power supply 108.

  However, the spectroscopic measurement apparatus of the present embodiment uses a measurement method different from that of the first embodiment.

  The spectroscopic measurement apparatus according to the present embodiment performs measurement in the following order in a state where the ultrasonic probe 102a and the specimen contact unit 1001 are in contact with the living body 104 in advance.

  (1) Ultrasonic sound velocity measurement process (first time)

  (2) Uniform heating / cooling start: Using the drive power supply 108, heating (or cooling) of the living body 104 by the heat conversion unit 107 is started.

  (3) Ultrasonic velocity measurement process (second time)

  (4) Selective light heating start

  (5) Ultrasonic sound velocity measurement process (third time)

  (6) Sound velocity change calculation (first time): The ultrasonic pulse waveforms (electrical signals) reflected from the living body 104 obtained in (1) and (3) are compared, and the living body 104 before and after the step (2). The amount of change in sound velocity of each part is obtained.

  (7) Sound velocity change calculation (second time): The ultrasonic pulse waveforms (electrical signals) reflected from the living body 104 obtained in (3) and (5) are compared, and the living body 104 before and after the step (2). The amount of change in sound velocity of each part is obtained.

  (8) Temperature rise amount calculation: The sound velocity temperature change coefficient at each position in the living body 104 is obtained from the result of (6), and the temperature at each position in the living body 104 is calculated from the result of (7) and the sound velocity temperature change coefficient. Find the amount of increase.

  In the present embodiment, as described above, ultrasonic sound velocity measurement is performed at least three times.

  First, as shown in (1) to (3) and (6), when the living body 104 is heated and not heated (or cooled and not) using the specimen contact unit 1001, the drive power supply 108, and the heat conversion unit 107. The ultrasonic pulse signals reflected from the living body 104 during cooling are compared. Since the temperature change of the living body 104 using the heating (cooling) method causes a temperature change that is not related to the material composition or concentration of each part in the living body 104, the temperature of each part of the living body 104 is uniformly heated (cooled). It becomes possible.

  That is, ultrasonic sound velocity measurement during uniform non-heating (cooling) and non-selective heating (first time) and ultrasonic sound velocity measurement during uniform heating (cooling) and non-selective heating (two) The sound velocity temperature change coefficient is obtained by comparing the sound velocity of each part of the second).

  Next, as shown in (3) to (5) and (7), ultrasonic sound velocity measurement (second time) and uniform heating (cooling) at the time of uniform heating (cooling) and selective heating light irradiation. The ultrasonic pulse signals reflected from the inside of the living body 104 for ultrasonic sound velocity measurement (third time) when no selective heating light is irradiated are compared. Light of a specific wavelength is irradiated to generate a heat generation (temperature rise) distribution according to a desired material concentration, and a change in sound velocity due to a temperature change in each part is obtained.

  As described above, the spectroscopic measurement apparatus according to the present embodiment includes means (steps) for obtaining a sound speed temperature change coefficient, so that the temperature increase amount closer to the actual condition can be obtained from the sound speed change at the time of selective heating light irradiation / non-irradiation. Since the distribution can be calculated, the component concentration can be detected with higher accuracy.

  Here, it is desirable to provide a means for measuring the temperature of the living body 104, such as a temperature measuring means 110 such as a thermistor or a thermocouple, and the sound velocity change coefficient can be obtained with higher accuracy. It is possible to measure the concentration of components.

  In addition, the same effect can be obtained in the present embodiment by using an improved configuration such as the location where the temperature measuring means and the heating / cooling means are brought into contact with the living body and the respective constituent materials as shown in the first embodiment. It goes without saying that he plays.

  Also in this embodiment, a spectroscopic measurement apparatus that irradiates the living body 104 with the selective heating light 105 having a wavelength of about 1200 nm (1100 nm or more and 1300 nm or less) and measures the fat degree of the intravascular plaque 106 becomes possible.

  In addition, both uniform heating and uniform cooling have the effects of the present embodiment, but uniform cooling can also achieve the effects shown in the first embodiment by suppressing blood flow, so uniform cooling is performed. It is more desirable.

  Hereinafter, the configuration of the spectroscopic measurement apparatus according to the present embodiment will be described in more detail.

  As in the first embodiment, the optical fiber is used as means for guiding the laser light emitted from the laser light source 101a to the living body. However, an optical system using a lens or a mirror may be used. However, it is desirable to use an optical fiber because the light guide means becomes smaller and lighter.

  In addition to the laser light source, the light source 101 can be a light source that generates light of a specific wavelength, such as an LED or a lamp with a wavelength filter. However, when an optical fiber is used as the light guide, It is desirable to use a laser light source. A spectroscopic measurement apparatus with lower power consumption can be realized.

  In addition, it is desirable to use a multimode fiber as the optical fiber, and it is desirable that the optical fiber includes at least one winding portion 101c. As a result, more uniform light irradiation is possible, and therefore, a spectroscopic measurement apparatus capable of measuring the concentration of components in a living body with high accuracy can be obtained.

  Further, the specimen contact portion 1001 is desirably a material having high thermal conductivity such as metal such as iron, aluminum, copper, diamond, graphite, and the temperature of the living body 104 can be lowered more quickly. For this reason, since it becomes possible to improve a measurement speed as a spectroscopic measurement apparatus, it is desirable.

  Further, in order to increase the contact area with the living body 104, the specimen contact unit 1001 desirably has an uneven shape that matches the living body, and further enables high-speed measurement.

  In addition, as described with reference to FIG. 4 in Embodiment 1, a configuration in which the specimen 104 is irradiated with the selective heating light 105 through the specimen contact portion using a specimen contact portion having a high light transmittance may be used.

  Accordingly, since the heat of the living body is taken from the irradiation surface of the selective heating light 105, which is a portion where the light intensity is high and the temperature is likely to increase and the blood flow is likely to increase, the temperature in the living body can be reduced more uniformly. . For this reason, it becomes possible to uniformly reduce the blood flow volume in the entire region from the vicinity of the light irradiation surface to the deep part of the living body. That is, it is possible to measure the component concentration in a wider range and with high accuracy.

  However, in the spectroscopic measurement apparatus of FIG. 10, since the specimen contact portion 1001 is not required to have high light transmittance, it is possible to select an inexpensive and high thermal conductivity material such as copper or aluminum, which is inexpensive. This configuration is desirable in that the apparatus can be used.

  As the specimen contact portion having a high light transmittance, a material such as quartz or diamond having a high thermal resistance and a high transmittance of the selective heating light 105 is desirable. In particular, diamond has a high thermal conductivity and is a desirable material for the specimen contact portion in the present embodiment.

  Further, similarly to the configuration of FIG. 10, by providing the temperature measuring means, it becomes possible to perform measurement with higher reproducibility. Moreover, when cooling from the selective heating light irradiation surface, a transparent temperature measuring means is more desirable, and it is more desirable to use a radiation thermometer. As a result, the surface temperature of the living body can be measured regardless of the contact between the living body and the specimen contact portion (contact thermal resistance), and the response speed is also fast. Become.

  Since it is possible to irradiate the living body with the selective heating light 105 more uniformly, it is possible to measure the distribution of the component concentration with higher accuracy.

  Further, as shown in FIG. 5 in the first embodiment, the configuration in which the specimen contact portion is inserted between the ultrasonic probe 102a and the living body 104 further heats the inside of the living body 104 uniformly. Since it becomes possible to cool, it is further desirable because it becomes a spectroscopic measurement apparatus capable of measuring with higher accuracy.

  Similarly to the configuration of FIG. 10, it is desirable to provide temperature measurement means such as a thermistor because measurement with high reproducibility becomes possible.

  Further, as shown in FIG. 5 in the first embodiment, a sonic heat change member whose sound speed changes due to a temperature change is installed in an area through which an ultrasonic pulse emitted from the ultrasonic probe 102a passes. It is more desirable.

  Thus, the temperature of the specimen contact portion can be obtained only by measuring the time during which the ultrasonic pulse passes through the sonic heat change member by the ultrasonic measurement device 102.

  As an example of the sonic heat change member, as in the first embodiment, a material having a large change in sound speed due to a temperature change is desirable. By using a material such as rubber or resin, an inexpensive and lightweight ultrasonic probe is possible. This is desirable.

  In addition, it is desirable to use a material having a glass transition point close to room temperature because the change in sound velocity due to a temperature change is large and more accurate measurement is possible.

However, when the sonic heat change member is provided between the living body and the ultrasonic probe, it is desirable that the material has an acoustic impedance different from that of the living body or the ultrasonic probe, in particular, 1.4 × 10 ⁶ kg / m ² s or less, Alternatively, the material is preferably 1.6 × 10 ⁶ kg / m ² s or more.

  As a result, a larger ultrasonic pulse is reflected at the boundary surface between the sonic heat change member and the living body and the boundary surface between the ultrasonic probe and the temperature can be measured with high accuracy.

Moreover, it is desirable to suppress reflection to a certain extent, and the acoustic impedance of the sonic heat change member is 1.0 to 1.4 × 10 ⁶ kg / m ² s, or 1.6 to 2.25 × 10 ⁶ kg / m ² s is more desirable, and a more sensitive ultrasonic probe is possible.

  For example, polyethylene or a mixture of silica and acrylic can be used as the sonic heat change material.

  This is desirable because an inexpensive temperature measurement means can be realized and an inexpensive spectroscopic measurement device can be provided, compared to the case where a thermistor or a radiation thermometer is used.

  More desirably, as shown in FIG. 6 in the first embodiment, it is desirable to provide an optical fiber including a fiber grating in the region where the selective heating light is irradiated. By monitoring the wavelength of the reflected light, it can be used as a temperature measuring means. Further, by using the fiber grating as the temperature measuring means, it becomes possible to install the temperature measuring means in a portion through which light and ultrasonic waves pass, so that the temperature can be adjusted with higher accuracy. That is, it is possible to further reduce the occurrence of measurement variations due to temperature variations for each measurement.

  Moreover, it is desirable that the temperature of the specimen contact portion at the time of measuring the internal structure of the living body by the ultrasonic measurement device is −4 ° C. or higher, which can prevent skin frostbite.

  Moreover, it is more desirable that the temperature is 15 ° C. or higher, and it is possible to supply necessary oxygen to the cells. Therefore, even if measurement is performed for a long time, it is difficult to feel fatigue due to a decrease in body temperature.

  In addition, the temperature is preferably 25 ° C. or lower, and the living body can be cooled without being affected by individual differences in body temperature.

  Further, when the selective heating light is irradiated through the specimen contact portion, the temperature of the specimen contact portion is preferably set to room temperature or higher. It becomes possible to prevent dew condensation from occurring in the specimen contact portion, and it is possible to suppress non-uniformity of selective heating light irradiation to the living body due to dew condensation. That is, light irradiation with high reproducibility is possible, and variation in accuracy for each measurement can be suppressed. In this case, the temperature of the specimen contact portion is desirably 30 ° C. or lower. Since it is possible to suppress non-uniformity of selective heating light irradiation on the living body due to sweating on the skin surface, it is possible to perform light irradiation with high reproducibility, and it is possible to suppress variation in accuracy for each measurement.

  In order to prevent the influence of individual differences in sweating temperature due to race, gender, humidity, etc., after measuring the sweating temperature of the living body that is the subject, the temperature of the specimen contact part should not be exceeded. It is most desirable to adjust.

  In addition, an ultrasonic probe using a transparent piezoelectric material can irradiate a living body with both light and ultrasonic waves from the same location. By using an ultrasonic probe using a bulk type transparent piezoelectric material such as crystal, lithium niobate, and lithium tantalate, which are transparent piezoelectric materials, light irradiation at the contact surface between the ultrasonic probe and the living body can be performed at low cost. It becomes possible. This is desirable because the light intensity in the vicinity of the ultrasonic probe of the living body becomes more uniform and strong, and more accurate and sensitive measurement is possible.

  In addition, it is desirable to use a transparent piezoelectric material using a single crystal thin film technology such as ZnO or AIN because a smaller spectroscopic measurement becomes possible.

  In addition, it is more desirable to use an ultrasonic probe that applies a voltage to a piezoelectric material using a transparent electrode such as ITO having excellent light transmission characteristics, and it is possible to measure a component concentration with higher sensitivity and accuracy.

  Further, it is more desirable to use a transparent electrode made of zinc oxide or magnesium, and it is possible to measure the component concentration with low cost, high sensitivity and high accuracy.

  Further, as shown in FIG. 9 in the first embodiment, the living body placed in the temperature-controlled water in the water tank is irradiated with selective heating light, and an ultrasonic probe is used. It is desirable to transmit and receive sound wave pulses, it is possible to keep the entire living body at a more uniform temperature, it is possible to measure the sonic temperature change coefficient with higher accuracy, and more accurate component concentration measurement is possible Become.

  Further, the temperature of the water is more preferably 15 ° C. or more, and the blood flow rate capable of supplying oxygen necessary for cells in the living body is maintained. It becomes difficult to feel fatigue due to the decrease.

  Moreover, the temperature of water is desirably 25 ° C. or less, and the living body can be cooled without being affected by individual differences in body temperature.

  Moreover, although water was used here, it does not necessarily need to be water. However, it is desirable that the liquid has a relatively low viscosity, and it is possible to cool the living body effectively by the movement of heat by convection, so that it is possible to measure the component concentration with high accuracy.

  In addition to water, for example, ethanol may be used. Since ethanol has a high bactericidal effect, it is not necessary to mix preservatives.

  Further, when water is used, an inexpensive spectroscopic measurement device can be realized. Further, water is desirable because it has a refractive index and an acoustic impedance that are comparable to those of a living body, and can irradiate both light and ultrasonic waves with high efficiency. It is also possible to perform measurement without directly pressing the ultrasonic probe 102a against the living body, and the shape of the living body is not deformed by pressing the ultrasonic probe, and even higher in comparison with past measurement results. This is desirable because it enables comparison with accuracy.

  However, when water is used, it is desirable to use water mixed with an antiseptic, and component concentration can be measured with high reproducibility.

  Moreover, it is more desirable to use water mixed with a surfactant, and it is possible to suppress the generation of bubbles on the surface of the living body and to measure the component concentration with higher accuracy.

  In the present embodiment, an example of a spectroscopic measurement apparatus that measures the concentration of fat has been described. However, it goes without saying that the present invention can be applied to all component concentration measurements to which the light heating phenomenon is applied. Yes. For example, a spectroscopic measurement device that measures the oxygen saturation of hemoglobin (ratio of oxidized hemoglobin concentration to deoxygenated hemoglobin concentration) using light having a wavelength of 650 nm to 800 nm is also possible, and determination of cancer and benign tumor is possible. It is also possible to apply to diagnosis of burn depth.

  In any case, such as when measuring fat concentration, when measuring hemoglobin concentration or oxygen saturation, etc., using a light source that generates light of multiple wavelengths, the absorption rate of light of multiple wavelengths It is desirable to obtain the component concentration, and the component concentration measurement can be performed.

  Further, the present embodiment may be applied to a spectroscopic measurement device intended for other than a living body.

  For example, the present invention can be applied to examples such as measurement of foreign matters mixed in food and detection of concentration of components contained in gas.

  Further, in the present embodiment, the spectroscopic measurement apparatus that measures the heating by light with ultrasonic waves has been described, but the spectroscopic measurement apparatus of the present invention does not necessarily need to be a spectroscopic measurement apparatus using ultrasonic waves.

  For example, even in a spectroscopic measurement apparatus that measures a temperature change due to light heating using a radiation thermometer, an effect of suppressing measurement errors due to a difference in the radiation spectrum measured by the radiation thermometer depending on the material composition can be obtained. Use of a radiation thermometer is desirable because it enables non-contact measurement of component concentration.

  In addition, as shown in the present embodiment, a spectroscopic measurement device that uses a change in sound velocity due to a temperature rise measures heating by light using ultrasound, which is an inexpensive means that is excellent in straightness in a living body. This is desirable because it enables inexpensive component concentration measurement with excellent position resolution even inside the living body.

  In the present embodiment, the configuration in which the specimen contact portion is provided between the ultrasound probe and the specimen (living body) has been described. However, the living body is heated by using the contact surface itself of the ultrasound probe as the specimen contacting section. It may have a (cooling) function and a multi-configuration.

  Further, in the present embodiment, as shown in the first embodiment, the configuration including the means for suppressing the blood flow makes it possible to measure the component concentration with higher accuracy.

(Embodiment 4)
In the present embodiment, as in the third embodiment, in a spectroscopic measurement apparatus that heats a specimen with light of a specific wavelength and measures a difference in temperature increase due to a difference in light absorption rate of each part as a change in sound speed. An object is to suppress a decrease in measurement accuracy due to a difference in proportionality coefficient between the temperature change and the sound speed change depending on the material composition and the composition ratio of each part.

  Similarly to the third embodiment, the ultrasonic sound velocity measurement results during uniform heating and non-uniform heating are compared, and the sound velocity temperature change coefficient is obtained, so that the change in the sound velocity at the time of selective heating light irradiation / non-irradiation can be obtained. Thus, it is possible to measure the temperature rise distribution (component concentration distribution) closer to the actual situation (uniform cooling cannot be performed in this embodiment).

  However, the present embodiment is different from the third embodiment in uniform heating means.

  As shown in FIG. 11, in the spectroscopic measurement apparatus of this embodiment, uniform heating is performed by irradiating the living body 104 with the microwave generated by the microwave transmission source 1101.

  Compared with near-infrared light (wavelength 600 nm to 1500 nm) used as selective heating light, the microwave has a smaller difference in absorption rate depending on the material composition of each part in the living body 104 and can be used as a uniform heating means. .

  For example, when a living body is used as a specimen, it is desirable to irradiate the living body with microwaves having a high water absorption rate around 2.45 GHz (2 to 3 GHz), thereby enabling uniform heating.

  In addition, it is desirable to irradiate the living body with 3 to 7 GHz or 1 to 2 GHz microwaves, because the living body can be uniformly heated to a deeper portion than when 2 to 3 GHz microwaves are irradiated.

  The spectroscopic measurement apparatus of the present embodiment enables highly accurate component concentration measurement by the same operation as that of the third embodiment.

  In addition, the uniform heating means using microwaves as in the present embodiment enables high accuracy even in a spectroscopic measurement apparatus that measures component concentration from photoacoustic wave energy as shown in FIG. .

  In the spectroscopic measurement device of FIG. 11, by comparing both the photoacoustic wave generated by selective heating pulsed light irradiation and the photoacoustic wave generated by pulsed microwave irradiation and the generation location by pulse driving both the light source and the microwave source, It can also be applied to suppress variations in the proportional coefficient between photoacoustic wave and light absorption rate (decrease in measurement accuracy) due to differences in temperature rise rate and expansion rate due to heat generation depending on the material composition and composition ratio of each part. It becomes.

  Further, in the present embodiment, as shown in the first embodiment, the configuration including the means for suppressing the blood flow makes it possible to measure the component concentration with higher accuracy.

  In particular, the spectroscopic measurement apparatus provided with the means for cooling the specimen of the first embodiment makes it possible to irradiate a living body with higher-output microwaves, and to achieve a more accurate component concentration. Measurement is possible.

(Embodiment 5)
In the conventional spectroscopic measurement apparatus as shown in FIG. 2, as shown in FIG. 13, after the ultrasonic sound velocity measurement (first time) 1301, selective light heating 1302 by selective heating light irradiation is started. Thereafter, the ultrasonic sound velocity measurement (second time) 1303 was performed at a timing when the temperature change of the plaque 106 in the living body 104 sufficiently increased and heat generation and heat release were balanced to reduce the temporal change in temperature.

  However, it takes a long time until the heat generation and the heat radiation are balanced, and a positional shift between the living body 104 and the ultrasonic probe 102 occurs between the ultrasonic sound speed measurement (first time) 1301 and the ultrasonic sound speed measurement (second time) 1303. However, the measurement accuracy was lowered.

  In this embodiment, a spectroscopic measurement apparatus that heats a specimen with light of a specific wavelength and measures a difference in temperature increase due to a difference in light absorption rate of each part as a change in sound speed enables a reduction in measurement time. .

  FIG. 12 shows the spectroscopic measurement apparatus of the present embodiment.

  As shown in FIG. 12, the spectroscopic measurement apparatus according to the present embodiment includes a light source 101, an ultrasonic measurement apparatus 102, and a signal transmission line 1201.

  12, similarly to the conventional example, the living body 104 is irradiated with selective heating light 1202 having a wavelength of about 1200 nm (1100 nm or more and 1300 nm or less), and the fat degree (fat concentration) of the intravascular plaque 106 is irradiated. ).

  A sound speed change (temperature change) in the living body 104 is obtained by measuring and comparing the sound speed of each part in the living body 104 when the selective heating light 1202 is irradiated and not irradiated by the light source 101 with the ultrasonic measuring device 102. Is possible. Thereby, a desired component concentration distribution in the living body 104 can be obtained.

  In particular, in the spectroscopic measurement apparatus according to the present embodiment, the light source 101 and the ultrasonic measurement apparatus 102 are connected by the signal transmission line 1201, the timing at which the living body 104 is irradiated with the selective heating light 1202, and the ultrasonic wave from the living body 104. The timing for measuring the sound speed in the living body 104 by pulse transmission / reception can be adjusted more accurately.

  As the spectroscopic measurement apparatus of the present embodiment, for example, as shown in FIG. 14, from ultrasonic sound speed measurement (first time) 1401 (or start of selective light heating 1302) to ultrasonic sound speed measurement (second time) 1402. It is desirable to reduce time. As a result, it is possible to suppress a decrease in measurement accuracy due to a positional deviation between the living body and the ultrasonic probe, and to perform more accurate component concentration measurement.

  More preferably, as shown in FIG. 15, ultrasonic sound velocity measurement (first time) 1501 is performed immediately before the end of selective light heating 1302, and ultrasonic sound velocity measurement (second time) is performed immediately after the end of selective light heating 1302. It is more desirable to implement 1502. Immediately after the start of the selective light heating 1302, the temperature 1304 of the portion (peripheral portion) other than the plaque 106 similarly rises, but immediately after the selective light heating 1302 is finished, the peripheral portion is compared with the decrease in the temperature 1305 of the plaque 106. Since the decrease in the temperature 1304 is small, it is possible to measure the component concentration with higher contrast by the ultrasonic sound velocity measurement at the timing shown in FIG.

  Further, as shown in FIG. 14 and FIG. 15, when the ultrasonic sound velocity measurement is performed at a timing when the time change of the temperature 1305 of the plaque 106 is large, as the ultrasonic probe 102a, a convex type, an electronic sector type, an electronic linear type, It is desirable to use an ultrasonic probe in which transducers are arranged two-dimensionally, and it is possible to measure component concentrations with higher accuracy by high-speed ultrasonic sound velocity measurement.

  In the case of convex type and electronic sector type, it is desirable to radiate ultrasonic pulses by changing the direction of the ultrasonic beam discontinuously, and more accurate component concentration measurement by higher-speed ultrasonic sound velocity measurement. Is possible.

  14 and 15, when ultrasonic sound velocity measurement is performed immediately after the start or end of the selective light heating 1302, the time constant of the change of the temperature 1305 depends on the size of the plaque 106 and the blood flow around the plaque 106. Is different. For this reason, it is desirable to perform ultrasonic sound velocity measurement (third time) 1403 and 1503 within 10 seconds from ultrasonic sound velocity measurement (second time) 1402 and 1502. As a result, the time constant for each plaque can be obtained, and the component concentration can be measured with high accuracy.

  In addition, it is desirable to reverse the ultrasonic beam scanning direction between ultrasonic sound velocity measurement (second time) and (third time), and furthermore, highly accurate component concentration measurement is possible.

  In addition, it is desirable to oscillate ultrasonic pulses having different waveforms in ultrasonic sound velocity measurement (second time) and (third time), and it becomes possible to measure component concentrations with high resolution from a shallow part to a deep part.

  Further, in a spectroscopic measurement apparatus using a human body as a specimen, ultrasonic sound velocity measurement is performed a plurality of times within 20 seconds, and a sound velocity change distribution is obtained by comparing at least two ultrasonic sound velocity measurement results. Is desirable. Regardless of individual differences, it is a time during which breathing can be stopped, and it is possible to suppress measurement errors due to breathing.

  Also, in the present embodiment, an example of a spectroscopic measurement device that measures the fat degree of plaque has been shown. Needless to say, the same applies to a spectroscopic measurement device for measuring other component concentration and component concentration distributions. The same effect can be obtained with this configuration.

  In addition, combining the configurations described in Embodiments 1, 3, 4, and 5 is desirable because a more effective configuration can be obtained.

(Embodiment 6)
In this embodiment, a spectroscopic measurement apparatus that performs component concentration distribution measurement by heating or cooling a specimen and measuring a difference in change of the Gruneisen constant due to a temperature change of each part in the specimen is shown.

  FIG. 16 is a schematic diagram showing an example of a spectroscopic measurement apparatus according to Embodiment 6 of the present invention.

  The spectroscopic measurement apparatus in FIG. 16 includes at least a light source 1601 and an ultrasonic measurement apparatus 102.

  FIG. 16 shows a spectroscopic measurement apparatus that measures a component concentration distribution by heating a specimen with light of a specific wavelength and measuring a difference in change in the Gruneisen constant due to a temperature rise in each part in the specimen. Hereinafter, an example of the operation will be described.

  (1) Photoacoustic wave generation step (first time): The selective heating pulse light 1602 is transferred to the living body 104 using the light source 1601 including the laser light source 1601a and the optical fiber 101b that guides the pulse laser light generated by the laser light source 1601a to the living body. Irradiate toward. As a result, instantaneous heat generation occurs at a portion where the light absorption rate with respect to the selective heating pulse light 1602 is high, and the instantaneous expansion accompanying the temperature rise generates an ultrasonic wave (photoacoustic wave).

  (2) Photoacoustic wave measurement process (first time): The photoacoustic wave in the living body 104 is received by the ultrasonic measuring apparatus 102 provided with the ultrasonic probe 102a, and the generation of the photoacoustic wave generated in each part in the living body It becomes possible to ask for energy.

  (3) Selection light heating step: The selection light 1604 is irradiated toward the living body 104 using the light source 1603 including the laser light source 1603a and the optical fiber 101b that guides the pulse laser beam generated by the laser light source 1603a to the living body. As a result, heat is generated in each part in accordance with the light absorption rate with respect to the selective heating light 1604, and a temperature rise is generated.

  (4) Photoacoustic wave generation process (second time): same as the first time

  (5) Photoacoustic wave measurement process (second time): same as the first time

  (6) From the results of the temperature rise calculation steps (2) and (5), the change in the energy of the photoacoustic wave generated in each part is obtained, and the temperature rise in each part is calculated from the change in the energy of the photoacoustic wave. .

  In this embodiment, as shown in (1) to (6) above, at least one photoacoustic wave generation and photoacoustic wave measurement is performed before and after heating the living body 104 with the selective heating light 1604.

  The sound pressure of the photoacoustic wave generated in each part of the living body is proportional to the product of the light absorption rate and the Gruneisen constant. However, here, the Gruneisen constant varies depending on the temperature of the part.

  For this reason, in (3) the selective light heating process, a temperature change corresponding to the component concentration of each part in the living body 104 is given, and the light of each part obtained in the photoacoustic wave generation / measurement process of (1) and (2). By comparing the energy of the acoustic wave with the energy of the photoacoustic wave of each part obtained in the photoacoustic wave generation / measurement process of (4) and (5) in the process of (6), the selective light heating in (3) The temperature change of each part in a process is calculated | required and component concentration distribution measurement is attained.

  Here, because the change in photoacoustic wave energy is proportional to the temperature change regardless of the sample size, it is possible to suppress variations in the component concentration measurement accuracy due to the sample size. Distribution measurement is possible.

  As described above, the spectroscopic measurement device that obtains the temperature rise from the rate of change of the energy of the photoacoustic wave is higher than the spectroscopic measurement device that obtains the temperature rise of each part from the change in sound speed as shown in the first embodiment depending on the application. Accurate component concentration distribution measurement is possible.

  For example, when the living body 104 is irradiated with selective heating light 1604 having a wavelength of about 1200 nm (1100 nm or more and 1300 nm or less) and the fat degree (fat concentration) of the intravascular plaque 106 is measured, the intravascular plaque 106 is the inner lining of the blood vessel. Therefore, when the sound velocity change of the plaque portion is obtained, it is necessary to measure the ultrasonic wave reflected by the inner film and the ultrasonic wave reflected by the outer film with the ultrasonic probe 102a.

  However, in the case of atherosclerosis (atherosclerosis), which is a kind of intravascular plaque, an intima that does not easily reflect ultrasonic waves may be provided. In this case, the accuracy for obtaining the change in sound speed is reduced.

  As shown in the present embodiment, the spectroscopic measurement device that obtains the temperature rise amount of each part from the rate of change of the energy of the photoacoustic wave obtains the temperature rise amount even for a site that hardly reflects ultrasonic waves as described above. Therefore, as in this embodiment, a spectroscopic measurement apparatus configured to measure a temperature rise caused by selective heating light by photoacoustic wave generation by selective heating pulse light irradiation is most desirable.

  Needless to say, the configuration of the first embodiment does not require an effective member such as a pulsed light source, and thus is desirable in terms of inexpensive component concentration distribution measuring means.

  In addition, even if there is no selective heating step of (3), the component concentration distribution measurement can be performed by measuring the photoacoustic wave generated according to the difference in the light absorption rate of each part as before, By performing the selective heating step (3) as shown in the present embodiment, it is possible to measure the component concentration distribution with higher resolution.

  That is, when simply measuring the component concentration with the magnitude of the photoacoustic wave energy, the resolution is determined according to the pulse width of the selective heating pulse light, but the temperature change due to the selective heating step (3) Regardless of the pulse width, the smaller the light absorption point, the higher the thermal diffusion coefficient. Therefore, the size of the light absorption point can be determined by calculating the temperature change rate (time constant) even for a smaller light absorption point. It becomes possible.

  In order to obtain the rate of temperature change due to light absorption, it is desirable to perform the steps (4) and (5) by changing the time from the start of the selective light heating in (3). By changing the time intervals of (3), (4), and (5), the size of the light absorbing portion can be obtained with high accuracy.

  In addition, after the selective light heating in (3) is performed for a certain time, the selective heating light irradiation is stopped, and (4) and (5) may be performed. In this case, the temperature lowering time of the light absorption portion due to the selective heating light irradiation is obtained, and the time from the end of the selective heating light irradiation to (4) and (5) is changed as in the case of obtaining the above temperature rising time. It is possible to measure the size of the light absorption portion with high accuracy.

  In the present embodiment, it is desirable that the selective heating pulse light irradiated in the steps (1) and (4) is generated from the same light source, and the wavelength and output of the two selective heating pulse lights are approximately the same. Since it is possible to align, it is possible to improve the accuracy of measurement.

  In addition, it is possible to employ a configuration in which both the selective heating light and the selective heating pulse light are generated by a single light source, which is desirable as a means capable of measuring the component concentration distribution at a lower cost.

  However, as shown in FIG. 16, it is desirable to generate selective heating light and selective heating pulse light with separate light sources, and to select the optimal wavelength according to the purpose, so that more accurate component concentration measurement is possible. It becomes.

  For example, when measuring the concentration distribution of oxyhemoglobin and deoxyhemoglobin for discrimination between cancer and benign tumor, it is desirable to use light having a wavelength of about 800 nm or 600 nm as selective heating pulse light. This is a wavelength at which the light absorptivity of oxygenated hemoglobin and deoxygenated hemoglobin is approximately the same. Further, as selective heating light, it is desirable to use light having a wavelength of about 750 nm or a wavelength of about 1064 nm which has a large difference in absorbance between oxyhemoglobin and deoxygenated hemoglobin. By selecting these wavelengths, cancer with higher accuracy can be obtained. And benign tumors can be identified.

  In the present embodiment, it is needless to say that the concentration distribution measurement of many components is performed with higher accuracy by changing the wavelength of the selective heating light and performing the measurement steps (1) to (6) multiple times. Is desirable because it becomes possible.

  Moreover, in this Embodiment, the output of selective heating light is changed and the measurement process of (1)-(6) is performed in multiple times, and nonlinear absorption rates, such as multiphoton absorption in each part in a measurement range, are calculated | required. It is desirable because it becomes possible. This makes it possible to measure the concentration distribution of many components.

  It is desirable to use pulsed light as selective heating light. As a result, the non-linear absorption rate can be obtained with higher accuracy, and the component concentration distribution measurement accuracy can also be improved.

  Further, by changing the waveform of the pulsed light used for the selective heating light and performing the measurement steps (1) to (6) a plurality of times, the component concentration distribution measurement can be performed with higher accuracy (the non-linear absorption rate is obtained). .

  In addition, the component concentration distribution measurement can be performed with higher accuracy by changing the peak light intensity of the pulsed light used for the selective heating light and performing a plurality of measurement steps (1) to (6).

  In addition, by calculating the difference in temperature rise of each part when irradiating a plurality of continuous pulsed light as selective heating light and when irradiating selective heating light of CW light having the same average output or wavelength, Furthermore, it becomes possible to obtain the nonlinear absorption rate with high accuracy, and the component concentration distribution measurement accuracy is also improved.

  Further, similarly to the fifth embodiment shown in FIG. 15, also in this embodiment, after sufficiently heating with selective heating light, (1) and (2) are performed, and after the heating is completed. It is good also as a measurement procedure which implements (4)-(6), and, thereby, component concentration distribution measurement with higher accuracy is possible.

  Needless to say, by performing the photoacoustic wave generation step and the photoacoustic wave measurement step a plurality of times after the heating is completed, the component concentration distribution measurement can be performed with higher accuracy.

  As mentioned above, the effect was shown about the structure which irradiates a specimen with pulsed light as selective heating light. However, the structure using CW light without using pulsed light as selective heating light is the cheapest and realizes large heating with high efficiency. It is desirable in that it is a light source that can be used.

  Also, in this embodiment, similarly to the other embodiments, it is more desirable to include a cooling means that absorbs part of the heat of the specimen through the specimen contact portion 103, and by suppressing thermal diffusion due to blood flow, Furthermore, highly accurate component concentration distribution measurement is possible.

  In addition, combining the configurations described in the first, third, fourth, and fifth embodiments is desirable because more accurate component concentration distribution measurement is possible.

  As described above, the spectroscopic measurement device and the light irradiation device of the present invention have been described. However, the configuration shown in this specification is an example, and it is needless to say that various modifications can be made without departing from the gist of the present invention. Yes.

  The spectroscopic measurement apparatus according to the present invention can be applied to liver fat concentration measurement, intravascular plaque property diagnosis, tumor property diagnosis, gas component distribution measurement, and the like. This is a useful means for improving the accuracy of these measurements.

DESCRIPTION OF SYMBOLS 101 Light source 101a Laser light source 101b Optical fiber 101c Optical fiber winding part 102 Ultrasonic measuring device 102a Ultrasonic probe 102b Measuring device main body 102c Cable 103 Specimen contact part 104 Specimen 105 Selective heating light 106 Plaque 107 Heat exchange part 108 Drive power supply 109 Heat radiation Unit 110 temperature measurement means 301 pulse light source 301a pulse laser light source 302 selective heating pulsed light 401 sample contact unit 501 sample contact unit
502 sonic heat change member 601 fiber grating 701 cancer tissue 702 selective heating light 703 living body 901 water tank 902 water 1001 specimen contact portion 1101 microwave transmission source 1201 signal transmission line 1202 selective heating light 1301 ultrasonic sound velocity measurement (first time)
1302 Selective light heating 1303 Ultrasonic sound velocity measurement (second time)
1304 Surrounding temperature 1305 Plaque temperature 1401 Ultrasonic sound velocity measurement (first time)
1402 Ultrasonic velocity measurement (second time)
1403 Ultrasonic sound velocity measurement (third time)
1501 Ultrasonic sound velocity measurement (first time)
1502 Ultrasonic velocity measurement (second time)
1503 Ultrasonic velocity measurement (third time)
1601 Light source 1601a Laser light source 1602 Selective heating pulse light 1603 Light source 1603a Laser light source 1604 Selective heating light

Claims (13)

A light source that generates pulsed light to irradiate the specimen, an ultrasonic probe that receives an ultrasonic pulse generated in the specimen, and an ultrasonic wave that is generated inside the specimen based on a signal received by the ultrasonic probe A spectroscopic measurement apparatus including a signal processing unit that calculates the generation location and intensity of a pulse,
A spectroscopic measurement apparatus that irradiates the specimen with pulsed light before and after irradiating the specimen with light generated by the light source or another light source. The spectroscopic measurement device according to claim 1, wherein the specimen is irradiated with a plurality of pulse lights having different waveforms. The spectroscopic measurement apparatus according to claim 1, wherein the light source irradiates the specimen with both short pulse light and CW light having a pulse width of nanosecond order at different timings. The spectroscopic measurement apparatus according to claim 3, wherein the CW light and the pulsed light that irradiate the specimen are generated from a single light source. The spectroscopic measurement device further includes:
The spectroscopic measurement apparatus according to claim 1, comprising means for absorbing part of the thermal energy of the specimen and reducing the temperature of the specimen. Means for absorbing part of the thermal energy of the specimen and lowering the temperature of the specimen,
A heat absorption part in contact with at least the specimen;
The heat absorption part is made of a material that transmits light generated by the light source,
The spectroscopic measurement apparatus according to claim 5, wherein the specimen is irradiated with light generated by the light source through the heat absorption unit. The spectroscopic measurement device further includes:
The spectroscopic measurement apparatus according to claim 1, further comprising means for pressing the specimen. The spectroscopic measurement apparatus according to claim 1, wherein the specimen is irradiated with a plurality of lights having different wavelengths. The specimen is a living body;
Irradiating the living body with light having a wavelength of 1100 nm or more and 1300 nm or less,
The spectroscopic measurement device according to claim 1, wherein the fat concentration at a desired location in the living body is measured. The spectroscopic measurement device further includes:
The spectroscopic measurement apparatus according to claim 5, further comprising a radiation thermometer that measures a change in surface temperature of the specimen. The spectroscopic measurement device further includes:
A means for heating or cooling the specimen to a temperature distribution different from the heating by the light, comprising at least a specimen contact portion in contact with the specimen;
The specimen contact portion is made of a material that transmits light generated by the light source,
The spectroscopic measurement apparatus according to claim 1, wherein the specimen is irradiated with light generated by the light source through the specimen contact portion. The spectroscopic measurement device according to claim 1, wherein photoacoustic waves in the sample are measured at least during light irradiation from the light source to the sample and after the light irradiation is completed. The spectroscopic measurement apparatus according to claim 12, wherein after the light irradiation ends, the same portion of the specimen is irradiated with pulsed light a plurality of times, and photoacoustic waves generated in the subject are received.

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