CN104207767B

CN104207767B - Bloodstream measurement device and use the cerebration measurement apparatus of this bloodstream measurement device

Info

Publication number: CN104207767B
Application number: CN201410411635.0A
Authority: CN
Inventors: 山海嘉之
Original assignee: JAPAN GOVERNMENT
Current assignee: JAPAN GOVERNMENT
Priority date: 2009-07-14
Filing date: 2009-07-14
Publication date: 2016-06-22
Anticipated expiration: 2029-07-14
Also published as: CN101953683B; CN101953683A; HK1151709A1; CN104207767A

Abstract

A kind of cerebration measurement apparatus, the control portion of the detection signal measurement cerebration state of the light therethrough amount there is the bloodstream measurement device being mounted to head, measuring according to this bloodstream measurement device and the measurement result that this control portion exports is delivered to the first radio communication device of external device (ED)。This bloodstream measurement device be provided with multiple by the base portion irradiation light of hat-shaped to form the sensor unit of light-guide wave path。Data administrator have receive the blood flow measurement data sent from the first radio communication device the second radio communication device, preserve the data base of the blood flow measurement data that this second radio communication device receives, according to the measurement data image display control apparatus of this blood flow measurement data genaration view data and the display showing this view data。

Description

Bloodstream measurement device and use the cerebration measurement apparatus of this bloodstream measurement device

The application be same applicant in the application number that on July 14th, 2009 submits to be 200910152286.4, denomination of invention be the divisional application of Chinese patent application of " bloodstream measurement device and use the cerebration measurement apparatus of this bloodstream measurement device "。

Technical field

The present invention relates to a kind of bloodstream measurement device and use the cerebration measurement apparatus of this bloodstream measurement device, this cerebration measurement apparatus is configured to, it is possible to the impact of the oxygen saturation concentration not being contained within by blood, exactly the supply condition of blood is measured。

Background technology

As the device to blood flowing measurement, such as, there is a kind of cerebration measurement apparatus, its probe (Probe) being formed into light-guide wave path is arranged on head, by cerebral blood flow is measured, the image of cerebration state is shown over the display (such as, with reference to Japanese documentation 1---" JP 2003-149137 publication ")。

It addition, also have a kind of device as cerebration measurement apparatus, this device has: light source, and it is for carrying out light irradiation to raw body；Photo measure unit, it comprises light transferring and receiving apparatus, and this light transferring and receiving apparatus is for detecting the light of multiple wavelength that raw body sends；Rheological parameters' change with time measuring unit, its change according to the transit dose of the light of multiple wavelength, obtain the rheological parameters' change with time of the special component that blood is contained within；Blood flow computing unit, it is according to the ratio in the rheological parameters' change with time of special component and the blood of special component, calculates blood flow (such as, with reference to Japanese documentation 2---" JP 2003-144401 publication ")。In above-mentioned patent documentation 1 and 2, multiple illuminating parts and multiple light accepting part are arranged on head, by applying the transit dose of light that the detection of near infrared ray optical spectroscopy is propagated in brain, the device that the active state of brain function carries out mapping process is also referred to as " light pattern (topography) " device。

Additionally, as the bloodstream measurement device that the blood flow beyond brain is measured, also have a kind of by blood layer is carried out light irradiation, then the transit dose of light is measured, to detect the device (with reference to Japanese documentation 3---" JP 2002-345787 publication ") whether in blood with thrombosis。

The device recorded in above-mentioned patent documentation 1-3, in the method using the illuminating part being formed as light-guide wave path and light accepting part that blood flow is measured, measurement object is through the change of the transit dose of the light of blood, rather than responds cerebration and carry out the erythrocytic amount or the density (hematocrit: hematocrit value) that change。On the other hand, the haemachrome (hemoglobin:Hb) contained in erythrocyte has and light is absorbed and the character of scattering and reflection, it addition, the impact that its optical characteristics is subject to the Hb density in blood, oxygen saturation and optical path length is also well-known。So, in using photo measure unit as above method that blood flow is measured, measurement result can be subject to the impact of haemachrome that erythrocyte is contained within and oxygen saturation (amount of oxygen delivered by erythrocyte) the two condition and change。

Therefore, if the oxygen saturation in blood is certain, then can be appropriately carried out measurement blood carried out according to the light therethrough amount based on erythrocytic amount or density (hematocrit value), but, if the activity of brain or muscle causes zmount of oxygen consumption to increase or reduces, then oxygen partial pressure (PaO2) can cause that oxygen saturation changes, simultaneously, oxygen saturation can cause that again light absorption changes, so, the variation of the light therethrough amount that oxygen saturation causes is likely to the change being mistakenly detected as blood flow。

When the endovascular blood to brain or muscle offer blood is measured by the measurement apparatus using above-mentioned patent documentation 1-3, if the activity of brain or muscle enlivens, then the oxygen partial pressure in blood will change, so, because the change of oxygen partial pressure can cause oxygen saturation change, so, in such a case it is difficult to exactly the active state of brain or muscle is measured。

It addition, when cerebration is enlivened, the zmount of oxygen consumption in brain also can increase, so, countless blood capillaries will provide blood to brain。So, measure and be actually the measurement that the blood in the preset range that there is multiple blood capillary is carried out by the size (being formed as the diameter of the probe of light-guide wave path) according to sensor。But, in existing blood measuring apparatus and cerebration measurement apparatus, the different blood of oxygen saturation is when multiple blood capillary Bottomhole pressure, owing to oxygen saturation is different, the light therethrough amount detected is also different, so, in this case, it is also difficult to exactly cerebration state is measured。

Additionally, when endovascular blood flow beyond brain is measured, if the oxygen saturation in blood is different, the factor of erythrocytic amount or density (hematocrit value) and oxygen saturation these two aspects all can cause that light therethrough amount changes, so, in this case, it is also difficult to correctly blood flow is measured。

Summary of the invention

The present invention proposes in view of above-mentioned problem, its object is to, it is provided that a kind of bloodstream measurement device that can solve the problem that above-mentioned problem and use the cerebration measurement apparatus of this bloodstream measurement device。

In order to solve above-mentioned problem, the present invention has technological means as described below。

The bloodstream measurement device of the present invention has: sensor unit, and it comprises illuminating part and light accepting part, and this illuminating part is for measured region irradiation light, and this light accepting part is for accepting to propagate the light of (propagate) in described measured region；Control portion, the blood flow state of measured region is measured by it according to the signal exported by described light accepting part；Wherein, it is arranged on light accepting part described at least two on the position different from the distance of described illuminating part and accepts the light that described illuminating part sends, described control portion, by carrying out the computing that the composition to the oxygen saturation contained in the signal obtained from described at least two light accepting part is cancelled, carrys out the blood flow state to described measured region and measures。

Additionally, in the described bloodstream measurement device of the present invention, described illuminating part sends the first light and the second light, described first light has the wavelength being difficult to be affected its optical characteristics by the oxygen saturation in blood, and described second light has the wavelength being affected its optical characteristics by the oxygen bag in blood and degree。

Additionally, in the described bloodstream measurement device of the present invention, the first light therethrough amount when described control portion is by receiving described first light by described light accepting part compares with the second light therethrough amount when receiving described second light, and the blood flow state of described measured region is measured。

It addition, in the described bloodstream measurement device of the present invention, the described control portion measurement data according to the described first, second light therethrough amount exported based at least said two light accepting part, the blood flow state of described measured region is measured。

Additionally, in the described bloodstream measurement device of the present invention, described sensor unit has light path separating component, this light path separating component is configured to, to from the refractive index of the light of measured region described in described illuminating part directive to different from the refractive index of the light of light accepting part described in described measured region directive；Described illuminating part and described light accepting part carry out emission of light and reception via described light path separating component。

It addition, the cerebration measurement apparatus of the present invention is by using described bloodstream measurement device that brain blood flow is measured, and according to the result that described bloodstream measurement device is measured, the active state of described brain is measured。

Additionally, in the described cerebration measurement apparatus of the present invention, different positions is provided with multiple described sensor unit, described control portion makes the light from light source of a sensor in the plurality of sensor, and detect the light therethrough amount received by light accepting part of sensor described at least two arranged on the position different from the distance of one sensor, then the measurement data according to the described first, second light therethrough amount exported based on said two light accepting part, measures the cerebration state of described measured region。

Additionally, in the described cerebration measurement apparatus of the present invention, described control portion makes all described illuminating part of the plurality of sensor unit sequentially luminous, and detect the light intensity that the light accepting part of sensor described at least two arranged on the position different from the distance of described luminescence sensor unit receives, then the measurement data according to the described first, second light therethrough amount exported based on said two light accepting part, measures the cerebration state of described measured region。

It addition, in the described cerebration measurement apparatus of the present invention, described sensor unit has the E.E.G for brain wave (that is: E.E.G) and measures electrode。

It addition, in the described cerebration measurement apparatus of the present invention, described E.E.G measures the side that electrode is formed on the first end face of described light path separating component。

According to the present invention, its effect is in that, received from light accepting part more than illuminating part at least two on different positions because the light that illuminating part sends is arranged on, then further according to the signal obtained from light accepting part more than described at least two, the blood flow state of measured region is measured, therefore, the composition of the oxygen saturation contained from the signal that light accepting part more than said two is obtained can be cancelled out each other, so, just can according to the signal based on the erythrocytic V/V contained in the blood of flowing in measured region, the state of blood flow and cerebration is measured accurately。

Accompanying drawing explanation

Fig. 1 is the system pie graph of an embodiment of the cerebration measurement apparatus of the bloodstream measurement device using the present invention。

Fig. 2 A is the longitdinal cross-section diagram that the installment state of sensor unit 24 is amplified display。

Fig. 2 B is the longitdinal cross-section diagram of the variation of sensor unit 24。

Fig. 3 is an illustration for the schematic diagram of blood flow measurement side's ratio juris。

Fig. 4 be optical maser wavelength and change in blood oxygen saturation time light absorption state between graph of a relation。

Fig. 5 is the schematic diagram from left sides brain。

Fig. 6 is an illustration for the schematic diagram of principle when cerebration being measured according to cerebral blood flow。

Fig. 7 is an illustration for the control portion 30 of cerebration measurement apparatus 100 and performs the flow chart of cerebral blood flow measurement processing。

Fig. 8 is an illustration for the measurement data image display control apparatus 80 of data administrator 50 and performs the flow chart that measurement data image display processes。

Fig. 9 A is the view before the measurement of shoulder motor region 352 and elbow motor region 354。

Fig. 9 B is the schematic diagram according to the view data wanting measurement data during carry arm obtained。

Fig. 9 C is the schematic diagram according to the view data wanting measurement data when toggle carry arm obtained。

Figure 10 A is the schematic diagram of the propagation path of the light that illuminating part 120 sends。

Figure 10 B indicate that the light that illuminating part 120 sends just irradiate after (elapsed time t1), along the longitdinal cross-section diagram of line A-A。

Figure 10 C indicates that the light that illuminating part 120 sends has irradiated longitdinal cross-section diagram after time t2, along line A-A。

Figure 10 D indicates that the light that illuminating part 120 sends has irradiated longitdinal cross-section diagram after time t3, along line A-A。

Figure 11 A is the schematic diagram of the installment state of the variation 1 of cerebration measurement apparatus。

Figure 11 B is the composition block diagram of each parts of variation 1。

Figure 12 is the schematic diagram of the installment state of the variation 2 of cerebration measurement apparatus。

Figure 13 is the schematic diagram of the installment state of the variation 3 of cerebration measurement apparatus。

Figure 14 is the longitdinal cross-section diagram of the variation of sensor unit。

The summary that Figure 15 is the bloodstream measurement device of embodiment 2 constitutes system diagram。

Figure 16 is the longitdinal cross-section diagram of the composition of the sensor unit 820 of embodiment 2。

The summary that Figure 17 is the bloodstream measurement device of embodiment 3 constitutes system diagram。

Primary symbols illustrates:

10: cerebration measures system；20,800: bloodstream measurement device；22: base portion；22A: netted base portion；24 (24₁-24n), 24A-24C, 24A-24An, 24B1-24Bn ..., 24N1-24Nn, 24X, 700,820,930: sensor unit；30,830,940: control portion；40,60: radio communication device；50: data administrator；70: data base；80: measurement data image display control apparatus；90: display；100,100A-100C: cerebration measurement apparatus；120,950: illuminating part；130,960,962: light accepting part；140,720: light path separating component；150,710: E.E.G measures electrode；160,500,600: flexible wiring；170: propagation path of light；180: blood vessel；220: head surface；230: blood layer；240: erythrocyte；300: brain；301: brain；302: cerebellum；303: brain stem；400A-400N: radio communication device；810: hemodialysis's device；812: Dialysis tubing；860: holding member；870,880: sensor part；872: the first illuminating parts；874,876,884,886: first to fourth light accepting part；882: the second illuminating parts；900: bloodstream measurement device；910: skin surface；920: measurement portion；924: measuring surface；970: light path separating component；980: display。

Detailed description of the invention

The preferred forms of the present invention is described below with reference to accompanying drawing。

[first embodiment]

Have as it is shown in figure 1, cerebration measures system 10: cerebration measurement apparatus 100；Data administrator 50, it is for managing the data measured by cerebration measurement apparatus 10。In addition, it is necessary to illustrate, illustrate only the schematic diagram of the head side of cerebration measurement apparatus 100 in Fig. 1, the opposite side of the cerebration measurement apparatus 100 being positioned at the paper back side also has identical composition。

Cerebration measurement apparatus 100 has: bloodstream measurement device 20, it is arranged on head；Control portion 30, brain activity state (erythrocytic distribution) is measured by it according to the detection signal of the light therethrough amount measured by bloodstream measurement device 20；Radio communication device 40, the measurement result (blood flow data) that control portion 30 is exported by it in the way of radio communication sends to external device (ED)。

Preserving control program in control portion 30, this control program is used for performing computing (with reference to computing formula described later), and this computing is the composition for cancelling the oxygen saturation contained from the signal that light accepting part described at least two obtains。

Multiple optical sensor unit 24 (24 it is configured with in bloodstream measurement device 20₁-24n), sensor unit 24 is by forming light-guide wave path to base portion 22 irradiation light of medicated cap type。In the present embodiment, because the diameter of sensor unit 24 is about 10mm-50mm, so, in the base portion 22 of semi-spherical shape, it is possible to according to predetermined configuration mode (predetermined interval), about 150-300 sensor unit 24 is installed。Multiple sensor units 24 are managed by address date respectively, and this address date is to have carried out corresponding data with the position of measuring measuring object in advance。The measurement data obtained from each sensor unit 24 is together sent out with each address date, and is saved。

In addition, it should be noted that multiple sensor units 24 (24₁-24n) the matrix shape that is preferably arranged according to certain intervals of configuration mode, but, because the nose shape of measured body also differs, and, the size of head and curve form are also diversified, so, it is also possible to sensor unit 24 is configured at irregular intervals。

It addition, cerebration measurement apparatus 10 has the radio communication device 40 as output unit。In the present embodiment, radio communication device 40 uses with data administrator 50 combination, this data administrator 50 is for being managed the blood flow measurement data transmitted by radio communication device 40, but it is also possible to these blood flow measurement data to be sent to other external device (ED)s (such as: as the device of control object of electronic installation or actuator (actuator) etc. of PC etc.)。

Data administrator 50 has: radio communication device 60, and it is for receiving the blood flow measurement data that radio communication device 40 transmits；Data base 70, and it is for preserving the blood flow measurement data obtained from radio communication device 60；Measurement data image display control apparatus 80, it is for according to the blood flow measurement data genaration view data provided by data base 70；Display 90, it is for showing the view data of the measurement result generated by measurement data image display control apparatus 80。

It addition, because radio communication can be carried out with cerebration measurement apparatus 100, so, data administrator 50 can also be arranged on the place away from cerebration measurement apparatus 100, for instance, it is possible to it is disposed at the place that the measured be can't see。

Fig. 2 A is the amplification display figure of the installment state of sensor unit 24。

It should be noted that state when sensor unit 24A, 24B, 24C of being shown that in Fig. 2 A in multiple sensor unit 24 being configured are mounted。As shown in Figure 2 A, each sensor unit 24A, 24B, 24C are inserted in the installing hole 26 of the base portion 22 with flexual semi-spherical shape, and the agent that gets adhered etc. is fixing。So, each sensor unit 24A, 24B, 24C are kept in the installing hole 26 of base portion 22 by being fixed on, so that its first end portion contacts with the head surface of the measured。It addition, the composition of each sensor unit 24A, 24B, 24C is identical, and, it is endowed identical symbol in identical position。

Sensor unit 24 has: illuminating part 120, and it is made up of laser diode, and this laser diode is used for head surface 220 irradiating laser (transmitting light) A；Light accepting part 130, it is made up of photo detector, and this photo detector is for exporting the signal of telecommunication corresponding with the light therethrough amount received；Light path separating component 140, it is made up of hologram (hologram), this hologram is configured to, and the refractive index of its laser A to being pointed into measured region by illuminating part 120 is different to the refractive index through measured scope incident illumination B, C of being incident to light accepting part 130。

It addition, the E.E.G for measuring E.E.G has been inlayed in the periphery of light path separating component 140 measures electrode 150, E.E.G is measured electrode 150 and is formed cylindrical shape, and is formed on the side of the first end face of light path separating component 140。The Wiring pattern (pattern) of upper end and flexible wiring 160 that E.E.G measures electrode 150 is electrically connected。

The upside of illuminating part 120 and light accepting part 130 is by the actual load downside at flexible wiring 160。Flexible wiring 160 is formed the Wiring pattern being connected with control portion 30。The position corresponding with each sensor unit 24 in Wiring pattern, by scolding tin etc., is electrically connected with illuminating part 120 and light accepting part 130。In addition, it is necessary to illustrate, the shape of measured body head when flexible wiring 160 can contact with measured region according to the tip of sensor unit 24 deforms, so, when installation and removal operation, will not break。

Measuring in electrode 150 at E.E.G, the contact probe head 152 that tip bends to the inside also highlights than the end face of light path separating component 140。So, when the end face of light path separating component 140 contacts with measured region, contact probe head 152 also can contact with this measured region, and E.E.G is measured。It addition, E.E.G measurement electrode 150 can also be adopted and be formed with the following method, it may be assumed that by plating the thin film generation type of gas or plating etc., at the periphery of light path separating component 140 and first end edge portion coating conducting film。It addition, measure the material of electrode 150 as E.E.G, for instance, it is possible to formed by the nesa coating being referred to as made by the tin indium oxide of ITO (IndiumTinOxide) in the periphery of light path separating component 140 and first end edge portion。When being formed E.E.G measurement electrode 150 by this nesa coating, because E.E.G is measured electrode 150 and is had light transmission, so, it is possible to wave measurement electrode 150 of requiring mental skill is to cover the whole periphery of light path separating component 140 and first end face。

It addition, in general, when carrying out brain tomography (scanning), it is impossible to also blood flow state and E.E.G are measured simultaneously。But, by arranging electrode 150 on sensor unit 24, it is possible to measure blood flow and E.E.G, it is also possible to the dependency relation between cerebral blood flow and E.E.G is carried out detailed analysis simultaneously。

When carrying out blood flow measurement, control portion 30 selects any one sensor unit 24 from the multiple sensor units 24 arranged, and makes the illuminating part 120 of this sensor unit 24 send laser A。Now, the laser that illuminating part 120 sends is output with the wavelength X (λ is about 805nm) not affected by oxygen saturation。

It addition, each sensor unit 24 is retained as the state that its tip (end face of optical path separator material 140) contacts with the measured region of measured body head。The laser A penetrated by illuminating part 120 passes through light path separating component 140, along the direction incidence in brain being perpendicular to head scalp。In brain, laser A with incoming position for basic point, propagates along brain surface while advancing to brain center towards periphery。From the side, laser A propagation path of light 170 in brain is circular arc, after head blood vessel 180, is returning scalp surface 220。

Through the light of above-mentioned propagation path of light 170, its transit dose is changed with the erythrocytic amount contained in the blood of flowing in blood vessel 180 or density, while arriving on sensor unit 24B, 24C of sensitive side。It addition, because the transit dose of laser A is gradually reduced with laser A propagation in brain, so, laser A from basic point (incoming position) more away from, then the light grade of light accepting part 130 proportionally declines with distance。So, the transit dose of the light received also leaves the distance of incoming position according to laser A and changes。

In fig. 2, if will be located in the sensor unit 24A of left end as emission side basic point, then sensor unit 24A itself, its right neighbour sensor unit 24B and, the sensor unit 24C of the right neighbour of its right neighbour constitute sensitive side basic point (measurement point)。

Light path separating component 140 such as can pass through the mode making the Density Distribution of transparent acrylic resin change, and makes laser A straight ahead, and is formed, it is possible to incident illumination B, C import the structure of light accepting part 130。It addition, light path separating component 140 has: emitting side passes through field 142, and it makes the laser A that illuminating part 120 sends pass through from base end side (upside Fig. 2 A), and is incident to tip side (downside in Fig. 2 A)；Light incident side passes through field 144, and it makes the light propagated in brain pass through from first side (downside Fig. 2 A), and is incident to base end side (upside in Fig. 2 A)；Refraction field 146, it is formed and passes through between field 144 through field 142 and light incident side at emitting side。This refraction field 146 makes laser A pass through, but, also there is the character making the light (incident illumination B, C) passing through blood flow reflect。Refraction field 146 such as can arrange by making the density of allyl resin change, in this field metallic film or, make the mode of metal microparticle dispersion etc. be formed。So, light accepting part 130 just can be all collected to from the light that the tip of light path separating component 140 is incident。

Fig. 2 B is the schematic diagram of the variation of sensor unit 24。

As shown in Figure 2 B, in the sensor unit 24X of variation, the lower end of light path separating component 140 is provided with diffraction lattice 190。The lower side edge of diffraction lattice 190 by E.E.G measure electrode 150, contact probe head 152 that tip bends to the inside keeps。Diffraction lattice 190 is configured to, the back side and be formed with fine convex-concave pattern on surface, from the light of head surface 22 incidence by the boundary member of this convex-concave pattern time, be refracted to light accepting part 130 according to diffraction。

Below, blood flow measurement side's ratio juris is illustrated。

As shown in Figure 3, if externally to blood illuminator laser A, then be incident to the laser A of blood layer 230 as by general erythrocyte 240 launched the light component with scattering and, reflected by the thrombosis paid and two kinds of compositions of light component of scattering through blood and are advanced。

Light influence in through blood layer process ceaselessly changes according to the state of blood, so, by measuring the transit dose (emission measure of light can also) of light continuously, and observe the change of its light quantity, it is possible to observe the change of various blood properties。

After cerebration is active, the zmount of oxygen consumption in brain will increase, so, the state of the blood flow caused by the oxygen saturation of the erythrocytic hematocrit value of delivery oxygen and blood, just become the change of light quantity, and be represented。

Here, hematocrit value (Hct: the erythrocytic volume ratio of representation unit volume, it may be assumed that the erythrocytic volumetric concentration of unit volume。Can also represent with Ht。) etc. change also to the relevant factor of change of haemachrome density, affect the change of light quantity。Rationale here is that of the present embodiment, as it has been described above, use laser A according to the change of the light path light therethrough amount produced by blood flow, blood flow state to be measured, further, measures cerebration state according to the blood flow state in brain。

Below, inventive feature is illustrated by constituting in its principle。The optical characteristics of blood is determined by blood cell composition (particularly the haemachrome of erythrocytic cell interior)。It addition, because haemachrome has the character being easily combined with oxygen, so, erythrocyte can also play the effect delivering oxygen to brain cell。The numerical value that the percent of the haemachrome that the oxygen saturation of blood is used to indicate that in blood be how many and oxygen has combined。It addition, oxygen saturation is relevant to the oxygen partial pressure (PaO2) in arterial blood, it it is the important indicator of respiratory function (gas exchange)。

It is known that if oxygen partial pressure is high, then oxygen saturation also uprises。If oxygen saturation changes, then through the transit dose also change of the light of blood。So, when performing blood flow measurement, by removing the impact of oxygen saturation, it is possible to measure more accurately。

Additionally, alveolar ventilation amount is also had, the factor of the gas exchange etc. in the further alveolar also having the environment of atmospheric pressure or oxygen intake concentration (FiO2) etc., ventilation/blood flow ratio or diffusibility of gases, short circuit ratio etc. as the factor that oxygen partial pressure (PaO2) is produced impact。

Control portion 30 has computing unit, and for performing the process of signal, this signal is the signal that light therethrough amount (light intensity) that the light accepting part 130 with the sensor unit 24A, 24B, 24C generates is corresponding。In this computing unit, as described later, computing blood flow state measured for the measured value exported according to the light accepting part 130 of sensor unit 24B, 24C is performed。

The laser A of illuminating part 120 is pulse laser or the continuous laser of (such as, 10Hz-1MHz) intermittent irradiation at predetermined intervals。When a pulsed laser is used, the irradiation determining pulse laser according to velocity of blood flow and the frequency do not irradiated are (namely, blinking frequency), and continuously or, with more than this blinking frequency twice measurement sample (sampling) frequency measurement。It addition, when using continuous laser, determine measurement sample frequency according to velocity of blood flow, with measurement。

Haemachrome (Hb) in blood becomes HbO2 with oxygen generation chemical reaction by breathing in lung, oxygen is taken in blood, but, due to breathing state etc., the degree (oxygen saturation) of the oxygen being ingested in blood there is also delicate difference。That is: in the present invention, after blood illuminator light, it was found that this oxygen saturation can cause the phenomenon that light absorption changes。Due to this phenomenon be above-mentioned use laser A to carry out the unfavorable factor in blood flow measurement, so, invention removes the impact of oxygen saturation。

Fig. 4 is the graph of a relation between light absorption state when optical maser wavelength and the oxygen saturation changing blood。

In vivo, haemachrome contained in erythrocyte is divided into two kinds, and as shown in Figure 4, a kind of is the oxidized heme (HbO2: curve II) combined with oxygen, and another kind is the haemachrome (Hb: curve I) not being combined with oxygen。Under both states, there is very big difference in the absorbance of light。Such as, the blood rich in oxygen is the blood that color is fresh, and venous blood is because releasing some blackout of its color of oxygen。As shown in the curve I, II of Fig. 4, the state of these light absorption is changed in wider wave-length coverage。

Select specific wavelength that blood is irradiated according to the curve I, II in Fig. 4, both the oxygen saturation that raw internal oxygen metabolism etc. result in the haemachrome in erythrocyte had been made to there occurs very big variation, light absorption can also be unaffected, and blood flow is measured accurately。

Unrelated with the oxygen saturation of the haemachrome in erythrocyte, in certain wave-length coverage, light absorption is less。In this manner it is possible to determine that whether light is easily by blood layer according to wavelength X。Therefore, if using the light of predetermined wavelength range (such as, wavelength X range from about 800nm-1300nm) to irradiate, it is possible to oxygen saturation is controlled to minimum, and on this basis blood flow is measured。

Therefore, the wave-length coverage of the laser A used in the present invention is about 600nm-1500nm。Within the scope of this, the light absorption of haemachrome (Hb) is very little in actual applications, further, within the scope of this, isobestic point X is also comprised, so, the measurement point of more than 2 wavelength can be efficiently used, and, computationally, it is regarded as isobestic point, it may be assumed that the method that can obtain not affected by oxygen saturation。But, it should be noted that, in other wave-length coverages, when wavelength X is less than 600nm, light absorption uprises, and S/N declines, when wavelength X is more than 1500nm, the light reception sensitivity of light accepting part 130 is not enough, the impact of the unfavorable factor of other compositions etc. that can be subject in blood, it is impossible to carry out high-precision measurement。

Therefore, in the present embodiment, illuminating part 120 uses the light-emitting component being made up of variable wavelength semiconductor laser generator, and the wavelength of the laser A sent by illuminating part 120 is set as two kinds: a kind of is the wavelength X 1=805nm (the first light) corresponding to isobestic point X on curve I, II；Another kind is the wavelength X 2=680nm (the second light) corresponding to minimum light absorption on curve I。

Below, the detection method of erythrocyte concentration R, Rp, Rpw is illustrated, and this detection method is based on the detection method of the erythrocyte concentration R of light therethrough amount when receiving the laser A light propagated via propagation path of light 170 (with reference to Fig. 2), Rp, Rpw。

That existing measuring method adopts, use the computing formula of erythrocyte concentration R during 1 wavelength as follows:

R=log10 (Iin/Iout)=f (Iin, L, Ht) ... (formula 1)

In the method for above-mentioned formula 1, erythrocyte concentration R be distance (optical path length) L between the transit dose Iin of the incident illumination of the laser A that illuminating part 120 sends, illuminating part 120 and light accepting part 130 and, the function of aforementioned hematocrit value (Ht)。So, in the method for above-mentioned formula 1, when calculating erythrocyte concentration, erythrocyte concentration is changed by the impact of three factors, and therefore, it is very difficult to accurately measure erythrocyte concentration。

That the present embodiment adopts, use the computing formula of erythrocyte concentration Rp during two one wavelength modes as follows:

Rp=log10{Iout/ (Iout-Iout) }=Φ (L, Ht) ... (formula 2)

In the method for above-mentioned formula 2, as shown in Figure 2, because being receive light at two points (light accepting part 130 of sensor unit 24B, 24C) place that the distance from laser A is different, so, erythrocyte concentration Rp is the distance L between two light accepting parts 130 and the function of aforementioned hematocrit value (Ht)。So, in the method for above-mentioned formula 2, when calculating erythrocyte concentration, one of them in two factors is the distance L between light accepting part 130 is the constant known in advance, so, it is possible to only erythrocyte concentration is measured as coefficient using hematocrit value (Ht)。Therefore, in the method for above-mentioned formula 2, it is possible to calculate erythrocyte concentration exactly, it may be assumed that this erythrocyte concentration is the measured value corresponding with hematocrit value (Ht)。

It addition, the computing formula of erythrocyte concentration Rpw when using two the two wavelength mode of variation of the present embodiment is as follows:

Rpw=[log10{Iout/ (Iout-Iout) } λ 1]/[log10{Iout/ (Iout-Iout) } λ 2]=ζ (Ht) ... (formula 3)

In the method for above-mentioned formula 3, the wavelength of the laser A by being sent by illuminating part 120 is set as that different λ 1, λ 2 is (in the present embodiment, λ 1=805nm, λ 2=680nm), it is possible to erythrocyte concentration Rwp is measured as the function being only hematocrit value (Ht)。Therefore, the method using above-mentioned formula 3, it is possible to correctly measure erythrocyte concentration, it may be assumed that this erythrocyte concentration is the measured value corresponding with hematocrit value (Ht)。

Below, the brain as measured region is illustrated。

Fig. 5 is the schematic diagram from left sides brain。

As it is shown in figure 5, the brain 300 of the mankind is made up of brain 301, cerebellum 302, brain stem 303。Brain 301 is the maincenter controlling human motion function, cerebral cortex be divided into each position with human body (hands, elbow, shoulder, waist, knee joint, ankle each joint etc.) corresponding each motor region。Such as, brain 301 has sinciput proparea 330, front motor region 340, motor region 350, somatosensory area 360 etc.。It addition, brain 301 has front top ocular movement district 332, language district (Broca district) 334, olfactory region 336, front motor region 340 has Motion-Joint district 342。

It addition, motor region 350 is the region for controlling human limb motion, for instance, there is shoulder motor region 352, elbow motor region 354。So, by measuring the blood flow of shoulder motor region 352, elbow motor region 354, the blood flow change in each region is carried out mapping process, it is possible to detect which type of motion shoulder or ancon are feeling like doing。

As shown in Figure 6, brain 300 is covered by medullary substance 400, skull 410, scalp 420。Each sensor unit 24 contacts, with scalp 420, the measurement carrying out blood flow by making the first end face of light path separating component 140。The laser A that the illuminating part 120 of sensor unit 24A sends, through scalp 420, skull 410, medullary substance 400, advances to the inside of brain 300。Further, it is pointed into the light of the head arc-shaped pattern 440 shown in the dotted line in Fig. 6 to propagate along radiation direction (depth direction and radial direction)。

In above-mentioned light is propagated, it is more remote that laser leaves, along radial direction, the distance irradiating basic point 450, light propagation path is more long, light penetration is also more low, so, with the sensor unit 24A predetermined distance of emission side and the light grade (light therethrough amount) of sensor unit 24B that is disposed adjacent is relatively strong, and with sensor unit 24B predetermined distance and the light grade (light therethrough amount) more weak (the light grade less than sensor unit 24B) of sensor unit 24C that is disposed adjacent。It addition, the light accepting part of the sensor unit 24A of emission side also receives the light from brain 300。By the detection signal corresponding with the light intensity of the light received by these sensor units 24 is carried out mapping process, it is possible to obtain the figure (equal pitch contour) of the light intensity corresponding with blood flow change。

Additionally, by detection signal (signal corresponding with the light therethrough amount received) that each sensor unit 24 is exported as the Iout in aforementioned formula 2 and formula 3, just can accurately measuring erythrocyte concentration, this erythrocyte concentration corresponds to the measured value of hematocrit value (Ht)。

Below, with reference to Fig. 7, the measurement processing of the brain blood flow practiced by the control portion 30 of cerebration measurement apparatus 100 is illustrated。

Fig. 7 is an illustration for the control portion 30 of brain activity measurement apparatus 100 and performs the flow chart of brain blood flow measurement processing。

As shown in Figure 7, cerebral cortex is divided into the measured zone of each motor region by control portion 30, carry out blood flow measurement process again, for instance, can to sinciput proparea 330, front motor region 340, motor region 350, somatosensory area 360 each measured zone blood flow measurement process carry out parallel processing。

Below, for instance, when performing the blood flow measurement of motor region 350, illustrate for the situation that the active state of motor region 350 is carried out mapping process。

First, control portion 30 selects any one sensor unit 24A (sensor unit of address number n=1) in the step S11 of Fig. 7 from multiple sensor units of configuration, and makes the illuminating part 120 of this sensor unit 24A to measured region (comprising the head zone of motor region 350) irradiating laser。Then, in step s 12, the detection signal (signal of telecommunication corresponding with the light therethrough amount received) exported by the light accepting part 130 of the sensor unit 24B of the n=n+1 adjacent with address number n=1 is sent to data administrator 50 from radio communication device 40。In data administrator 50, the data of the n=n+1 obtained from radio communication device 60 are preserved to data base 70。

In next step S13, the detection signal (signal of telecommunication corresponding with the light therethrough amount received) that the light accepting part 130 of the sensor unit 24C of the n=n+2 adjacent with address number n=n+1 exports is sent to data administrator 50 from radio communication device 40。In data administrator 50, the data of the n=n+2 obtained from radio communication device 60 are saved to data base 70。

So, detection signal that be basic point with the sensor unit 24A that sends laser A, that be arranged in all the sensors 24 about is just all transferred into data administrator 50。

Then, in step S14, it is n+1 using the address change of the sensor unit as luminous point。In next step S15, check whether all of sensor unit 24 is all luminous。In step S15, the luminescence if all of sensor unit 24 has not been completed, and makes the illuminating part 120 of the sensor unit 24B of above-mentioned n+1 send laser A the process of repeated execution of steps S11 to step S15。

It addition, in step S15, the luminescence if all of sensor unit 24 is completed, it is possible to the blood flow measurement terminating this measured zone processes, or, this measured zone is started anew again performs above-mentioned blood flow measurement again and processes。

Below, with reference to Fig. 8 the measurement data image display practiced by the measurement data image display control apparatus 80 of data administrator 50 processed and illustrate。

The measurement data (data of the light therethrough amount corresponding with blood flow) that measurement data image display control apparatus 80 preserves in reading database 70 in the step S21 of Fig. 8。Then, enter step S22, by using measurement data and above-mentioned formula 1 or formula 2, calculate erythrocyte concentration Rp or Rpw。

In next step S23, generate the scattergram (line chart represented with equal pitch contour) of each erythrocyte concentration measuring point, the view data of this scattergram is preserved to data base 70。Then, enter step S24, check whether the calculating of all erythrocyte concentration Rp or Rpw measuring point is complete。In step s 24, if the calculating of all erythrocyte concentration Rp or Rpw measuring point has not been completed, then return above-mentioned steps S21, repeat from the S21 process started。

It addition, in step s 24, if the calculating of all erythrocyte concentration Rp or Rpw measuring point is all complete, then enters step S25, would indicate that the cerebration state diagram of erythrocyte CONCENTRATION DISTRIBUTION is shown on display 90。

So, by calculating erythrocyte concentration Rp or Rpw according to the measurement data corresponding with the blood flow measured by cerebration measurement apparatus 100, cerebration state based on erythrocyte concentration is shown on display 90, it is possible to confirm measured region ground cerebration state exactly。

Below, the display example as the view data of the measurement result of cerebral blood flow (erythrocyte concentration) obtained by analyzing the measurement data transmitted by cerebration measurement apparatus 100 in measurement data image display control apparatus 80 is illustrated。

Fig. 9 A is the schematic diagram of the state before the measurement of shoulder motor region 352 and elbow motor region 354。

As shown in Figure 9 A, there is the interior convulsion region 352a and outer convulsion region 352b of shoulder joint in the shoulder motor region 352 (region represented by dotted line) of brain 300, there is the flexing muscle region 354a of elbow joint in elbow motor region 354 (region represented by dotted line) and stretch muscle region 354b。

As shown in Figure 9 B, for instance, when brain 300 wants to lift arm, centered by the interior convulsion region 352a takeing on motor region 352 and outer convulsion region 352b, as equal pitch contour, the view data of zone of action 360 is generated, and be displayed on display 90。In the view data of this zone of action 360, closeer part represents that light intensity is relatively strong, blood flow is more, and the part relatively dredged represents that light intensity is more weak, blood flow is less。Therefore, from figure shown in Fig. 9 B it can be seen that when take on the interior convulsion region 352a of motor region 352, outer convulsion region 352b cerebration enliven time, it is meant that its sending act arm instruction。

As shown in Figure 9 C, such as, when brain 300 want toggle develop simultaneously arm time, centered by the flex region 354a of the interior convulsion region 352a takeing on motor region 352, outer convulsion region 352b and elbow motor region 354, as equal pitch contour, the view data of zone of action 370 is generated, and be displayed on display 90。In this zone of action 370, closeer part represents that light intensity is relatively strong, blood flow is more, and the part relatively dredged represents that light intensity is more weak, blood flow is less。Therefore, from figure shown in Fig. 9 C it can be seen that when takeing on the cerebration of flex region 354a of interior convulsion region 352a, the outer convulsion region 352b of motor region 352 and elbow motor region 354 and enlivening, it is meant that it is sending toggle and is developing simultaneously the instruction of arm。

Below, with reference to 10A-10D, the display example of the blood flow measurement result of depth direction is illustrated。

Figure 10 B indicate that the light that illuminating part 120 sends just irradiate after (have passed through time t1), along the longitdinal cross-section diagram of line A-A。

As shown in Figure 10 A, the laser A launched from illuminating part 120, for instance, as shown in three propagation path of lights 170, the track along substantially arc-shaped is propagated。It addition, in Figure 10 B-Figure 10 D, show, with image, the change measuring the light intensity putting A1, A2, A3 that three propagation path of lights 170 intersect with line A-A。

From Figure 10 B it can be seen that the light sent at illuminating part 120 just irradiate after (have passed through time t1) propagation path of light 170, the blood flow (light reception intensity) measuring some A3 place is detected as the strongest。

From Figure 10 C it can be seen that the light sent at illuminating part 120 irradiated time t2 after propagation path of light 170, the blood flow (light reception intensity) measuring some A2 place is detected as the strongest。

From Figure 10 D it can be seen that the light sent at illuminating part 120 irradiated time t3 after propagation path of light 170, the blood flow (light reception intensity) measuring some A1 place is detected as the strongest。

In this manner it is possible to the light therethrough amount measuring some A1, A2, A3 place according to the depth direction of propagation path of light 170 carrys out the distribution measurement of the blood flow to depth direction。Such as, in the situation of Figure 10 B to Figure 10 D, it is possible to measure, carrying out over time, the point that blood flow is maximum moves from inside brain to skin section。

Below, the variation of cerebration measurement apparatus 100 is illustrated。

As shown in Figure 11 A, in the bloodstream measurement device 20A of the cerebration measurement apparatus 100A of variation 1, multiple sensor units 24 are installed in and are formed on spherical netted base portion 22A。In addition, it should be noted that in Figure 11 A, only it is shown that the schematic diagram of unilateral observation cerebration measurement apparatus 100A from head, but, the cerebration measurement apparatus 100A of the head opposite side being positioned at the paper back side also has identical composition。

Each sensor unit 24 is retained as the state running through Box junction part。It addition, the attachment structure of the tetragon of netted base portion 22A can be stretched according to the surface configuration of the mounted head shape that assumes diamond in shape, so, it can be deformed into corresponding with head surface shape spherical。

The netted arm (4 to 8) that netted base portion 22A is connected by each cross section has elastic resin material and is formed, so, the first end of the multiple sensor units 24 arranged can be passed through the elasticity of material itself and is closely contacted at head surface, additionally, both made head surface shape different, it is also possible to be closely contacted the first end of multiple sensor units 24 at the head surface as measurement object。

In variation 1, the diameter of sensor unit 24 is about 10mm-50mm, so, in netted base portion 22A, it is possible to the sensor unit 24 of about 150-300 is installed by predetermined configuration pattern (interval)。It addition, multiple sensor units 24 with previous embodiment 1 likewise it is possible to respectively by that obtain in advance and measure the corresponding address date in position of measuring of object and manage。The measurement data obtained from each sensor unit 24 is transferred into data administrator 50 together with respective address date, and is saved。

It addition, netted base portion 22A is divided into multiple region unit A-N, a small-sized wireless communication device (in Figure 11 the 400A-400N shown in stain) is set in each region unit A-N。So, the measurement data of multiple sensor units 24 just can be sent to data administrator 50 by the radio communication device 400A-400N in each region unit A-N。

Figure 11 B is the composition block diagram of each parts of variation 1。

As shown in Figure 11 B, multiple sensor units 24 are such as classified to each region unit A-N by each function of brain 300, and, for instance, turned to sensor unit group 24A1-24An, 24B1-24Bn ..., 24N1-24Nn by group。Transmission and the reception of wireless signal is carried out between the radio communication device 400A-400N and the data administrator 50 that arrange in each region unit A-N, if receiving the luminous instruction sent from data administrator 50, then export luminous signal concurrently to each sensor 24 of each region unit A-N。So, each illuminating part 120 of each region unit A-N just can be sequentially luminous, and is irradiated to the head surface (measured region) of each region unit。Meanwhile, it is sent to data administrator 50 with the sensor unit group 24A1-24An that arranges, 24B1-24Bn ..., measurement data that the light therethrough amount that receives of light accepting part 130 of 24N1-24Nn is corresponding in each region unit A-N from radio communication device 400A-400N。So, in data administrator 50, each data of each region unit A-N measured by sensor unit group 24A1-24An, 24B1-24Bn ..., 24N1-24Nn are processed concurrently。

In this variation 1, cerebration measurement apparatus 100A has multiple radio communication device 400A-400N, so, the measurement data that sensor unit group 24A1-24An, 24B1-24Bn ..., 24N1-24Nn record can be sent out within the very short time。Meanwhile, in data administrator 50, it is possible to by each region unit, measurement data is analyzed, thus can pass through parallel processing and generate the view data of each region unit A-N efficiently。

Additionally, in netted base portion 22A, two in multiple arms that each cross section connects are made of an electrically conducting material, the two conductive material is connected with the illuminating part 120 of sensor unit 24 and light accepting part 130 respectively, in this manner it is possible to carry out instruction and the measurement data that receives of detection of luminescence。

As shown in figure 12, in the bloodstream measurement device 20B of the cerebration measurement apparatus 100B of variation 2, the flexible wiring 500 being made up of resin material is radially provided with multiple otch 510A-510N。In addition, it should be noted that in fig. 12, only it is shown that the schematic diagram of unilateral observation cerebration measurement apparatus 100B from head, but, the cerebration measurement apparatus 100B of the head opposite side being positioned at the paper back side also has identical composition。It addition, in flexible wiring 500, also such as previous embodiment 1 similarly, be provided with multiple sensor unit 24 at a predefined interval。

Flexible wiring 500 has pliability, so, by multiple otch 510A-510N, it can easily be deformed into the curve form corresponding with head surface shape。But, by arranging multiple otch 510A-510N from the lateral central part being formed flat flexible wiring 500, and, adjust the angle of otch and the length of otch, it is also possible to corresponding with various curve forms。So, in the present embodiment, it is possible to bending flexible wiring 500, while being easily positioned on head surface, meanwhile, measure after terminating, it is possible to only by flexible wiring 500 is reverted to plane, it is possible to easily pulled down。

It addition, each region that the multiple sensor units 24 being arranged on flexible wiring 500 are split by incision 510A-510N is controlled, turned to sensor unit group 24A1-24An, 24B1-24Bn ..., 24N1-24Nn by group respectively。Because multiple otch 510A-510N can be arranged on arbitrary position, so, it is possible to each region of each region unit A-N is set according to measured region。

It addition, in this variation 2, also in the same manner as Aforesaid deformation example 1, be provided with small-sized wireless communication device 400A-400N (representing with bullet in fig. 12) in each region unit A-N。So, the measurement data of multiple sensor units 24 just can be transferred into data administrator 50 by each region unit A-N from radio communication device 400A-400N。

As shown in figure 13, the flexible wiring 600 being made up of resin material is formed as banding by the bloodstream measurement device 20C of the cerebration measurement apparatus 100C of variation 3, and, flexible wiring 600 is rolled up in the shape of a spiral the structure paid。In addition, it is necessary to illustrate, in fig. 13, only it is shown that the schematic diagram of unilateral observation cerebration measurement apparatus 100C from head, but, the cerebration measurement apparatus 100C of the head opposite side being positioned at the paper back side also has identical composition。It addition, in flexible wiring 600, in the same manner as Aforesaid deformation example 2, multiple sensor units 24 and radio communication device 400A-400N (representing with bullet in fig. 13) are configured to predetermined distance of being separated by respectively。

Flexible wiring 600 is because being formed with flexual banding, so it can freely be curled into the shape of head surface, and it is possible to be easily mounted to head so that its curve form with head is in close contact。Although it addition, the nose shape of the measured is varied, but, when mounted, it is possible to pay scope adapt to it by suitably adjusting the volume of flexible wiring 600。

It should be noted that in fig. 14, the part identical with the sensor unit 24 of earlier figures 2 is marked identical symbol, and the description thereof will be omitted。As shown in figure 14, in the sensor unit 700 of variation, the inner side measuring electrode 710 at the E.E.G being formed as cone cylinder shape is provided with the light path separating component 720 being formed as taper with inserting。In this variation, on the periphery of light path separating component 720, inlay E.E.G integratedly and measured electrode 710。In addition, it is necessary to illustrate, E.E.G is measured the cone angle of electrode 710 and light path separating component 720 and at random can be set according to the area of total length and upper and lower end parts。Additionally, light path separating component 720 is also in the same manner as aforementioned enforcement 1, be made up of hologram (hologram), penetrate from first end 722 for laser that illuminating part 120 is sent, and by that propagate brain 300 in, be collected to light accepting part 130 from the light of elder generation's end 722 incidence。

E.E.G is measured the first end 712 of electrode 710 and is also downwardly projected than the first end 722 of light path separating component 720, so, by contacting with head surface 220, it is possible to measure the E.E.G of this measured region。

It addition, the base end side that E.E.G measures electrode 710 is provided with blade of a sword portion, big footpath 714。The inwall of this blade of a sword portion 714 axially (above-below direction) and the outer cylinder member 730 formed by conductive material is inserted into slidably。Outer cylinder member 730 has: space 740, and it is used for making above-mentioned E.E.G measurement electrode 710 and light path separating component 720 slide in axial direction；Top wall portion 732, it is formed around the top in space 740；Lower part wall portion 734, it is not formed about the bottom in space 740。

Measure to be provided with between blade of a sword portion 714 and the top wall portion 732 of electrode 710 at E.E.G and pay pressure part (coil spring) 750, for E.E.G being measured 710 pairs of electrode pressure in lower section。When E.E.G measurement electrode 710 contacts with head surface with the first end of light path separating component 720, pay pressure part 750 to be pressed power and compressed, so, E.E.G is just measured the tip of electrode 710 and light path separating component 720 and is pressed against head surface 220 by contrary with this compression stress elastic reaction。

Therefore, installing by pressing downwards outer cylinder member 730, that pays pressure part 750 pays pressure generation effect, it is possible to make the tip that E.E.G measures electrode 710 and light path separating component 720 be closely contacted to head surface 220。So, both having made measured region have hair, E.E.G is measured electrode 710 and can also positively be contacted with head surface 220 with the tip of light path separating component 720。

The upper surface 724 of light path separating component 720 is mounted with illuminating part 120 and light accepting part 130。The light path separating component 720 of this variation is formed the taper that upper end is big footpath, so, the area of upper surface 724 can be set according to the size of illuminating part 120 and light accepting part 130。Alternatively, it is also possible to illuminating part 120 and light accepting part 130 independently, by the diameter of the first end 722 of light path separating component 720 is carried out path process, make the contact area with head surface 220 reduce。So, when the upper surface 724 of light path separating component 720 contacts with head surface 220, it is possible to chuck is not sent out, and improves certainty of measurement。

In addition, it is necessary to illustrate, in the present embodiment, the laser A sent from head surface 220 and the light received from the tip of light path separating component 720, because reflection concurrently form guided wave road on the inwall of taper, so not affecting the transit dose of light。

[embodiment 2]

As shown in figure 15, the bloodstream measurement device 800 of embodiment 2 is for measuring blood flow during hemodialysis, and this bloodstream measurement device 800 has: sensor unit 820, and it is mounted to the Dialysis tubing 812 being connected with hemodialysis's device 810；Control portion 830, hemodialysis's device 810 is controlled by it according to the measurement data of sensor unit 820 output。

Dialysis tubing 812 is constituted by having elastic semi-transparent resin。It addition, Dialysis tubing 812 is connected with the blood vessel 842,844 of the patient 840 accepting dialysis, the blood taken out from blood vessel 842,844 is supplied to hemodialysis's device 810。In hemodialysis's device 810, having: artificial kidney (dialyzer), it is used for filtering blood, it is provided that dialysis solution；Pump installation, it is used for transmitting blood。

Control portion 830 calculates blood flow and erythrocyte concentration according to the measurement data measured by sensor unit 820, and controls the quantity delivered of the dialysis solution of hemodialysis's device 810 and the revolution of pump installation according to blood flow。It addition, the measurement result of sensor unit 820 and dialysis data are exported to PC 850 by control portion 830。In PC 850, measure preservation and the analysis of result and dialysis data。

As shown in figure 16, sensor unit 820 has: holding member 860, and it for remaining the state from above-below direction pressing by a part for Dialysis tubing 812；Two sensors portion 870,880。First sensor portion 870 is made up of the first illuminating part 872 being arranged in Dialysis tubing 812 top, first, second light accepting part 874,876 that is arranged in Dialysis tubing 812 bottom。It addition, the second sensor part 880 is also in the same manner as first sensor portion 870, by being arranged in second illuminating part 882 on Dialysis tubing 812 top, it is arranged in the three, the 4th light accepting parts 884,886 below Dialysis tubing 812 and is formed。

In this embodiment 2, above-mentioned formula 3 is used to adopt the measuring method of two two wavelength that erythrocyte concentration Rpw is measured。That is: the wavelength of the laser by the first illuminating part 872 and the second illuminating part 882 being sent is set as different wavelength X 1, λ 2 (λ 1=805nm, λ 2=680nm), only as variable, hematocrit value (Ht) is measured erythrocyte concentration。Therefore, by these computational methods it can be seen that erythrocyte concentration value can correctly be measured, this erythrocyte concentration value is based on the measured value of hematocrit value (Ht)。

[embodiment 3]

As shown in figure 17, the bloodstream measurement device 900 of embodiment 3 has: measurement portion 920, and it contacts with the skin surface 910 of measured region；Sensor unit 930, it is arranged on the inside in measurement portion 920；Control portion 940, it generates blood flow measurement image according to the measurement data of sensor 930 output。

Measurement portion 920 is formed the size that can move with hands, for instance, it is possible to according to which position measurement of human body suitably move。The prominent handle part 926 in top it addition, in measurement portion 920, the bottom surface in coniform portion 922 is the measuring surface 924 contacted with measured region, in coniform portion 922。Therefore, the gauger performing blood flow measurement can pass through to hold this handle part 926, makes measuring surface 924 suitably contact with the skin surface 910 of measured region, measures the blood flow of this measured region。

Sensor unit 930 has: illuminating part 950, and it is used for launching laser A；Light accepting part 960,962, it is configured to the position different from light injection point；Light path separating component 970, it is made up of hologram (hologram)。At installed above illuminating part 940 and a pair light accepting part 960,962 of light path separating component 970, light path separating component 970 measuring surface 924 is formed below。

So, if be irradiated to the skin surface 910 of arbitrary measured region after passing through light path separating component 970 from the laser A of illuminating part 940 transmitting, the blood flow in blood vessel on the downside of laser A traverse skin surface 910, propagate to measuring surface 924。Then, in a pair light accepting part 950,960, receive respectively and propagate the light to light path separating component 970, the signal of telecommunication based on the light therethrough amount received is exported to control portion 940。

In the present embodiment, aforementioned formula 2 is used to adopt the measuring method erythrocyte concentration Rp measurement to flowing in blood vessel 912 of two one wavelength。That is: erythrocyte concentration is the distance L between two light accepting parts 960,962 and the function of aforementioned hematocrit value (Ht)。So, when erythrocyte concentration is calculated, owing to the distance L between the light accepting part 960,962 in two factors is known that in advance, so, can measuring erythrocyte concentration, this erythrocyte concentration is using the hematocrit value (Ht) value as variable。Therefore, by this computational methods it can be seen that erythrocyte concentration can be accurately measured, this erythrocyte concentration is based on the measured value of hematocrit value (Ht)。

Control portion 940 is connected with display 980, is used for according to the blood flow measurement data genaration view data measured by the sensor unit 930 in measurement portion 920, and will be shown on display 980 by the measurement image that this view data is obtained。So, gauger just can observe the measurement image 982 of display on display 980, and hand-held measurement portion 920 makes measuring surface 924 contact with skin surface 910 on one side, confirms that whether blood flow is normal。

Additionally, because the measurement portion 920 of bloodstream measurement device 900 can suitably be moved, so the blood flow at position beyond head can easily be measured, simultaneously, because bloodstream measurement device 900 is easy to carry, it is possible to not by the restriction in specifically used place, it may be assumed that the place beyond the consulting room of medical treatment office is (such as, interim clinic when earthquake occurs or the building beyond medical treatment office, tent, even outdoor etc.) can also be convenient to use。

The invention is not limited in above-mentioned specific embodiment, without departing from the scope of claims, other versions also can be adopted to replace, but those versions still fall within scope involved in the present invention。

Claims

1. a bloodstream measurement device, including:

Sensor unit, it has for the illuminating part of measured region irradiation light and for receiving the light accepting part of light propagated in described measured region,

Control portion, the blood flow state of described measured region is measured by it for the signal exported according to described light accepting part,

Wherein,

Described illuminating part sends the first light and the second light, and described first light has the wavelength being difficult to be affected its optical characteristics by the oxygen saturation in blood, and described second light has the wavelength being affected its optical characteristics by the oxygen saturation in blood,

Light accepting part described at least two being arranged on the position different from the distance of described illuminating part accepts described first light and described second light that described illuminating part sends,

Described control portion is by setting the ratio from the erythrocyte concentration the first light that described illuminating part sends with the erythrocyte concentration under described second light, perform the computing that the composition of the oxygen saturation contained in the signal obtained from light accepting part described at least two is cancelled, function to be only used as the hematocrit value Ht of the erythrocytic volumetric concentration representing per unit volume is calculated, carry out the blood flow state to described measured region to measure

Described sensor unit has the light path separating component being made up of hologram, described hologram is configured to, to from the refractive index of the light of measured region described in described illuminating part directive to different from the refractive index of the light of light accepting part described in described measured region directive。

2. bloodstream measurement device according to claim 1, wherein,

The second light therethrough amount when the first light therethrough amount when described control portion is by receiving described first light by described light accepting part and described light accepting part receive described second light compares, and the blood flow state of described measured region is measured。

3. bloodstream measurement device according to claim 2, wherein,

The blood flow state of described measured region, according to based on from the measurement data of the described first, second light therethrough amount of light accepting part output described at least two, is measured by described control portion。

4. according to any 1 the described bloodstream measurement device in claims 1 to 3, wherein,

Described illuminating part and described light accepting part carry out emission of light and reception via described light path separating component。

5. a cerebration measurement apparatus, wherein,

By using any 1 the described bloodstream measurement device recorded in claim 1 to 4 that the blood flow of brain is measured, and according to the result that described bloodstream measurement device is measured, the active state of described brain is measured。

6. cerebration measurement apparatus according to claim 5, wherein,

Different positions arranges multiple described sensor unit,

Described control portion makes the light from light source of a sensor unit in multiple described sensor unit, and detect from this sensor unit have left the position of different distances arrange at least two described in sensor unit light accepting part received by light therethrough amount, then according to the measurement data based on the first, second light therethrough amount from two described light accepting part outputs, the cerebration state of described measured region is measured。

7. cerebration measurement apparatus according to claim 6, wherein,

Described control portion makes all described illuminating part of multiple described sensor unit sequentially luminous, and detect and leave, from a sensor unit of described luminescence, the light intensity that the light accepting part of at least two sensor unit arranged the position of different distances receives, then according to the measurement data based on the described first, second light therethrough amount exported from two described light accepting parts, the cerebration state of described measured region is measured。

8. according to any 1 the described cerebration measurement apparatus in claim 5 to 7, wherein,

Described sensor unit has the E.E.G for measuring E.E.G and measures electrode。

9. cerebration measurement apparatus according to claim 8, wherein,

Described E.E.G is measured electrode and is formed on the first end face of described light path separating component in described sensor unit to side。