JP6762009B2 - Body fluid viscosity measuring device - Google Patents

Description

The present invention relates to a body fluid viscosity measuring device for measuring the viscosity of a body fluid.

Measuring the viscosity of body fluids is effective in knowing the state of health. For example, in the case of humans, it has been confirmed that the viscosity of blood increases when dehydrated or suffering from myocardial infarction or cerebral infarction. It is also known that the risk of developing diabetes increases as the blood viscosity increases.
There are various methods for measuring the viscosity of body fluids, and specific examples thereof are described in, for example, Patent Document 1. In Patent Document 1, a reference fluid having a reference viscosity and a measurement target fluid for which the viscosity is to be measured are injected from both sides of the pipe, and among a plurality of counting channels connected to the pipe at regular intervals, the measurement target fluid A method of measuring the viscosity of the fluid to be measured by the number of flowing fluids is disclosed.

Japanese Patent Application Laid-Open No. 2013-520676

However, the method described in Patent Document 1 has a problem that the measurement accuracy depends on the arrangement pitch of the counting channel.
The present invention has been made in view of such circumstances, and an object of the present invention is to provide a body fluid viscosity measuring device capable of measuring the viscosity of a body fluid while suppressing the measurement accuracy from depending on the structure.

The body fluid viscosity measuring device according to the present invention according to the above object is a body fluid viscosity measuring device for measuring the viscosity of a body fluid flowing through a flow path, and is a first conductive device provided in the flow path and connected to an external power source. A second conductive portion provided in the flow path and electrically connected to the first conductive portion via the body fluid in the flow path, and a second conductive portion connected to the second conductive portion. The first and second conductive portions include a calculation means for calculating the viscosity of the body fluid from a timing interval at which an electric signal output from the output terminal rises by a predetermined value or more per predetermined time length. , At least three in total, each of which is arranged at a different position in the flow path along the flow of the body fluid.

In the body fluid viscosity measuring device according to the present invention, it is preferable that the calculation means further calculates the electrical conductivity and viscosity of the body fluid from the magnitude of the electric signal output from the output terminal.

In the body fluid viscosity measuring device according to the present invention, it is preferable that the first and second conductive portions are alternately arranged along the flow of the body fluid.

In the body fluid viscosity measuring apparatus according to the present invention, it is preferable that the arrangement pitch of the first and second conductive portions is constant.

In the body fluid viscosity measuring device according to the present invention, the width of the flow path is preferably the size at which the body fluid flows due to the capillary phenomenon.

In the body fluid viscosity measuring device according to the present invention, it is preferable that there are a plurality of the second conductive portions, and the plurality of second conductive portions are connected to one output terminal.

In the body fluid viscosity measuring device according to the present invention, there are a plurality of the second conductive portions, and the electrical states of the plurality of second conductive portions are independently monitored, and each of the second conductive portions has the said. It is preferable that the time at the moment of contact with the body fluid is recorded.

In the body fluid viscosity measuring apparatus according to the present invention, the reagent solution is merged with the body fluid on the downstream side of the arrangement region of the first and second conductive portions of the flow path, and the body fluid and the reagent solution are mixed. It is preferable to further provide a liquid supply mechanism for adjusting the viscosity of the mixture to a predetermined value, and a concentration deriving means for measuring the electric conductivity and the electrolyte concentration of the mixed liquid.

In the body fluid viscosity measuring device according to the present invention, it is preferable that the calculation means calculates the viscosity of the body fluid by using the electrolyte concentration of the mixed solution measured by the concentration deriving means.

In the body fluid viscosity measuring device according to the present invention, electrode units P and Q having the flow path, at least three of the first and second conductive portions and the output terminal, respectively, are provided, and the electrode unit P is provided. The exit side of the flow path is connected to the entry side of the flow path of the electrode unit Q via a trap that removes a specific substance from the body fluid, and the calculation means flows through the electrode units P and Q. The viscosity of each body fluid may be calculated.

In the body fluid viscosity measuring device according to the present invention, a chip having the flow path and at least three of the first and second conductive portions in total, and a mounted body to which the chip is mounted are provided, and the mounted body is provided. The body has a first circuit for connecting the first conductive portion of the mounted chip to the power supply, and a second circuit for connecting the second conductive portion of the mounted chip to the output terminal. A circuit may be provided.

In the body fluid viscosity measuring device according to the present invention, the electrode unit R having the first and second conductive portions and the output terminal having at least three in total, and the electrode unit S having the same structure as the electrode unit R. Based on the viscosity of the standard sample solution calculated by flowing a standard sample solution whose viscosity is known to flow through the flow path of the electrode unit S, the calculation means applies the body fluid to the electrode unit R. The viscosity of the body fluid calculated by flowing through the flow path may be corrected.

In the body fluid viscosity measuring device according to the present invention, the electrode unit R'having the flow path, the first and second conductive portions and the output terminal in total, and an electrode having the same structure as the electrode unit R' A liquid supply means for supplying a viscosity adjusting liquid for changing the viscosity of the body liquid is provided in the flow path of the unit S'and the electrode unit S', and the calculation means passes through the flow path of the electrode unit R'. The viscosity of the flowing body liquid and the viscosity of the viscosity adjusting liquid flowing through the flow path of the electrode unit S'and the viscosity of the mixed liquid of the body liquid may be calculated respectively.

The body fluid viscosity measuring device according to the present invention has a first conductive portion provided in the flow path and a first conductive portion provided in the flow path and electrically connected to the first conductive portion via the body fluid in the flow path. A calculation means for calculating the viscosity of body fluid from the interval at which the electrical signal output from the second conductive portion and the output terminal connected to the second conductive portion rises by a predetermined value or more per predetermined time length. There are at least three first and second conductive parts in total, and each of them comes into contact with the body fluid at different positions in the flow path along the flow of the body fluid, so that the measurement accuracy depends on the structure. It is possible to suppress and measure the viscosity.

It is explanatory drawing of the body fluid viscosity measuring apparatus which concerns on one Embodiment of this invention. It is explanatory drawing of the electrode unit of the body fluid viscosity measuring apparatus. (A), (B), and (C) are a partial cross-sectional view of the chip of the body fluid viscosity measuring device and a partial cross-sectional view of the chip according to the first and second modifications, respectively. It is explanatory drawing which shows the connection of a plurality of electrode units and a trap. It is explanatory drawing which shows the connection of a plurality of electrode units and a liquid supply mechanism. It is explanatory drawing which shows the structure of the electrode unit which merges a reagent solution with a body fluid. It is explanatory drawing which shows the electrode unit R, S used for correcting the electric conductivity and viscosity using a standard sample liquid. It is explanatory drawing which shows the electrode unit R', S'used for measuring the viscosity of a body fluid and the viscosity of a mixture liquid of a viscosity adjusting liquid and a body fluid. It is a graph which shows the change of the output current value with the passage of time. It is a graph which enlarged a part of the graph of FIG. It is explanatory drawing which shows the example of connecting the single chip microcomputer to the 2nd conductive part. It is explanatory drawing which shows the change of the digital signal generated by a single chip microcomputer.

Subsequently, an embodiment embodying the present invention will be described with reference to the attached drawings, and the present invention will be understood.
As shown in FIGS. 1, 2, and 3 (A), the body fluid viscosity measuring device 10 according to the embodiment of the present invention is a device for measuring the viscosity of the body fluid F flowing through the flow path 11, and is a flow device. The first conductive portions 12, 13, 14 provided on the road 11 and connected to the external AC power source (an example of the external power source) V via the input terminal 40, and the second conductive portion provided in the flow path 11. The electric signal output from the output terminals 19 connected to the parts 15, 16, 17, 18 and the second conductive parts 15, 16, 17, 18 rises by a predetermined value or more per unit time. It has a calculation means 44 for calculating the viscosity of the body fluid F from the timing interval. The details will be described below.

The body fluid F whose viscosity is to be measured is an electrolyte solution, for example, human blood, cerebrospinal fluid, sweat, saliva, and tears.
As shown in FIGS. 1 and 2, the body fluid viscosity measuring device 10 includes an electrode unit 21 connected to the AC power supply V via a switch 20. As shown in FIGS. 1, 2, and 3 (A), the electrode unit 21 is provided with a flow path 11, and the first conductive portions 12, 13, 14 and the second conductive portions 15, 16, 17, It has a chip 22 including 18, and an attached body 23 on which the chip 22 is mounted.

As shown in FIGS. 2 and 3A, the chip 22 includes a front and rear long rectangular plate member 24 and a front and rear long plate-shaped base member 25 to which the plate member 24 is fixed on the upper side.
In the plate material 24, a recess 26 is formed on the bottom surface side along the longitudinal direction of the plate material 24, and the opening 27 formed from the upper surface of the plate material 24 to one side of the recess 26 and the other side of the recess 26 from the upper surface of the plate material 24. An opening 28 formed over the surface is provided. In the present embodiment, the opening 27 is the introduction port for the body fluid F and the opening 28 is the discharge port for the body fluid F. However, the opening 28 is used as the introduction port for the body fluid F and the opening 27 is used as the discharge port for the body fluid F. You may.

The flow path 11 of the chip 22 is formed by contacting the bottom surface of the plate member 24 with the upper surface of the base member 25 and fixing the flow path 11 so that the opening of the recess 26 of the plate member 24 is closed by the upper surface of the base member 25. The flow path 11 is hydrophilic, and the width of the flow path 11 is such that the body fluid F can move in the flow path 11 due to the capillary phenomenon, for example, in the range of 10 μm to 500 μm. Therefore, when the body fluid F is introduced from the opening 27, the body fluid F advances in the flow path 11 from the opening 27 side (one side) to the opening 28 side (the other side) due to the capillary phenomenon, and enters the flow path 11. Flow occurs from one side to the other.

In the present embodiment, the plate material 24 is formed of PDMS (dimethylpolysiloxane) containing Siluet to ensure the hydrophilicity of the flow path 11, but the hydrophilic treatment is limited to this. It's not a thing.

On the upper surface of the base member 25, the conductors 32, 33, 34 having the first conductive portions 12, 13 and 14, respectively, and the conductors 35, 36, 37 having the second conductive portions 15, 16, 17, 18 respectively. 38 is provided. In the present embodiment, the base member 25 is made of glass, but the present invention is not limited to this.

Then, as shown in FIGS. 2 and 3 (A), the conductor 35 (the same applies to the conductors 32 to 34 and 36 to 38) has a second conductive portion 15 (the conductors 32 to 34 and 36 to 38). The first conductive portions 12 to 14 and the second conductive portions 16 to 18) need only be arranged in the flow path 11, respectively, and as in the present embodiment, from the left end to the right end of the base member 25. The entire conductor 35 does not have to be in close contact with the upper surface of the base member 25.
For example, as shown in FIG. 3 (B), the second conductive portion 15 may be fixed to the upper side of the flow path 11 and the conducting wire 35 may be wired so as to be separated from the base member 25, or FIG. 3 (C). ), The conductor 35 may be wired so that one end is arranged in the flow path 11. These are the same for the conductors 32 to 34 and 36 to 38.

In the flow path 11, as shown in FIGS. 1 and 2, the second conductive portion 15, the first conductive portion 12, the second conductive portion 16, and the first conductive portion are along the flow of the body fluid F. 13, the second conductive portion 17, the first conductive portion 14, and the second conductive portion 18 are arranged in order (that is, the first conductive portion and the second conductive portion are alternately arranged along the flow of the body fluid. Is located in).
Therefore, the body fluid F introduced into the opening 27 travels through the flow path 11, the second conductive portion 15, the first conductive portion 12, the second conductive portion 16, the first conductive portion 13, and the first conductive portion 13. The conductive portion 17, the first conductive portion 14, and the second conductive portion 18 are contacted in this order, and the first conductive portions 12, 13, 14 and the second conductive portions 15, 16, 17, and 18 are body fluids. It comes into contact with the body fluid F at different positions in the flow path 11 along the flow of F.

Further, the second conductive portion 15, the first conductive portion 12, the second conductive portion 16, the first conductive portion 13, the second conductive portion 17, the first conductive portion 14, and the second conductive portion 18 The arrangement pitch of is constant. Therefore, the body fluid F introduced from the opening 27 has a second conductive portion 15, a first conductive portion 12, a second conductive portion 16, and a first conductive portion at regular (substantially constant) time intervals. It reaches the portion 13, the second conductive portion 17, the first conductive portion 14, and the second conductive portion 18 in this order.

Since the body fluid F has electrical conductivity, the body fluid F introduced from the opening 27 passes through the second conductive portion 15 and reaches the first conductive portion 12, and the opening 27 to the first of the flow path 11 When the body fluid F is present in the entire region up to the conductive portion 12, the second conductive portion 15 is electrically connected to the first conductive portion 12 via the body fluid F in the flow path 11. To. After that, when the body fluid F reaches the second conductive portion 16, the second conductive portion 16 is electrically connected to the first conductive portion 12 and the second conductive portion 15 via the body fluid F. Will be done. Then, when the body fluid F reaches the second conductive portion 18, all the first conductive portions 12, 13, 14 and the second conductive portions 15, 16, 17, 18 pass through the body fluid F. It is electrically connected.

As shown in FIGS. 1 and 2, the mounted body 23 includes a frame portion 39 into which the chip 22 is fitted. The frame portion 39 is provided with an input terminal 40 connected to the AC power supply V and a circuit 41 (first circuit) having a lead wire branched into three from the input terminal 40 on the left side, and the output terminal 19 and the frame portion 39. A circuit 42 (second circuit) having a lead wire branched into four from the output terminal 19 is provided on the right side.
By fitting the chip 22 inside the frame portion 39 (that is, the chip 22 is mounted on the mounted body 23), the first conductive portions 12, 13 and 14 of the chip 22 are inserted through the circuit 41. It is connected to the input terminal 40, and the second conductive portions 15, 16, 17, and 18 are connected to the output terminal 19 via the circuit 42.

That is, the plurality of second conductive portions 15, 16, 17, and 18 are connected to the circuit 42, and the circuit 42 connects the second conductive portions 15, 16, 17, and 18 to one output terminal 19. Hereinafter, unless otherwise specified, it is assumed that the chip 22 is mounted on the mounted body 23.
As shown in FIG. 1, a calculation means 44 is connected to the output terminal 19 via a switch 43. As shown in FIG. 1, the switch 43 can switch the connection destination of the arithmetic means 44 from the output terminal 19 of the electrode unit 21 to the reference resistor 44a for calibration (calibration).

The calculation means 44 has a clock function and a function of measuring the value of the current (an example of an electric signal) output from the output terminal 19, and can associate the measured current value with the time information.
As the head portion of the body fluid F introduced into the opening 27 and traveling through the flow path 11 advances toward the opening 28, the head portion of the body fluid F becomes the second conductive portion 15, the first conductive portion 12, and the second. The current value (hereinafter, hereinafter, the current value) that has passed through the conductive portion 16, the first conductive portion 13, the second conductive portion 17, the first conductive portion 14, and the second conductive portion 18 in this order, and is output from the output terminal 19. (Simply referred to as "output current value") gradually increases. The stepwise increase in the output current value starts after the head portion of the body fluid F reaches the first conductive portion 12.

The calculation means 44 detects a time when the output current value rises by a predetermined value or more per predetermined time length (0.5 to 3 seconds in the present embodiment), and gradually increases the output current value. It is designed to detect the timing of the rise. The following values are registered in advance in the calculation means 44.

Registered values: the distance from the second conductive portion 15 to the first conductive portion 12, the distance from the first conductive portion 12 to the second conductive portion 16, the distance from the second conductive portion 16 to the first conductive portion 16. The distance to the conductive portion 13, the distance from the first conductive portion 13 to the second conductive portion 17, the distance from the second conductive portion 17 to the first conductive portion 14, and the distance from the first conductive portion 14 to the second Distance to the conductive part 18 of

When the flow path is a capillary (ie, the cross section of the flow path is circular), the equation of motion of the fluid moving in the flow path can be easily solved, resulting in the well-known result known as the Washburn equation. Be done. In the case of a fluid having a viscosity η and a surface tension γ that moves in a capillary tube having a diameter D, the Washburn equation is expressed as the following equation (1).

Here, L is the invasion distance of the fluid into the capillary, t is the time from when the fluid starts invading the capillary, and θ is the contact angle.

On the other hand, when the cross section of the flow path is rectangular instead of circular as in the present invention, 1) the motion of the fluid is not axisymmetric, and 2) the contact angles of the four surfaces in contact with the fluid are all the same. It is difficult to analytically solve the motion of a fluid because it cannot be regarded. However, by analogy with the equation (1), it is easily estimated that the relationship of the following equation (2) holds between the invasion distance L of the fluid and the invasion time t, which can be confirmed experimentally. it can.

Here, C is a constant unique to the flow path, which is determined by the geometric shape (width and height) of the flow path and the properties of the inner surface of the flow path (contact angle of each surface). The value of the constant C can be determined by recording the flow of a body fluid-like electrolyte solution (reference solution) having a known viscosity η and surface tension γ.

In the calculation means 44, the head portion of the body fluid F moves from the first conductive portion 12 to the second conductive portion 16, so that the first stepwise increase timing of the output current value and the second output current value are obtained. The time interval of the stepwise ascending timing is detected, and the detected time interval and the distance from the first conductive portion 12 to the second conductive portion 16 are substituted into t and L of the above equation, respectively, to form the body fluid F. Calculate the viscosity.

In the same procedure, the calculation means 44 moves the head portion of the body fluid F from the second conductive portion 16 to the first conductive portion 13, and moves the body fluid F from the first conductive portion 13 to the second conductive portion 17. By the movement of the body fluid F from the second conductive portion 17 to the first conductive portion 14, and the movement of the body fluid F from the first conductive portion 14 to the second conductive portion 18, each of the body fluid F Calculate the viscosity.

Therefore, the calculation means 44 calculates the viscosity of the body fluid F from the interval of the timing at which the output current value rises by a predetermined value or more per predetermined time length. The "timing at which the output current value rises by a predetermined value or more per predetermined time length" is defined as the first conductive portion 12, the second conductive portion 16, and the first conductive portion at the head portion of the body fluid F. Since the output current value may fluctuate slightly even at the timing when the portion 13, the second conductive portion 17, the first conductive portion 14, or the second conductive portion 18 is not passed, the leading portion of the body fluid F is The timing of passing through the first conductive portion 12, the second conductive portion 16, the first conductive portion 13, the second conductive portion 17, the first conductive portion 14, or the second conductive portion 18 is reliably detected. Because.

In the present embodiment, the viscosity of the body fluid F can be measured five times while the body fluid F introduced from the opening 27 moves to the second conductive portion 18. Since it is necessary to gradually increase the output current value at least twice in order to measure the viscosity of the system F, there are at least three first and second conductive portions in total, and each of them is a flow path. It is necessary that they are arranged in different positions along the flow of.

Further, the calculation means 44 can calculate the viscosity of the body fluid F from the magnitude of the output current value in addition to calculating the viscosity of the body fluid F from the time interval of the timing at which the output current value gradually increases. Hereinafter, a method of calculating the viscosity of the body fluid F from the magnitude of the output current value will be described.
In the calculation means 44, the head portion of the body liquid F is a first conductive portion 12, a second conductive portion 16, a first conductive portion 13, a second conductive portion 17, a first conductive portion 14, and a second conductive portion. The impedance between the input terminal 40 and the output terminal 19 (combined resistance value in the present embodiment) is obtained from the magnitude of the output current value that changes each time the conductor passes through the conductive portion 18.

Then, the calculation means 44 derives the electric conductivity (electrical conductivity) and viscosity of the body fluid F based on the obtained impedance. It is well known that the impedance between the input terminal 40 and the output terminal 19 is determined by the electric conductivity of the body fluid F, and that there is a direct correlation between the electric conductivity of the body fluid F and the viscosity of the body fluid F. (It is known, for example, by Walden's law) that there is a correlation between electrical conductivity and viscosity).

Therefore, the calculation means 44 can obtain the electric conductivity and viscosity of the body fluid F from the impedance between the input terminal 40 and the output terminal 19. The impedance between the input terminal 40 and the output terminal 19 gradually decreases as the output current value increases stepwise.
Derivation of the viscosity of body fluid F by the calculation means 44 is performed from the timing at which the output current value gradually increases (measurement from a hydrodynamic point of view) and from the magnitude of the output current value (electrical conductivity). There is a rate-based measurement), and an accurate value can be selected according to the situation.
For example, when an anticoagulant that suppresses blood coagulation is mixed with blood, the electrical conductivity is affected, so it is conceivable to select a measured value from a hydrodynamic point of view.

Here, the calculation means 44 calculates the body fluid F from the hydrodynamic point of view and calculates the viscosity based on the electric conductivity each time the output current value increases stepwise. Therefore, a predetermined amount of body fluid F (the amount in which all of the first conductive portions 12, 13, 14 and the second conductive portions 15, 16, 17, 18 are electrically connected by the body fluid F in the flow path 11) By introducing the body fluid F from the opening 27, the calculation means 44 can calculate the viscosity of the body fluid F a plurality of times, respectively, by two kinds of measurement methods from the hydrodynamic viewpoint and the electrical conduction viewpoint.

Then, the calculation means 44 obtains the final viscosity value of the body fluid F based on a plurality of viscosity values (viscosity coefficients in the present embodiment) calculated by different measurement methods. For example, the average of a plurality of calculated viscosity values is used as the final viscosity value, or the one having the smaller variation in each measurement value of viscosity is selected from the two measurement methods to obtain the final viscosity value. Can be done. In the present embodiment, the output current value increases stepwise 6 times until the body fluid F introduced from the opening 27 reaches the second conductive portion 18, so that the calculation means 44 is a hydrodynamic viewpoint. The viscosity from the body fluid F will be measured 5 times, and the viscosity from the value of the electrical conductivity of the body fluid F will be measured 6 times.

Further, when there is a difference of more than a predetermined value in each of the calculated viscosity values, or when the output current value does not gradually increase at a predetermined time interval, the calculation means 44 outputs a signal indicating that there is an abnormality. Is designed for.
In the present embodiment, as shown in FIG. 1, the arithmetic means 44 is mainly composed of two electric circuits 45 and 46, but the number of electric circuits does not have to be two.
Further, in the present embodiment, the first conductive portions 12, 13, 14 and the second conductive portions 15, 16, 17, and 18 are seven in total, but the first and second conductive portions are combined. At least three are required.

Further, in the present embodiment, there is only one electrode unit 21, but as shown in FIG. 4, two electrode units 48 and 49 (electrode units P and Q) can be provided. The electrode units 48 and 49 each have basically the same structure as the electrode unit 21, and the flow path 11 and a total of seven (that is, at least three in total) first conductive portions 12, 13, 14 and It has a second conductive portion 15, 16, 17, 18, and an output terminal 19.

The exit side (other side) of the flow path 11 of the electrode unit 48 is on the entry side (one side) of the flow path 11 of the electrode unit 49, and is a specific substance from the body fluid F (for example, when the body fluid F is blood, a specific substance). The material is connected via a trap 50 that removes blood cells). In the electrode units 48 and 49, the same reference numerals are given to the same configurations as those of the electrode units 21, and detailed description thereof will be omitted (the same applies hereinafter).

Therefore, the body fluid F introduced from the opening 27 of the electrode unit 48 passes through the flow path 11 of the electrode unit 48, and after the specific substance is removed by the trap 50, flows through the flow path 11 of the electrode unit 49. Therefore, a calculation means (not shown) calculates the electrical conductivity and viscosity of the body fluid F from which the specific substance has not been removed based on the output current value from the output terminal 19 of the electrode unit 48 (two measurement methods for viscosity). The electrical conductivity of body fluid F (for example, blood containing plasma from which blood cells have been removed) from which a specific substance has been removed is based on the output current value from the output terminal 19 of the electrode unit 49. And the viscosity is calculated.

Further, as shown in FIG. 5, a reagent solution is added to the body fluid F on the downstream side of the arrangement regions of the first conductive portions 12, 13, 14 and the second conductive portions 15, 16, 17, and 18 of the flow path 11. A liquid supply mechanism 52 that merges and adjusts the viscosity of the mixed solution of the body fluid F and the reagent solution to a predetermined value may be provided.
In the example shown in FIG. 5, an electrode unit 51 is provided on the downstream side of the electrode unit 49 with the entrance side of the flow path 11 connected to the exit side of the flow path 11 of the electrode unit 49, and the flow path 11 of the electrode unit 49 A liquid supply mechanism 52 is connected to the connection region of the flow path 11 of the electrode unit 51 via a pipe.

The electrode unit 51 has basically the same structure as the electrode unit 21, and the liquid supply mechanism 52 can be configured to include, for example, a pump and a solenoid valve.
The liquid supply mechanism 52, for example, joins distilled water (an example of a reagent solution, hereinafter simply referred to as “water”), which is approximately 20 times the volume ratio of the body fluid F, into the body fluid F between the electrode units 49 and 51. The viscosity of the mixture of body fluid F and water is set to the same level as that of water. At the output terminal 19 of the electrode unit 51, a concentration deriving means (not shown) for measuring the electric conductivity of the mixed solution flowing through the flow path 11 of the electrode unit 51 and the electrolyte concentration of the mixed solution based on the output current value from the output terminal 19. Is connected. The concentration deriving means can be configured by, for example, a computer in which a software program is installed.

The configuration in which the reagent solution is merged with the body fluid F is not limited to the one in which the liquid supply mechanism is provided between the two electrode units connected in series. For example, as shown in FIG. 6, two electrode units 55 and 56 are provided, and the body fluid F introduced from one opening 27 common to each flow path 11 of the electrode units 55 and 56 is the electrode units 55 and 56. Even if the liquid supply mechanism 52 is provided between the opening 27 and the electrode unit 55 so as to be fed toward each opening 28 and the reagent liquid is merged with the body fluid F sent to the flow path 11 of the electrode unit 55. Good.

The calculation means can obtain the electric conductivity and the electrolyte concentration measured by the concentration derivation means from the concentration derivation means, and the body fluid F is used by the electric conductivity of the mixed solution or the electrolyte concentration of the mixed solution measured by the concentration derivation means. Calculate the viscosity of.
Here, the calculation formula for calculating the viscosity of a body fluid based on impedance requires the electrolyte concentration of the body fluid. In this respect, the value of the electrolyte concentration of the body fluid is within a certain range for each type of body fluid, and the variation is small. Therefore, by substituting a predetermined value of the electrolyte concentration into the calculation formula, the viscosity of the target body fluid can be calculated without measuring the electrolyte concentration. However, from the viewpoint of more accurately calculating the electrolyte concentration, it is preferable to substitute the measured electrolyte concentration into the calculation formula to calculate the viscosity.

Further, as shown in FIG. 7, two electrode units 53 and 54 (electrode units R and S) having the same structure as the electrode unit 21 are provided, and the body fluid F is allowed to flow through the flow path 11 of the electrode unit 53 to form the electrode unit 54. It is also possible to correct the calculated viscosity of the body fluid F by flowing a standard sample solution having a known viscosity through the flow path 11.
The calculation means calculates the viscosity of the standard sample solution flowing through the flow path 11 of the electrode unit 54 and the viscosity of the body fluid F flowing through the flow path 11 of the electrode unit 53, respectively, and calculates the viscosity of the standard sample solution (specifically). Corrects the calculated viscosity of the body fluid F based on the calculated viscosity of the standard sample solution and the difference in viscosity of the standard sample solution whose viscosity has been found). Since it is possible that the calculated viscosity of body fluid F may have some errors due to differences in the environment such as the temperature at the time of measurement, it is necessary to correct the calculated viscosity of body fluid F based on the viscosity of the standard sample solution. , Suitable for obtaining more accurate viscosity. Further, it is also possible to install a temperature measuring means such as a thermistor element on the electrode unit to record the temperature at the time of measurement to ensure more accuracy.

Further, as shown in FIG. 8, the viscosity adjustment that changes the viscosity of the body liquid F in the flow paths 11 of the two electrode units 58, 59 (electrode units R', S') and the electrode unit 59 having the same structure as the electrode unit 21. A liquid supply means 60 for supplying a liquid (for example, a coagulation stimulating reagent) is provided, and the calculation means are the viscosity of the body liquid F flowing through the flow path 11 of the electrode unit 58 and the viscosity adjusting liquid and the body liquid flowing through the flow path 11 of the electrode unit 59. The viscosity of each of the mixed solutions of the above may be calculated. Thereby, for example, the effect of the viscosity adjusting solution on coagulating blood (an example of body fluid F) can be easily measured.

Next, an experiment conducted to confirm the action and effect of the present invention will be described.
In this experiment, an electrode unit having a total of seven first and second conductive parts was adopted, and sucrose was added to the flow path to increase the viscosity of the saline solution (hereinafter, also simply referred to as "saline solution"). Shed. 9 and 10 show the transition of the measured output current with respect to the time axis. The graph of FIG. 10 is an enlargement of a part of the graph of FIG. 9, and FIG. 10 shows the value of the combined resistance corresponding to each of the output currents that gradually increase.
From FIGS. 9 and 10, it was confirmed that the respective increase values of the output current gradually increasing were substantially the same, and that the output current gradually increased at intervals of 5 to 6 seconds. As a result, it can be seen that the electric conductivity and the viscosity can be calculated from each of the output currents that gradually increase.
In FIG. 9, D indicates the time when the saline solution was introduced, and W indicates the time when the saline solution was washed away by flowing water through the flow path.

Although the embodiments of the present invention have been described above, the present invention is not limited to the above-described embodiments, and all changes in conditions that do not deviate from the gist are within the scope of the present invention.
For example, the viscosity of a body fluid may be measured only from a hydrodynamic point of view. In that case, it is not necessary to quantitatively record the magnitude of the current, and only the time when the body fluid reaches the second conductive part (the time when the body fluid comes into contact with the second conductive part) can be accurately recorded. Good. That is, it is not necessary to record the current value as an analog value, but it is sufficient to record it as a digital value. Therefore, as shown in FIG. 11, a simple configuration using the single-chip microcomputer 61 can be achieved.

In the example shown in FIG. 11, a plurality of conductive portions 15, 16, 17, and 18 (second conductive portions) are independently connected to four channels (input terminals) of the single-chip microcomputer 61. The single-chip microcomputer 61 independently monitors the electrical states of the conductive parts 15, 16, 17, and 18 by the input capture function provided as standard, and the timing when the voltage values of the four channels change. That is, the time at which the body fluid F reaches the conductive portions 15, 16, 17, and 18 is read and recorded. T0, t1, t2, and t3 shown in FIG. 12 mean the timing when the head portion of the body fluid F reaches the conductive portions 15, 16, 17, and 18, respectively, and the digital values corresponding to each channel are t0, t1, t2, respectively. It rises discontinuously at t3. The viscosity of the body fluid F is measured based on the time interval of t0 and t1, the time interval of t1 and t2, and the time interval of t2 and t3.
Then, instead of connecting the AC power supply to the first conductive portion, the DC power supply E may be connected as shown in FIG.

Further, instead of the flow path through which the body fluid travels due to the capillary phenomenon, a flow path through which the body fluid travels by a pump or gravity may be adopted. However, when a flow path through which the body fluid travels due to the capillary phenomenon is adopted, the amount of the body fluid required for measuring the viscosity can be reduced.
In the present embodiment, the frequency of the AC voltage applied from the AC power supply to the input terminal is single and constant, but a plurality of AC voltages having different frequencies can be applied to the input terminal. When AC voltages having different frequencies are applied to the input terminals, the calculation means calculates the viscosity of the body fluid by obtaining the impedance of each frequency when calculating the viscosity from the electric conductivity.

Further, it is not necessary that the first and second conductive portions are alternately arranged along the flow of the body fluid. Further, the arrangement pitch of the first and second conductive portions does not have to be constant.
Further, when there are a plurality of second conductive portions, it is not necessary to connect the plurality of second conductive portions to one output terminal, and they may be connected to separate output terminals.

10: Body fluid viscosity measuring device, 11: Flow path, 12-14: First conductive part, 15-18: Second conductive part, 19: Output terminal, 20: Switch, 21: Electrode unit, 22: Chip, 23: Attached body, 24: Plate material, 25: Base member, 26: Recess, 27, 28: Opening, 32 to 38: Conductor, 39: Frame, 40: Input terminal, 41, 42: Circuit, 43: Switch, 44: Computational means, 44a: Reference resistance, 45, 46: Electric circuit, 48, 49: Electrode unit, 50: Trap, 51: Electrode unit, 52: Liquid supply mechanism, 53, 54, 55, 56, 58 , 59: Electrode unit, 60: Liquid supply means, 61: Single chip microcomputer, E: DC power supply, F: Body liquid, V: AC power supply

Claims (13)

A body fluid viscosity measuring device that measures the viscosity of body fluid flowing through a flow path.
A first conductive portion provided in the flow path and connected to an external power source,
A second conductive portion provided in the flow path and electrically connected to the first conductive portion via the body fluid in the flow path, and a second conductive portion.
It is provided with a calculation means for calculating the viscosity of the body fluid from the interval at which the electric signal output from the output terminal connected to the second conductive portion rises by a predetermined value or more per predetermined time length.
A body fluid viscosity measuring device, characterized in that there are at least three conductive portions in total, and the first and second conductive portions are arranged at different positions in the flow path along the flow of the body fluid. In the body fluid viscosity measuring device according to claim 1, the calculation means further calculates the electrical conductivity and viscosity of the body fluid from the magnitude of the electric signal output from the output terminal. .. The body fluid viscosity measuring device according to claim 1 or 2, wherein the first and second conductive portions are alternately arranged along the flow of the body fluid. The body fluid viscosity measuring device according to any one of claims 1 to 3, wherein the arrangement pitch of the first and second conductive portions is constant. The body fluid viscosity measuring device according to any one of claims 1 to 4, wherein the width of the flow path is such that the body fluid flows by a capillary phenomenon. In the body fluid viscosity measuring device according to any one of claims 1 to 5, there are a plurality of the second conductive portions, and the plurality of second conductive portions are connected to one output terminal. A featured body fluid viscosity measuring device. In the body fluid viscosity measuring apparatus according to any one of claims 1 to 5, there are a plurality of the second conductive portions, and the electrical states of the plurality of second conductive portions are independently monitored. A body fluid viscosity measuring device, characterized in that the time at the moment when the body fluid comes into contact with each of the second conductive portions is recorded. In the body fluid viscosity measuring apparatus according to any one of claims 1 to 7, the reagent solution is merged with the body fluid on the downstream side of the arrangement region of the first and second conductive portions of the flow path. The body fluid viscosity is further provided with a liquid supply mechanism for adjusting the viscosity of the mixture of the body fluid and the reagent solution to a predetermined value, and a concentration derivation means for measuring the electric conductivity and the electrolyte concentration of the mixture. measuring device. The body fluid viscosity measuring device according to claim 8, wherein the calculation means calculates the viscosity of the body fluid using the electrolyte concentration of the mixed solution measured by the concentration deriving means. In the body fluid viscosity measuring apparatus according to any one of claims 1 to 9, electrode units P and Q having the flow path, the first and second conductive portions in total, and the output terminal, respectively. Is provided, the outlet side of the flow path of the electrode unit P is connected to the entry side of the flow path of the electrode unit Q via a trap for removing a specific substance from the body fluid, and the calculation means is A body fluid viscosity measuring device for calculating the viscosity of the body fluid flowing through the electrode units P and Q, respectively. In the body fluid viscosity measuring device according to any one of claims 1 to 9, a chip having the flow path and at least three of the first and second conductive portions in total, and a chip to which the chip is mounted are mounted. A body is provided, and the mounted body is provided with a first circuit for connecting the first conductive portion of the mounted chip to the power supply, and the second conductive portion of the mounted chip. A body fluid viscosity measuring device characterized in that a second circuit connected to the output terminal is provided. In the body fluid viscosity measuring apparatus according to any one of claims 1 to 9, an electrode unit R having at least three first and second conductive portions and an output terminal in total, and the electrode. An electrode unit S having the same structure as the unit R is provided, and the calculation means is based on the viscosity of the standard sample fluid calculated by flowing a standard sample fluid having a known viscosity through the flow path of the electrode unit S. , A body fluid viscosity measuring device, characterized in that the viscosity of the body fluid calculated by flowing the body fluid through the flow path of the electrode unit R is corrected. In the body fluid viscosity measuring apparatus according to any one of claims 1 to 9, the electrode unit R'having the flow path, at least three of the first and second conductive portions and the output terminal, and the said. An electrode unit S'having the same structure as the electrode unit R'and a liquid supply means for supplying a viscosity adjusting liquid for changing the viscosity of the body liquid are provided in the flow path of the electrode unit S'. A body fluid viscosity measuring device for calculating the viscosity of the body fluid flowing through the flow path of the electrode unit R'and the viscosity of the viscosity adjusting liquid and the mixed liquid of the body fluid flowing through the flow path of the electrode unit S', respectively. ..

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