WO2016151787A1 - 血管認識用血流測定方法 - Google Patents
血管認識用血流測定方法 Download PDFInfo
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- WO2016151787A1 WO2016151787A1 PCT/JP2015/059041 JP2015059041W WO2016151787A1 WO 2016151787 A1 WO2016151787 A1 WO 2016151787A1 JP 2015059041 W JP2015059041 W JP 2015059041W WO 2016151787 A1 WO2016151787 A1 WO 2016151787A1
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- blood vessel
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- 210000004204 blood vessel Anatomy 0.000 title claims abstract description 82
- 230000017531 blood circulation Effects 0.000 title claims abstract description 53
- 238000000034 method Methods 0.000 title claims abstract description 10
- 238000001228 spectrum Methods 0.000 claims abstract description 149
- 230000010354 integration Effects 0.000 claims description 12
- 238000000691 measurement method Methods 0.000 claims description 7
- 230000001678 irradiating effect Effects 0.000 claims description 6
- 230000002123 temporal effect Effects 0.000 abstract 1
- 230000009466 transformation Effects 0.000 abstract 1
- 210000004369 blood Anatomy 0.000 description 14
- 239000008280 blood Substances 0.000 description 14
- 238000001514 detection method Methods 0.000 description 13
- 238000010606 normalization Methods 0.000 description 9
- 239000013307 optical fiber Substances 0.000 description 6
- 230000003068 static effect Effects 0.000 description 5
- 230000015271 coagulation Effects 0.000 description 4
- 238000005345 coagulation Methods 0.000 description 4
- 238000010336 energy treatment Methods 0.000 description 4
- 238000001356 surgical procedure Methods 0.000 description 4
- 230000000740 bleeding effect Effects 0.000 description 3
- 210000003743 erythrocyte Anatomy 0.000 description 3
- 0 CC(*)C(C*1(C2C(C)C*)*2[N+]([O-])=O)C1=C Chemical compound CC(*)C(C*1(C2C(C)C*)*2[N+]([O-])=O)C1=C 0.000 description 2
- 230000007423 decrease Effects 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 238000012986 modification Methods 0.000 description 1
- 230000004048 modification Effects 0.000 description 1
- 238000012545 processing Methods 0.000 description 1
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Classifications
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
- A61B5/026—Measuring blood flow
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01F—MEASURING VOLUME, VOLUME FLOW, MASS FLOW OR LIQUID LEVEL; METERING BY VOLUME
- G01F1/00—Measuring the volume flow or mass flow of fluid or fluent solid material wherein the fluid passes through a meter in a continuous flow
- G01F1/66—Measuring the volume flow or mass flow of fluid or fluent solid material wherein the fluid passes through a meter in a continuous flow by measuring frequency, phase shift or propagation time of electromagnetic or other waves, e.g. using ultrasonic flowmeters
- G01F1/663—Measuring the volume flow or mass flow of fluid or fluent solid material wherein the fluid passes through a meter in a continuous flow by measuring frequency, phase shift or propagation time of electromagnetic or other waves, e.g. using ultrasonic flowmeters by measuring Doppler frequency shift
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B10/00—Other methods or instruments for diagnosis, e.g. instruments for taking a cell sample, for biopsy, for vaccination diagnosis; Sex determination; Ovulation-period determination; Throat striking implements
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
- A61B5/026—Measuring blood flow
- A61B5/0261—Measuring blood flow using optical means, e.g. infrared light
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/02—Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
- A61B5/026—Measuring blood flow
- A61B5/0285—Measuring or recording phase velocity of blood waves
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B8/00—Diagnosis using ultrasonic, sonic or infrasonic waves
- A61B8/06—Measuring blood flow
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01S—RADIO DIRECTION-FINDING; RADIO NAVIGATION; DETERMINING DISTANCE OR VELOCITY BY USE OF RADIO WAVES; LOCATING OR PRESENCE-DETECTING BY USE OF THE REFLECTION OR RERADIATION OF RADIO WAVES; ANALOGOUS ARRANGEMENTS USING OTHER WAVES
- G01S15/00—Systems using the reflection or reradiation of acoustic waves, e.g. sonar systems
- G01S15/88—Sonar systems specially adapted for specific applications
- G01S15/89—Sonar systems specially adapted for specific applications for mapping or imaging
- G01S15/8906—Short-range imaging systems; Acoustic microscope systems using pulse-echo techniques
- G01S15/8979—Combined Doppler and pulse-echo imaging systems
Definitions
- the present invention relates to a blood flow measurement method for blood vessel recognition.
- Patent Document 1 a surgical treatment apparatus having a function of optically detecting a blood vessel present in a living tissue has been proposed (see, for example, Patent Document 1).
- Patent Document 1 a blood volume in a living tissue is measured, and it is determined whether or not a blood vessel exists based on the measured blood volume.
- the blood vessel detection method based on the blood volume of Patent Document 1 has a problem that blood vessel detection accuracy is low and usefulness for an operator is poor. That is, blood in the blood vessel and leaked blood leaked from the blood vessel due to bleeding are measured in the same manner without distinction, so that the blood vessel cannot be accurately detected separately from the leaked blood. For the surgeon, it is particularly important to accurately recognize the position of a thick blood vessel. However, in the method of Patent Document 1, a thin blood vessel and a thick blood vessel are detected without distinction, which is really important for the surgeon. The blood vessel cannot be identified.
- the present invention has been made in view of the above-described circumstances, and can accurately detect a blood vessel existing in a living tissue and can selectively detect a blood vessel having a predetermined thickness.
- An object is to provide a blood flow measuring method for recognition.
- One embodiment of the present invention includes a step of acquiring a real-time Doppler spectrum by Fourier-transforming a time waveform of scattered light intensity generated by irradiating a living body with laser light, and the real-time Doppler spectrum in a predetermined standardized region.
- a blood vessel comprising: obtaining a calculation spectrum by using the calculation spectrum; calculating an average frequency based on the calculation spectrum; and comparing the calculated average frequency with a predetermined threshold to determine a blood flow velocity This is a blood flow measurement method for recognition.
- the time waveform of the scattered light intensity in the living body of the laser light is Fourier-transformed to obtain the real-time Doppler spectrum, and the obtained real-time Doppler spectrum is normalized by the average value in the normalization region A real time Doppler spectrum is calculated.
- a standard obtained by separately obtaining a zero spectrum obtained by Fourier-transforming the time waveform of the scattered light intensity obtained by irradiating laser light in the absence of blood flow, and standardized by the average value in the standardized region A zero spectrum is calculated.
- the normalization region an arbitrary frequency region in which the intensity of the real-time Doppler spectrum corresponding to the desired blood flow is set to a frequency higher than the frequency at which the intensity is the same as that of the noise floor is employed.
- a difference spectrum with reduced noise floor and spike noise is calculated.
- a region spectrum in which low frequency noise is reduced is calculated.
- a PS reference spectrum with reduced random noise and spike noise is calculated by subtracting the maximum value in the PS reference area from the area spectrum.
- the average frequency is calculated based on the calculation spectrum from which the low-frequency noise, noise floor, spike noise, and random noise included in the real-time Doppler spectrum are removed. It is possible to accurately determine the thickness of the blood vessel to be performed.
- the step of determining the blood flow velocity by comparing the calculated average frequency with a predetermined threshold value determines that there is a blood vessel when the average frequency is greater than the predetermined first threshold value. Also good. By doing so, it is determined that a blood vessel exists only when the average frequency is greater than the first threshold value and the blood flow is relatively large, so that attention is not given to a site where only a small blood vessel exists. The treatment can be performed smoothly.
- the step of determining the blood flow velocity by comparing the calculated average frequency with a predetermined threshold is performed when the average frequency is smaller than the second threshold greater than the first threshold. It may be determined that there is a blood vessel. By doing so, when the scattered light intensity of the laser light in the living body is low, when the average frequency is larger than the second threshold, it is determined that there is no blood vessel, so that only a small blood vessel exists. Since the accuracy for not calling attention to the part is increased, the treatment can be performed more smoothly.
- the step of calculating the average frequency includes obtaining a calculation spectrum in a predetermined integration region and a frequency integral value of the spectrum obtained by multiplying the calculation spectrum by the frequency, and a predetermined integration cutoff.
- the average frequency is calculated only when the frequency integral value of the spectrum for calculation is larger than the predetermined integral cutoff value, and the average frequency is set to zero when it is less than the integral cutoff value. It is possible to prevent the determination accuracy of blood vessels from being lowered by a noise floor that cannot be completely removed by random noise.
- the present invention it is possible to accurately detect a blood vessel existing in a living tissue and to selectively detect a blood vessel having a predetermined thickness.
- FIG. 1 It is a figure which shows typically the surgical treatment system to which the blood flow measurement method for blood vessel recognition which concerns on one Embodiment of this invention is applied. It is a flowchart which shows the blood flow measurement method for blood vessel recognition of FIG. It is a figure explaining scattering of the laser beam by the static component in a biological tissue. It is a figure explaining scattering of the laser beam by the dynamic component in a biological tissue. It is a figure which shows an example of the time series data of the intensity
- FIG. 1 It is a figure which shows an example of the real-time Doppler spectrum in case the blood flow acquired in the determination part of FIG. 1 exists. It is a figure which shows an example of the signal spectrum by the blood flow contained in the real time Doppler spectrum of FIG. It is a figure which shows an example of the low frequency noise contained in the real-time Doppler spectrum of FIG. It is a figure which shows an example of the noise floor contained in the real-time Doppler spectrum of FIG. It is a figure which shows an example of the spike noise contained in the real-time Doppler spectrum of FIG. It is a figure which shows an example of the random noise contained in the real-time Doppler spectrum of FIG. It is a figure which shows a mode that the low frequency noise of FIG.
- the blood flow measuring method for blood vessel recognition includes an energy treatment tool 1 for treating a living tissue A and a blood vessel detecting means for optically detecting a blood vessel B in the living tissue A. 2 and the blood vessel detection means 2 of the system including the control unit 3 that controls the energy treatment device 1 based on the detection result of the blood vessel detection means 2.
- the energy treatment instrument 1 is connected to an elongated body 4 that can be inserted into the body, an energy acting unit 5 that is provided at the distal end of the body 4 and applies energy to the living tissue A, and a proximal end of the body 4. And an energy supply unit 6 for supplying an energy source to the energy acting unit 5 through a wiring passing through the inside of the body unit 4.
- the energy action unit 5 is an energy forceps (for example, a grasping forceps capable of supplying a monopolar, bipolar or energy source) having a pair of jaws 7 and 8 capable of gripping the living tissue A.
- the upper jaw 7 and the lower jaw 8 have inner surfaces 7a and 8a facing each other.
- the upper jaw 7 and the lower jaw 8 generate energy (for example, high-frequency current or ultrasonic waves) when an energy source (for example, high-frequency current) is supplied from the energy supply unit 6, and the generated energy is transmitted to the inner surfaces 7a, 7a, From 8a, it discharge
- the energy action part 5 has an incision mode in which the living tissue A is incised with high energy and a coagulation mode in which the living tissue A is coagulated with low energy lower than the high energy in the incision mode.
- the energy operation unit 5 switches between the incision mode and the coagulation mode according to the strength of the energy source supplied from the energy supply unit 6.
- the blood vessel detection means 2 includes a laser light source 9 that outputs laser light L, a light emitting unit 10 that is provided on the inner surface 7a of the upper jaw 7 and emits the laser light L supplied from the laser light source 9, and an inner surface 8a of the lower jaw 8.
- a light receiving unit 11 that receives the scattered light S of the laser light L scattered by the biological tissue A
- a light detection unit 12 that detects the scattered light S received by the light receiving unit 11, and the light detection unit.
- Frequency analysis unit 13 that acquires time series data of the intensity of scattered light S detected by 12 and frequency-analyzes the time series data, and a diameter in a predetermined range based on the frequency analysis result by frequency analysis unit 13.
- a determination unit 14 that determines the presence or absence of the blood vessel B to be detected.
- the laser light source 9 outputs laser light L in a wavelength region (for example, infrared region) that is less absorbed by blood.
- the laser light source 9 is connected to the light emitting unit 10 via an optical fiber 15 that passes through the inside of the body unit 4.
- the laser light L incident on the optical fiber 15 from the laser light source 9 is guided to the light emitting unit 10 by the optical fiber 15 and is emitted from the light emitting unit 10 toward the inner surface 8 a of the lower jaw 8.
- the light receiving unit 11 is connected to the light detection unit 12 via an optical fiber 16 that passes through the inside of the body unit 4.
- the scattered light S received by the light receiving unit 11 is guided to the light detecting unit 12 by the optical fiber 16 and is incident on the light detecting unit 12.
- the light detection unit 12 converts the intensity of the scattered light S incident from the optical fiber 16 into a digital value, and sequentially transmits the digital value to the frequency analysis unit 13.
- the digital value received from the light detection unit 12 is recorded in time series over a predetermined period by the frequency analysis unit 13.
- the time series data indicating the time change of the intensity of the scattered light S is acquired (step S1).
- the frequency analysis unit 13 calculates the real-time Doppler spectrum f RT ( ⁇ ) by performing fast Fourier transform on the acquired time-series data (step S2).
- the biological tissue A includes fat, a static component that is stationary like leaked blood exposed from the blood vessel B due to bleeding, and blood in the blood flowing in the blood vessel B. And moving dynamic components such as red blood cells C.
- the static component is irradiated with the laser beam L having the frequency f
- scattered light S having the same frequency f as the laser beam L is generated.
- the dynamic component is irradiated with the laser beam L having the frequency f
- scattered light S having a frequency f + ⁇ f shifted from the frequency f of the laser beam L is generated by Doppler shift.
- the frequency shift amount ⁇ f at this time depends on the moving speed of the dynamic component.
- the scattered light S scattered by the blood in the blood vessel B and having the frequency f + ⁇ f, and static other than the blood in the blood vessel B is simultaneously received by the light receiving unit 11.
- the intensity of the entire scattered light S periodically changes due to the interference between the scattered light S with the frequency f and the scattered light S with the frequency f + ⁇ f. Appears.
- the traveling direction of the light and the moving direction (blood flow direction) of the red blood cell when the laser light enters the red blood cell are determined.
- the incident angle formed is not single but has a distribution.
- distribution occurs in the frequency shift amount ⁇ f due to the Doppler shift.
- the beat of the intensity of the scattered light S as a whole overlaps several frequency components corresponding to the distribution of ⁇ f.
- the distribution of ⁇ f spreads to the higher frequency side as the blood flow velocity increases.
- the normalized region R Nrm is set to an appropriate frequency range in the real-time Doppler spectrum f RT ( ⁇ ). As shown in FIG. 9, the normalized region R Nrm is set to a frequency higher than the frequency at which the intensity of the real-time Doppler spectrum f RT ( ⁇ ) corresponding to the desired blood flow is comparable to the noise floor intensity. Any frequency range. Further, the zero spectrum f ZERO ( ⁇ ) including only the noise floor and the spectrum is calculated from the scattered light intensity obtained by irradiating the laser light L in the absence of blood flow (step S3).
- the real-time Doppler spectrum f RT ( ⁇ ) and the zero spectrum f ZERO ( ⁇ ) are normalized using the average value of the real-time Doppler spectrum f RT ( ⁇ ) in the normalization region R Nrm (steps S4 and S5).
- the normalized zero spectrum f zNrm ( ⁇ ) from the normalized real-time Doppler spectrum f Nrm ( ⁇ ) is calculated (step S6).
- the noise spectrum and the differential spectrum f SUB ( ⁇ ) in which the spike noise is partially reduced are calculated.
- an integration region R Int is set so that the signal spectrum region due to blood flow is not excessively cut and low frequency noise can be cut, and as shown in FIGS. 13A and 13B,
- the spectrum in the frequency region lower than the integration region R Int is removed from the difference spectrum f SUB ( ⁇ ) to calculate the region spectrum f rng ( ⁇ ) (step S7).
- a region spectrum f rng ( ⁇ ) from which low frequency noise and some spike noise are removed is generated.
- the PS reference spectrum f PS ( ⁇ ) is calculated by subtracting the maximum value max PS from the region spectrum f rng (step S8).
- an element having a negative intensity is generated by subtracting the maximum value max PS of the region spectrum f rng . Therefore, as shown in FIG. 15A and FIG.
- the calculation spectrum f C ( ⁇ ) having all the intensities of 0 or more is calculated (steps S9 to S11).
- step S12 the calculated spectrum f C ( ⁇ ) and the calculated spectrum f C ( ⁇ ) multiplied by the frequency ⁇ are integrated with respect to the frequency ⁇ in the integration region R Int to obtain two integral values I f , I ⁇ f is acquired (step S12).
- step S13 it is determined whether or not the integral value If of the calculation spectrum is 0 (step S13). If it is 0, it is replaced with 1 for convenience (step S14). This avoids division by zero.
- step S15 it is determined whether or not the integral value If of the calculation spectrum is greater than a predetermined integral cutoff value IfCUT (step S15), and the average frequency is calculated as follows according to the determination result.
- step S16 the average frequency ⁇ ave is calculated (step S16), and when it is the integral value If below the cut-off value I fCUT, it is set to 0 without calculating the average frequency ⁇ ave. As a matter of fact (step S17), erroneous determination is prevented.
- step S18 it is determined whether or not the calculated value of the average frequency ⁇ ave is larger than a predetermined average frequency threshold value (first threshold value) ⁇ th (step S18). Since a faster blood flow exists, a determination result S TRUE that a relatively thick blood vessel B is present is generated (step S19). On the other hand, when the average frequency ⁇ ave is equal to or less than the average frequency threshold ⁇ th , a determination result S FALSE that the thick blood vessel B does not exist is generated (step S20). Then, a signal indicating one of the determination results is output from the determination unit 14 (step S21).
- first threshold value first threshold value
- the control unit 3 supplies an energy source having a high intensity from the energy supply unit 6 to the energy operation unit 5, thereby causing the energy operation unit Operate 5 in incision mode.
- the control unit 3 transfers the energy source from the energy supply unit 6 to the energy action unit 5 with a lower intensity than the energy source in the incision mode. To actuate the energy acting part 5 in the coagulation mode.
- the treatment target site of the living tissue A is held between the pair of jaws 7 and 8.
- the treatment target region between the jaws 7 and 8 is irradiated with the laser light L from the light emitting unit 10, and the scattered light S of the laser light L transmitted through the treatment target region while being scattered by the living tissue A is received by the light receiving unit 11.
- the received scattered light S is detected by the light detection unit 12, and time-series data of the scattered light S is generated in the frequency analysis unit 13.
- the average frequency ⁇ ave of the real-time Doppler spectrum f RT ( ⁇ ) is extracted by frequency analysis of time-series data, and the determination unit 14 applies a predetermined value to the living tissue A based on the average frequency ⁇ ave. It is determined whether or not there is a blood vessel B to be detected having a diameter in the range of.
- the control unit 3 When it is determined that the blood vessel B to be detected does not exist in the treatment target region, the control unit 3 operates the energy action unit 5 in the incision mode, thereby supplying high energy from the jaws 7 and 8 to the treatment target region. Then, the site to be treated is incised. When it is determined that the blood vessel B to be detected exists in the treatment target region, the control unit 3 operates the energy acting unit 5 in the coagulation mode, whereby low energy is supplied from the jaws 7 and 8 to the treatment target region. As a result, the target site is coagulated.
- the blood flowing in the blood vessel B is removed from the blood vessel B by bleeding. It is clearly distinguished from the leaking blood. Thereby, there exists an advantage that the blood vessel B which exists in the biological tissue A can be detected correctly.
- the average frequency ⁇ ave depends on the thickness of the blood vessel B, not only the presence or absence of the blood vessel B but also the thickness of the blood vessel B can be recognized.
- the control unit 3 displays a display indicating that the blood vessel B to be detected exists to the surgeon. It may be displayed on a display (not shown), or sound may be output from a speaker (not shown). By doing in this way, it can be made to recognize reliably by the surgeon that the blood vessel B to be detected exists in the treatment target region.
- control unit 3 determines that the blood vessel B to be detected exists by the determination unit 14 instead of controlling the intensity of the energy source supplied from the energy supply unit 6 to the energy action unit 5. If the energy supply unit 6 stops supplying the energy source to the energy application unit 5 and the determination unit 14 determines that the blood vessel B to be detected does not exist, the energy supply unit 6 supplies the energy. An energy source may be supplied to the action unit 5. By doing in this way, the effect
- the present embodiment it is determined that there is a thick blood vessel B when the calculated average frequency ⁇ ave is larger than the predetermined threshold value ⁇ th , but as shown in FIG. (Second threshold)
- ⁇ UPth is employed and the average frequency ⁇ ave is equal to or higher than the upper limit threshold ⁇ UPth
- the blood flow determination based on the real-time Doppler spectrum f RT ( ⁇ )
- random noise becomes dominant when the blood flow decreases, and the noise floor cannot be completely removed in the upper step. Therefore, by performing such processing, it is possible to prevent erroneous determination due to random noise that cannot be removed in the upper step.
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Abstract
Description
そして、このようにして算出された計算用スペクトルに基づいて平均周波数が算出される。平均周波数は、血流の速度に応じて大きくなるので、平均周波数に基づいて血管の太さを判断することができる。
このようにすることで、平均周波数が第1の閾値より大きく血流が比較的大きい場合にのみ、血管が存在すると判定することにより、小さい血管のみが存在する部位に対する注意喚起は行われないため、処置をスムーズに行うことができる。
このようにすることで、レーザ光の生体における散乱光強度が低い場合において、平均周波数が第2の閾値より大きくなる場合には、血管が存在しないと判定することにより、小さい血管のみが存在する部位に対する注意喚起が行われないことへの精度が高められるため、処置をよりスムーズに行うことができる。
If>IfCUTの場合、ωave=Iωf/If
If≦IfCUTの場合、ωave=0
本実施形態に係る血管認識用血流測定方法は、図1に示されるように、生体組織Aを処置するエネルギ処置具1と、生体組織A内の血管Bを光学的に検出する血管検出手段2と、該血管検出手段2による検出結果に基づいてエネルギ処置具1を制御する制御部3とを備えるシステムの血管検出手段2において、実施される測定方法である。
光検出部12は、光ファイバ16から入射された散乱光Sの強度をデジタル値に変換し、該デジタル値を周波数解析部13へ順次送信する。
生体組織Aには、図3および図4に示されるように、脂肪や、出血によって血管Bから露出した漏出血液のように静止している静的成分と、血管B内を流動する血液中の赤血球Cのように移動している動的成分とが含まれる。静的成分に周波数fのレーザ光Lが照射されたときには、レーザ光Lと同一の周波数fを有する散乱光Sが発生する。これに対し、動的成分に周波数fのレーザ光Lが照射されたときには、ドップラーシフトによって、レーザ光Lの周波数fからシフトした周波数f+Δfを有する散乱光Sが発生する。このときの周波数のシフト量Δfは、動的成分の移動の速さに依存する。
このような散乱光Sの時系列データを高速フーリエ変換すると、図6Aおよび図6Bに示されるように、血流の速さに応じた周波数ω(以下、周波数シフトΔfをωと記す)に強度を有する実時間ドップラースペクトルfRT(ω)が得られる。
本実施形態においては、まず、実時間ドップラースペクトルfRT(ω)における適当な周波数範囲に規格化領域RNrmを設定する。規格化領域RNrmは、図9に示されるように、所望の血流に対応する実時間ドップラースペクトルfRT(ω)の強度がノイズフロア強度と同程度となる周波数よりも高い周波数に設定される任意の周波数領域である。
また、血流が無い状態でレーザ光Lを照射して取得された散乱光強度から、ノイズフロアおよびスペクトルのみを含む零スペクトルfZERO(ω)を算出しておく(ステップS3)。
そして、規格化された規格化実時間ドップラースペクトルfNrm(ω)から規格化された規格化零スペクトルfzNrm(ω)を減算することにより、図10および図11に示されるように、差分スペクトルfSUB(ω)を算出する(ステップS6)。これにより、ノイズフロアおよび部分的にスパイクノイズが低減された差分スペクトルfSUB(ω)が算出される。
これにより低周波ノイズおよび一部のスパイクノイズを除去した領域スペクトルfrng(ω)が生成される。
ここで、計算用スペクトルの積分値Ifが0であるか否かが判定され(ステップS13)、0である場合には便宜上1に置き換えられる(ステップS14)。これにより、0で除算されることを回避するようになっている。また、計算用スペクトルの積分値Ifが所定の積分カットオフ値IfCUTより大きいか否かが判定され(ステップS15)、判定結果に応じて、以下のように平均周波数が算出される。
If≦IfCUTの場合、ωave=0
このようにすることで、検出対象の血管Bへのエネルギの作用を確実に回避することができる。
L レーザ光
fRT(ω) 実時間ドップラースペクトル
RNrm 規格化領域
fNrm(ω) 規格化実時間ドップラースペクトル
fZERO(ω) 零スペクトル
fzNrm(ω) 規格化零スペクトル
fSUB(ω) 差分スペクトル
frng(ω) 領域スペクトル
RPS PS基準領域
fPS(ω) PS基準スペクトル
fC(ω) 計算用スペクトル
RInt 積分領域
ωave 平均周波数
ωth 平均周波数閾値(第1の閾値)
ωUPth 上限閾値(第2の閾値)
ωPS PS基準周波数
If 計算用スペクトルの積分値
Iωf 計算用スペクトルfC(ω)に周波数ωを乗算したものを積分領域RInt内で周波数ωについて積分したときの積分値
IfCUT 積分カットオフ値
Claims (4)
- レーザ光を生体に照射することにより発生する散乱光強度の時間波形をフーリエ変換して実時間ドップラースペクトルを取得するステップと、
所定の規格化領域における前記実時間ドップラースペクトルの平均値を用いて、該実時間ドップラースペクトルを規格化して規格化実時間ドップラースペクトルを算出するステップと、
血流が無い状態でレーザ光を照射することにより測定した零スペクトルを前記規格化領域における前記零スペクトルの平均値を用いて規格化して規格化零スペクトルを算出するステップと、
前記規格化実時間ドップラースペクトルから前記規格化零スペクトルを減算して差分スペクトルを算出するステップと、
所定の積分領域により前記差分スペクトルから積分する領域を抽出して領域スペクトルを算出するステップと、
所定のPS基準領域における前記領域スペクトルの最大値を前記領域スペクトルから減算してPS基準スペクトルを算出するステップと、
該PS基準スペクトルが負となる要素については0に置き換えて計算用スペクトルを取得するステップと、
該計算用スペクトルに基づいて平均周波数を算出するステップと、
前記算出された平均周波数と所定の閾値とを比較して血流速度を判定するステップとを含む血管認識用血流測定方法。 - 前記算出された平均周波数と所定の閾値とを比較して血流速度を判定するステップは、前記平均周波数が所定の第1の閾値より大きい場合に血管があると判定する請求項1に記載の血管認識用血流測定方法。
- 前記算出された平均周波数と所定の閾値とを比較して血流速度を判定するステップは、前記平均周波数が前記第1の閾値より大きい第2の閾値より小さい場合に血管があると判定する請求項2に記載の血管認識用血流測定方法。
- 前記平均周波数を算出するステップが、所定の積分領域において計算用スペクトルおよび該計算用スペクトルに周波数を乗算したスペクトルの周波数積分値を取得するステップと、所定の積分カットオフ値と前記計算用スペクトルの周波数積分値とを比較するステップと、比較の結果、下式に基づいて平均周波数を設定するステップとを含む請求項1から請求項3のいずれかに記載の血管認識用血流測定方法。
If>IfCUTの場合、ωave=Iωf/If
If≦IfCUTの場合、ωave=0
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JPWO2019189630A1 (ja) * | 2018-03-28 | 2021-04-15 | 京セラ株式会社 | 流量流速算出装置、流量流速センサ装置、流量装置および流量流速算出方法 |
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