KR20130057242A - Device for automatically measuring oxigen delivery index of blood - Google Patents

Abstract

PURPOSE: An automatic measuring apparatus of oxygen delivery index(ODI) of blood is provided to automatically maintain blood temperature, insert a needle, and supply a predetermined amount of liquid by measuring ODI of blood, and to reduce worker's mistake. CONSTITUTION: An automatic measuring apparatus of ODI is used for measuring ODI by automatically extracting blood from a blood container(20). The apparatus comprises a container receiving member(220), a blood supply member(240), a viscosity measuring member(400), a hematocrit measuring member(500), and a control unit. The container receiving member is used for receiving a storage container. The blood supply member supplies blood from the storage container. The viscosity measuring member measures viscosity of blood supplied from the blood supply member. The hematocrit measuring member is used for measuring hematocrit of blood. The control unit is used for calculating ODI of blood using viscosity of blood and hematocrit value.

Description

DEVICE FOR AUTOMATICALLY MEASURING OXIGEN DELIVERY INDEX OF BLOOD}

The present invention relates to an oxygen supply capacity index of blood, and more particularly, to an automatic oxygen supply capacity index measuring device capable of automatically measuring the oxygen supply capacity index from the collected blood.

In general, the viscosity of blood is shown to increase as the hematocrit of blood increases. The primary purpose of blood flow is to transport oxygen, and the capacity of oxygen is proportional to the flow of blood, so how the flow of blood changes as hematocrit increases can be a very important issue.

Accordingly, the oxygen delivery index (ODI) of blood may be defined. For example, the maximum value of the oxygen supply index may be obtained when hematocrit is about 33%.

[Oxygen supply capacity (ODI) = Hematocrit / viscosity of blood]

Here, hematocrit refers to the volume ratio of red blood cells in whole blood. Hematocrit is one of the factors that determine the amount of oxygen delivered to the body. Recently, hematocrit has been used as an important indicator for evaluating the risk of death for cardiovascular and kidney diseases along with blood viscosity.

Considering that the adult male hematocrit is approximately 44-49%, in terms of oxygen supply, hematocrit is unnecessarily increased and flow resistance is increased. In other words, for most adult men, lowering hematocrit by about 35% can improve blood circulation, resulting in a much more efficient oxygen supply, and as a result, can significantly solve vascular diseases.

In order to measure hematocrit, a method of centrifuging a microtube containing blood to separate red blood cells and reading the ratio visually has been mainly used. Various methods have been attempted to solve the inconvenience of measuring the hematocrit ratio directly after measuring the blood directly by the tester and directing the blood into the microtube. The measuring method using the electrical conductivity is representative. have.

Many methods have been tried to determine the relationship between the electrical conductivity and hematocrit of blood, but due to the difficulties caused by various variables such as plasma resistance of blood, conductivity inside red blood cells, and conductance on the surface of red blood cells Because of this, hematocrit measurements of blood using electrical conductivity were relatively inaccurate.

For example, oxidation / reduction reactions may occur at the electrodes, and accurate measurements may be hindered by the electrolyte effect of plasma. In addition, polarization may occur at the electrode, and a decrease in current may occur. In particular, the conduction phenomenon may occur in the cells of the red blood cells, and the storage of the red blood cells may cause problems in the accuracy of the measurement.

In order to solve the problem of measurement caused by the electrolysis effect of plasma, a sine alternating signal rather than a direct current (DC) was used, but the measurement deviation due to plasma resistance was still not solved. In addition, a measurement method using dual frequency has been introduced to solve the difficulty of measurement due to the change in conductivity inside the red blood cell and the change in conductance on the surface of the red blood cell above a certain frequency. Since the measurement was made, the electrical conductivity did not show a constant value by erythrocyte sedimentation.

For example, Korean Patent No. 10-829928 discloses a method for measuring hematocrit in blood using electrical impedance and digital signal processing technology. The measurement method uses a pulse voltage of 1 ~ 999mV, and collects analog data such as sine wave, converts it into digital data, and controls and manages it. However, even when using a pulse signal, although there is a difference in degree compared to the use of a direct current power source, the oxidation / reduction of the electrode, the electrolyte effect of the plasma and polarization phenomenon in the electrode can still occur.

In addition, if the frequency of the pulse voltage is too high, a decrease in the current waveform may occur, a phenomenon in which the red blood cell itself acts as a conductor, and if a pulse wave in the form of a sine wave is provided, storage on the surface of the red blood cell (membrane) may occur. Symptoms may occur.

In recent years, a blood viscosity measuring device allows blood obtained from a body to pass through a flow restrictor tube, and measures blood viscosity and blood cell aggregation rate by measuring blood flow characteristics in the flow resistance tube. .

Korean Patent No. 747605 discloses a viscosity measuring device using a double vertical tube / single capillary tube. The viscosity measuring device monitors the height change of the two opposing-flowing blood columns from the circulating blood of the patient, and the capillary tube of certain dimensions through which the blood flow measures the blood viscosity over a range of shear forces, especially low shear forces. The system includes a pair of upright tubes, a capillary tube connected between the upright tubes, and a valve device for controlling the circulating blood flow from the patient to the upright tube, wherein a separate sensor is provided for each of the upright tubes. The flow of blood pillars in the tube is monitored and the microprocessor analyzes the blood flow in the capillary.

Thus, in order to supply blood for measuring blood viscosity, a needle or a tube may be inserted directly into a body blood vessel, and blood may be stored in a separate storage container and transferred to a viscosity measuring device. Vacuum can also be used to artificially transfer blood, or to pressurize air or other fluids to a specific pressure to transfer blood. Korean Patent Publication No. 2003-8223 (published Jan. 24, 2003) may be referred to a method of transferring blood using a vacuum.

The present invention provides an apparatus capable of automatically measuring the oxygen supply capacity of the blood.

The present invention provides an automatic oxygen supply capacity measuring apparatus that can automatically perform from the temperature maintenance of the blood and the insertion of the needle to supply a certain amount of blood.

The present invention provides an automatic oxygen supply capacity measuring device that is easy to install and detach the needle and can automatically measure the viscosity and hematocrack of the blood by handling the blood through automation.

The present invention can prevent the operator from being stuck to the needle or exposed to blood in the process of mounting and detaching the needle, and provides an automatic oxygen supply capacity automatic measuring device capable of completing the desired work in a stable and fast time.

The present invention provides an automatic oxygen supply capability measuring device that uses electrical conductivity for measuring hematocrit, prevents oxidation / reduction of the electrode and electrolyte effect of plasma, and suppresses polarization phenomenon and reduction of current at the electrode. do.

The present invention can prevent the erythrocyte cell itself from acting as a conductor in the process of measuring hematocrit, can prevent the accumulation of electricity on the erythrocyte membrane, recognize the erythrocyte as a non-insulator and measure the electrical conductivity of plasma Provides automatic measuring device for oxygen supply capacity.

The present invention measures the electrical conductivity using a low-frequency bipolar square wave signal without a separate centrifugation process from acquiring blood from the human body or from already acquired whole blood, and automatically calculates hematocrit through the electrical conductivity value. It provides automatic measuring device for oxygen supply ability that can be measured and utilized.

The present invention provides an automatic oxygen supply capacity measuring apparatus that can reduce the operator's mistakes due to the automated progress, can reduce the dependency on the operator's skill, and can provide the same conditions even if repeated every time.

According to an exemplary embodiment of the present invention, the oxygen supply capacity index automatic measuring device is a device for automatically extracting blood from the storage container in which blood is stored to measure the oxygen supply capacity index of blood, the container for accommodating the storage container Receiving member, blood supply member for supplying blood from the storage container accommodated in the container receiving member, viscosity measuring member for measuring the viscosity of the blood using the blood supplied from the blood supply member, blood using the blood supplied from the blood supply member And a hematocrit measuring member for measuring hematocrit, and a control unit for calculating an oxygen supply capacity index of blood using the viscosity and hematocrit value of blood obtained from the amount measuring member.

The automatic oxygen supply capacity measuring apparatus of the present invention automatically measures the viscosity of blood and hematocrit of blood using the blood supplied from the blood supply member, and calculates the oxygen supply capacity index of blood using the measured viscosity and hematocrit. There is a number. In this process, the blood is not exposed to the operator at all, and a consistent result can be obtained regardless of skill.

The viscosity measuring member and the hematocrit measuring member may be connected in series or parallel to the blood supply member, and after measuring the viscosity and the hematocrit using the supplied blood, the oxygen supply capacity index may be calculated using the measured values. have.

In addition, the blood supply member may include a needle portion and a needle fixing portion, and may further include a needle transfer member for adjusting the distance between the storage container and the needle portion. When the needle portion is inserted into the storage container by the needle transfer member, a pressure gas such as air is supplied into the storage container by the pressure gas supply member, and blood is measured again through the needle portion as the pressure gas is supplied. Can be supplied to the device.

When the supply of blood through the needle portion is completed, the pressure gas supply member may stop operating, and the needle transfer member may separate the needle portion from the storage container. The needle part and the storage container may be separated from the operator to automatically supply the liquid for viscosity measurement, and the pressure gas supply member may supply the pressure gas at a constant pressure and flow rate by using a stepping motor or a sophisticated driving or pumping device.

In addition, the needle portion may transfer the pressure gas and the sample liquid, respectively, using two needles separated as before, but may prevent the bending and facilitate the insertion and separation using the double needles described below.

For example, the double needle may include an elongated hollow inner needle, a relatively shorter length than the inner needle, the outer needle receiving the inner needle, and a fixing body for fixing both needles. The outer needle and the inner needle are formed hollow, and a flow path for the pressure gas may be formed therebetween. In addition, a flow path connecting the inner needle and an external viscosity measuring device by a fixed body and a flow path connecting the pressure gas source and the flow path for the pressure gas may be provided independently. The double needle can be inserted through the rubber packing of the storage container at one time through the needle conveying member. A pressure gas, such as air, may be supplied to the flow path for the pressure gas, and the end of the inner needle may remain in the blood and then transfer the blood to an external viscosity measuring device.

The container accommodating member includes a constant temperature part, and the storage container accommodated in the accommodating part may be maintained at about 36.5 to 37 ° C. or a specific temperature to prevent the viscosity of the liquid from changing with temperature.

The hematocrit measuring member may include a measuring cell including a working electrode and a receiving electrode spaced apart from each other in the measurement space, and the controller may include a signal generator for supplying a bipolar signal to the working electrode, and the receiving electrode in response to the bipolar signal. It may include a data analysis unit for calculating the electrical conductivity between the electrodes using the electrical signal measured from, the control unit may measure the hematocrit of blood using the measured electrical conductivity.

As used herein, the term "control unit" may be understood as a whole of equipment or circuits for controlling equipment and handling measured values, and may be provided as a single body or separated into two or more components.

When measuring the volume fraction or concentration of red blood cells, ie, hematocrit, using the electrical conductivity, it can be seen that it is very difficult to reflect the plasma resistance or the surface conductance of red blood cells. At this time, by supplying a bipolar signal, that is, a signal repeating (+) and (-) at regular intervals based on a voltage of 0 V, stable measured values reflecting plasma resistance and red blood cell conductance can be obtained. It is possible to solve the deviation of the electrical conductivity caused by.

In addition, providing a bipolar signal as a square wave avoids the change in conductance on the surface of red blood cells, resulting in higher electrical conductivity accuracy. In addition, by using a low-frequency signal of about 10 kHz or less, preferably about 5 kHz, the bipolar signal can solve a decrease in signal in the blood, and minimize the effect of the change in the internal conductivity of red blood cells.

By allowing blood to move horizontally between the working electrode and the receiving electrode in the measurement cell, it is possible to suppress the erythrocyte sedimentation in the blood and to change the electrical conductivity due to the sedimentation of the erythrocytes and the like.

The automatic measuring device of the present invention can be automatically performed from maintaining the temperature of the blood and inserting the needle to supply a certain amount of liquid.

In addition, since the needle is easy to install and detach and the blood can be handled through automation, it is possible to prevent the worker from being stuck or exposed to the blood during the installation and detachment of the needle. You can complete the task you want.

The automatic measuring device of the present invention can reduce the operator's error due to the automated progress, can reduce the dependency on the operator's skill, and can support the same conditions to measure the viscosity of the liquid even if repeated every time.

1 is a perspective view of an automatic oxygen supply capacity measuring apparatus according to an embodiment of the present invention.
FIG. 2 is a perspective view for explaining a state of use of the automatic measuring device of FIG. 1. FIG.
3 is a front perspective view for explaining the transfer part and the viscosity measurement part of FIG.
4 is a rear perspective view of the conveying part of FIG. 3.
FIG. 5 is a front view illustrating the double needle part of FIG. 3. FIG.
FIG. 6 is an exploded view for describing the double needle part of FIG. 5.
7 is an exploded perspective view for explaining the container receiving member of FIG.
8 is a configuration diagram illustrating the function of the hematocrit measurement part of FIG. 3.
FIG. 9 is a perspective view of a measuring cell of the hematocrit measuring part of FIG. 8. FIG.
10 is a cross-sectional view of the measuring cell of FIG. 8.
11 is an exemplary circuit diagram of a measuring apparatus for explaining a hematocrit measuring method.
12 to 18 illustrate signals generated according to a circuit sequence in the process of calculating hematocrit according to the present embodiment.
19 is a front view illustrating the automatic measuring device of FIG. 1.
20 is a front view for explaining the viscosity measuring part of FIG.
21 is a flowchart illustrating a process of measuring the viscosity using an automatic viscosity measuring device according to the present embodiment.
22 are front views for explaining an operation process of the viscosity measuring part.
Fig. 23 is a graph showing the results of using the optical sensor of the viscosity measuring part.
24 is a configuration diagram of an automatic measuring device for explaining another embodiment of the present invention.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS Hereinafter, preferred embodiments of the present invention will be described in detail with reference to the accompanying drawings. However, the present invention is not limited to the embodiments. For reference, the same numbers in this description refer to substantially the same elements and can be described with reference to the contents described in the other drawings under these rules, and the contents which are judged to be obvious to the person skilled in the art or repeated can be omitted.

1 is a perspective view of an automatic oxygen supply capacity measuring apparatus according to an embodiment of the present invention, Figure 2 is a perspective view for explaining a state of use of the automatic measuring apparatus of FIG.

1 and 2, the automatic viscosity measuring device 100 includes a base body 110, a conveying part 200, a viscosity measuring part 400, a hematocrit measuring part 500, a control part 160, and a display. Part 140 is included. A stage 130 is formed on the base body 110, and a transfer part 200, a viscosity measuring part 400, and a hematocrit measuring part 500 are provided to the stage 130. The stage 130 may be selectively opened and closed by the cover 120, and the cover 120 may be in a closed state during storage or operation. When the setting or needle / tool replacement is required, the cover 120 may be temporarily closed ( 120) can be opened.

The control part 160 may use a general personal computer or other controller equipment, and an input part 150 such as a keyboard, a mouse, or a wired or wireless information reading device may be attached to the base body 110 to input necessary information. . As the display part 140, a general monitor or similar equipment may be used, and a printing function may be further added.

The user can open the cover 120 and replace the storage container or needle, flow resistance tube, hematocrit measuring cell, etc., after mounting the storage container to the receiving member, close the cover 120, and close the viscosity measuring device 100 It can work. In some cases, the measurement function of the viscosity measuring device 100 may operate at the same time as the cover 120 is closed, and the cover 120 may be formed of a transparent material to check the progress of the inside.

3 is a front perspective view for explaining the conveying part and the viscosity measuring part of FIG. 1, and FIG. 4 is a rear perspective view of the conveying part of FIG. 3.

3 and 4, the transfer part 200 is for automatically supplying blood from the storage container 20 of the vacuum in which the blood is stored to the hematocrit measuring part 500 and the viscosity measuring part 400. Blood supply member 240 for supplying the blood to the hematocrit measuring part 500 and the viscosity measuring part 400 by supplying the container receiving member 220 for receiving the container 20, the pressure gas to the storage container 20 , A needle transfer member 230, and a pressure gas supply member 250 for adjusting a gap between the needle and the storage container 20. These configurations are mounted on one base plate 210 and can be operated sequentially or simultaneously under the control of the control module. For reference, the viscosity measuring part 400 may measure the viscosity using a flow resistance tube, but may be replaced by a measuring device using various viscosity methods. The hematocrit measurement part 500 also measures the concentration of erythrocytes using electrical conductivity, but it is also possible to configure an automatic measuring device using another hematocrit measurement method.

First, the needle transfer member 230 is mounted to be vertically movable up and down on the base plate 210, and the container receiving member 220 is fixed to the needle transfer member 230. As the needle transfer member 230 moves up and down, the double needle part 300 of the blood supply member 240 may be inserted into the storage container 20. Since the storage container 20 includes the upper silicon packing and the end of the double needle part 300 is sharp, the double needle part 300 may enter the storage container 20 through the silicon packing.

For reference, in this embodiment, the container receiving member 220 is mounted on the needle transfer member 230 and moves, and the blood supply member 240 is fixed. In some cases, the blood supply member moves and the container receiving member is moved. It may be fixed, and in other cases, both the blood supply member and the container receiving member may be provided to move.

The pressure gas supply member 220 may supply a pressure gas such as air, and supply air at a constant pressure, a constant flow rate, or a constant pressure / flow rate. The pressure gas supply member 220 may provide air using a syringe principle as shown, and may provide air using pumping equipment or pumping means of another principle. In this embodiment, the pressure gas supply member 250 includes a scanning unit 260 and a stepping driving unit 270 for moving the piston of the scanning unit 260. The cylinder body 262 of the injection unit 260 is fixed on the base plate 210, and the piston 264 may move up and down through the moving block 276 of the stepping driving unit 270.

Referring to FIG. 4, in addition to the moving block 276 moving along the slit in front of the base plate 210, the stepping driver 270 may correspond to the rotation of the stepping motor 272 and the stepping motor 272. Block guide 274 for moving 276. The movement of the stepping motor 272 allows the moving block 276 to move at a predetermined speed and pressure, and pressurizes the piston 264 through the moving block 276 at a controlled speed and amount of movement.

The needle transfer member 230 also includes a mounting block 236 for mounting the motor 232 and the container receiving member 220, and moves the mounting block 236 up and down by using the driving of the motor 232. Can be. In this case, as in the stepping driving unit 270, a rod guide, a ball screw, or the like may be used, and the motor 232 may be a stepping motor or a linear motor.

The blood supply member 240 includes a needle fixing part 245 for fixing the double needle part 300 and the double needle part 300 on the base plate 210. The needle fixing part 245 can detachably fix the double needle part 300, and can be replaced with a new double needle part 300 every time the blood viscosity is measured. As shown, the double needle portion 300 has a double structure in which the inner needle and the outer needle are formed on the same axis, and the needles of the double structure simultaneously pass through the silicon packing of the storage container 20 to the storage container 20. Can be inserted and removed.

For reference, in the present embodiment, the storage container 20 is a vacuum container for storing blood, and the storage container 20 may contain an anticoagulant to prevent blood from coagulating while measuring the viscosity of the blood. Ethylenediamine tetraacetic acid (EDTA), heparin (heparin) or sodium citrate (sodium citrate) and the like can be used.

FIG. 5 is a front view illustrating the double needle part of FIG. 3, and FIG. 6 is an exploded view illustrating the double needle part of FIG. 5.

5 and 6, the double needle part 300 includes an inner needle 310, an outer needle 320, and a fixing body 330. The inner needle 310 has an end which is cut in an inclined direction to penetrate into soft tissue, and the outer needle 320 is also formed with a larger diameter than the inner needle 310 and has an end that is cut in an inclined direction.

The fixed body 330 may be generally formed through plastic injection, and the outer needle 320 or the inner needle 310 may be formed by insert injection from the time of manufacture, or may be fixed later. . In detail, the fixing body 330 may include an intermediate portion 332, an inner needle fixing portion 336, and an outer needle fixing portion 338. The intermediate portion 332 forms a T-shaped connected passage. When a passage connected in a straight line in the T-shaped passage is vertically disposed, an inner needle fixing portion 336 is mounted at the upper end of the passage, and an outer needle fixing portion 338 is mounted at the lower end thereof. The inner needle fixing part 336 is integrally formed by the inner needle 310 and the insert injection, etc., and the flow path I by the inner needle 310 is separated from the flow path provided by the intermediate part 332. The outer needle fixing part 338 is fixed to the lower end of the middle part 332, and the inner needle 310 passes through the outer needle 320.

A flow path (III) for introducing air is formed between the outer needle 320 and the inner needle 310, and the injection hole 334 formed at the side portion at the middle portion 332 and the discharge hole formed at the lower end thereof are nozzles of the injection portion 260. And a flow path II communicating with the inside of the storage container 20. The air supplied through the hose is provided to the pressure gas inlet 334 of the double needle part 300, and may be introduced into the blood storage container 20 through the flow path II supplied into the fixed body 330. have.

The inner needle fixing part 336 may be fixed through interference fitting or hook coupling at the upper end of the middle part 332, and the outer needle fixing part 338 is fixed by screwing at the lower part of the middle part 332. Can be.

For reference, the double needle portion 300 may be mounted and used in the transfer part 200, but may also be used in other viscosity measuring devices that operate automatically or manually, and the double needle portion 300 may have a concentric structure. Because of this, it is very easy to insert and remove into the storage container.

Referring again to the drawings, by moving the piston 264 of the pressure gas supply member 250, it is possible to move the air to the storage container 20 through the communication flow path (II, III). As the air is introduced, the blood inside may be discharged to the outside through the inner needle 310, and the blood rising through the inner needle 310 may be measured along the other flow path I in the fixing body 330. 400).

7 is an exploded perspective view for explaining the container receiving member of FIG.

Referring to FIG. 7, the container receiving member 220 may include a receiving opening 222 for accommodating the storage container 20, a holder 224 for fixing the receiving opening 222 to the needle conveying member 230, and a male container. It includes a constant temperature unit 226 for maintaining at a temperature of about 36 ~ 37 ℃ around the tool 222. The thermostat 226 may be provided as a silicon heater with a built-in hot wire, and the thermostat 226 may be provided around the storage container 20 by using a tool such as a binding clip. The control part 160 may maintain the temperature of the inside of the receiving port 222 and the storage container 20 uniformly through the constant temperature part 226 of the transfer part 200, and the viscosity of the blood is measured while the viscosity is measured. You can avoid being affected by the change.

8 is a configuration diagram for explaining the function of the hematocrit measurement part of FIG. 3, FIG. 9 is a perspective view of a measurement cell of the hematocrit measurement part of FIG. 8, FIG. 10 is a cross-sectional view of the measurement cell of FIG. 8, and FIG. It is an example circuit diagram of a measuring device for explaining the hematocrit measurement method.

8 to 11, there is shown a measurement part 500 for measuring hematocrit in blood. The hematocrit measurement part 500 includes a measurement cell 520 and may measure hematocrit of blood together with the signal generator 162 and the data analyzer 164 of the controller 160. The blood supply member 240 may supply a quantitative amount of blood to the measuring cell 520, and the blood passes through the electrodes therein while the blood is supplied to the measuring cell 520. The signal generator 162 may supply a bipolar square wave signal for measuring the electrical conductivity of blood, and the data analyzer 164 may calculate the electrical conductivity from the measured electrical signal.

Referring to FIG. 8, hematocrit may be measured using whole blood already obtained from the body and containing anticoagulant. In this case, the blood to be supplied to the measurement cell 520 may be moved using the injection unit 260 or other similar device of the pressure gas supply member 250. When the blood is in the storage container 20 and supplied to the measurement cell 520 along the supply pipe, the AC bipolar square wave voltage signal generated in the circuit of the signal generator 162 is sent to the two electrodes of the measurement cell 520. This signal causes a current to flow through the blood inside the measurement cell 520.

In general, this current value is inversely proportional to the amount of red blood cells in the blood, and the measured current value can be used to calculate the resistance, from which the electrical conductivity can be calculated. 9 and 10, the measuring cell 520 for measuring electrical conductivity largely includes a working electrode 522, a receiving electrode 524, and an insulating structure 526. The insulating structure 526 may be provided between the electrodes and both ends of the electrode to insulate the electrodes, and may be formed in a hollow shape to provide a measurement space 528 therein.

The working electrode 522 and the receiving electrode 524 may be manufactured using stainless steel 304L, and the size of the working electrode 522 and the receiving electrode 524 may be about 1/4 inch in diameter and about 1.5 cm in length. In order to prevent erythrocyte sedimentation that occurs naturally due to gravity, the measuring cell 520 may be designed in a horizontal shape such that the measuring space 528 is horizontally connected, and as shown, two fixing clip electrodes 550. Can be electrically connected to the circuit and fixed at the same time.

The internal volume of the measurement space 528 in which the two electrodes are combined within the measurement cell 520 may be about 1.2 mL, and the measurement cell 520 may be detached and electrically connected by the fixing clip electrode 550. . The fixing clip electrode 550 can easily make an electrical connection, it is also possible to use the electrical conductivity measuring cell 520 for a single use.

The measuring cell 520 is connected to the storage container 20 through a supply pipe and receives blood by the blood supply member 240, but in some cases, both blood collection tubes in the middle of the blood collection tube even while blood is collected from the human body. By inserting the end, hematocrit can be easily measured. In addition, hematocrit may be measured by simply installing the measuring cell 520 before the blood infusion unit in other blood test equipment.

Referring back to the drawings, it can be described the internal circuit constituting the hematocrit measuring part 500. Referring to FIG. 11, the signal generator 162 may be formed before the measurement cell 520, and then the data analyzer 164 may be formed thereafter.

The circuit is designed to generate a bipolar square wave voltage signal and send it to the measurement cell 520. In order to prevent oxidation on the electrode surface, a voltage of about 50 mV may be used, and a bipolar method may be used to prevent polarization. Thus, the applied voltage signal can form a square wave of peak to peak about 100 mV.

In order to prevent the electrical signal from decaying due to the insulation effect by the blood, a frequency of about 5 kHz can be used, and by using the signal in the low frequency region, it is possible to prevent the red blood cells from conducting by high frequency signals. Whole blood can lead to constant resistance.

The voltage of the bipolar signal consisting of (+) and (−) is supplied to the circuit, and a square wave may be generated by the signal generator 162 (eg, CMOS schmidt trigger relaxation oscillator) connected thereto. At this time, the supply voltage can be precisely set by about 2.5V Zener diodes. The square wave generated by the signal generator 162 may be scaled to 100 mV by a precision divider and supplied to the electrical conductivity measuring cell 520.

The current generated by the square wave supplied to the measuring cell 520 is in ㎂, and the op-amp circuit can be designed to receive this square wave signal and output a 5 mV peak output voltage per ㎂. The output voltage may represent a large output value by 2 or 3 times depending on the degree of resistance of the blood by a scaling switch.

According to the above-described output voltage value, the digital voltmeter (3 1/2 digital LCD) may display the current value measured by the electrical conductivity measuring cell 520 within the range of about 0-199.9.

The electrical conductivity G [S or mS] measured in this example is calculated as follows using Ohm's law as the inverse of the resistance.

Here, R _cell means a resistance value measured in the measurement cell 520 in which blood flows. In order to standardize the electrical conductivity value according to the shape difference of the measurement cell 520, a specific conductivity C [S / m or μS / m] is used and can be defined as follows.

Where d is the distance between the two electrodes and A is the total area of the two electrodes.

, 는 본래 두 전극의 총 면적과 두 전극 간의 거리의 비로 다음과 같이 나타낸다.Cell constant K (

Is the ratio of the total area of the two electrodes to the distance between the two electrodes.

However, since this formula does not take into account the resistance and fringe of the fringe electric field occurring at the interface of the electrode, the K value can usually be obtained by calibration with a standard electrical conductivity solution, which is known for its electrical conductivity. have.

12 to 18 illustrate signals generated according to a circuit sequence in the process of calculating hematocrit according to the present embodiment.

Referring to FIG. 12, in the circuit diagram of FIG. 11, A1 and A2 generate a drive signal of the circuit at 5 kHz. The waveform generated at pin 4 of the A2 device is as shown. In order to verify that the applied driving waveform shows a duty cycle of 50%, the signal was passed through the counter of the A3 device, and the waveform was checked at the pin 1 of the A3 device of the counter output. Is the same as

Since the amplitude of the square wave can be changed by an inaccurate supply voltage, it can be stabilized using a Q1 device, a Q2 device, and a precision reference diode and a Zener diode. The square wave signal is connected to ground (voltage 0) at each end to implement an accurate bipolar signal. Accordingly, the voltage waveforms at the positive electrode (light blue line) and the negative electrode (dark blue line) are shown in FIG. 14. Same as

When the voltages summed by the resistors R5 and R6 are measured at the other resistor R19, the 100 mV peak-to-peak value can be confirmed as shown in FIG. The signals at pins 3 and 6 of OPAMP U1 are measured as shown in FIG. 15, and the same signal can be implemented in a U1 unity gain amplifier.

The current value output from the measurement cell 520 is converted into a voltage signal at the op amp U2, and the conversion may be set in three steps by adjusting a gain setting. For example, if you set the Gain setting to the 1X position, the output meter will display the current value output from 측정 from the measurement cell 520, and if it is set to the 2X or 3X position, the output meter will display the existing value. Can be divided by 2 or 3. After placing the setting in the 1X position, the serrated signal measured at pin 6 of the U2 circuit is shown in FIG.

Circuits U3 and U4 are for amplifying the absolute value of the current output from the measuring cell 520. When measured at pin 7 of the circuit U4, the waveform is as shown in FIG. As shown in FIG. 17, the current amplified to an absolute value is represented by a voltage through a voltage meter as indicated by the index line, which may be associated with the current value output from the measuring cell. For example, when the measured voltage is 1.21 V, the current output from the measuring cell may mean 121 mA.

The signals of FIG. 18 are measured in circuits U5-A and U5-B, and the dark blue color displayed horizontally is a DC level signal superimposed on the amplified signal of FIG. The switch S2 is intended to be able to select whether to display on the screen as the average value or peak value of the signal. In the case of FIG. 18, the peak value is about 1.77 V, which means that a current of 177 mA is output from the measurement cell.

As a result, a bipolar square wave voltage signal can be generated using the circuit developed through the present embodiment, and the square wave applied to the measuring cell outputs a current proportional to the electrical conductivity of the blood, and then reads the current signal again. As shown in FIG. 18, it is possible to finally measure a very stable current value.

The measurement method used in the present embodiment is very stable, no noise, and in particular, red blood cell sedimentation does not occur even while blood flows through the measurement cell 520, so that the deviation of the output value does not occur during measurement.

Referring to FIG. 3 again, the storage container 20 in which the blood is stored stores the blood in a vacuum state and is fixed to the container receiving member 220. The container accommodating member 220 may be fixed to the needle transfer member 230 to move vertically up and down with the storage container 20, and as shown in FIG. 19, the blood storage container 20 is fixed upward while rising. The needles 310 and 320 of the double needle part 300 may be inserted into the blood storage container 20 through the silicon packing.

In this case, the needle transfer member 230 may sense an appropriate position of the storage container 20 using the sensors 238 and 239. In the double needle part 300, the inner needle 310 is immersed in blood and the outer needle. 320 may transfer the storage container 20 to the exposed position.

In order to easily control the position of the double needle part 300, a display for displaying an appropriate position may be formed on the outer surface of the inner needle 310 or the outer needle 320. The container transfer unit 240 may further raise or lower the blood storage container 20 according to the display, and adjust the height of the container according to the depth even while blood is supplied. Meanwhile, in the present embodiment, the sensors 238 and 239 are mounted on the side of the base plate 210, and the moving distance of the container accommodating member 220 or the needle conveying member 230 is adjusted using the sensors 238 and 239. I can measure it.

Since the inner needle 310 and the outer needle 320 are located on the same axis, the needles 310 and 120 may not be bent or bent while the blood storage container 20 is raised. The insertion and removal of the fields 310 and 320 is very simple and safe.

Referring to the drawings, it may further include a thermostat 280 on the base plate 210. The thermostat 280 is also for temporarily storing another storage container storing blood to be measured viscosity, and may include a heating element for maintaining the temperature of the internal or storage container at about 36 ~ 37 ℃, the measurement target During the measurement of the blood viscosity of the storage container 20, the viscosity of the blood in the air can be maintained so as not to change.

Four receiving ports are formed in the thermostat 280, but in some cases, the number thereof may be changed, and one or more may be variously selected. In addition, the thermostat 280 may also be disposed at another position adjacent to the base plate 210 of the transfer part 200.

20 is a front view for explaining the viscosity measuring part of FIG.

3 and 20, the viscosity measuring part 400 has three directions for controlling the supply of blood to two vertical resistance tubes 412 and 414 and vertical resistance tubes 412 and 414 having lower ends interconnected thereto. Adjacent to the three-way valve 460, the capillary region 430 provided at the vertical resistance tubes 412 and 414, or a connection portion thereof, and the vertical resistance tubes 412 and 414, respectively. Optical sensors 440 and 450 for measuring height changes.

The vertical resistance tubes 412 and 414 may be supplied for single use as a U tube 410 provided in a U-shape connected to the lower end, and the lower portions of the separately provided resistance tubes may be integrally connected by assembly and the three-way valve ( 460 may be provided in a tubular structure of another shape that is integrally connected. In the viscosity measuring part 400, the vertical resistance tubes 412 and 414 are fixed through the fixing bracket 419, and may be replaced with another new resistance tube for the next blood viscosity measurement after measuring the viscosity using blood.

Valves may be provided on one side of the vertical resistance tubes 412 and 414. In this embodiment, the valve 460 is for controlling the inflow of blood passing through the hematocrit measuring part 500, and may block the flow of liquid or change the flow path. In this embodiment, the three-way valve 460 is connected to the lower portion of one vertical resistance tube 412 and provides the blood supplied from the transfer part 200 to one vertical resistance tube 412 to a predetermined height thereafter. The other vertical resistor tubes 414 may be provided to different predetermined heights, and both vertical resistor tubes 412 and 414 may be interconnected. In addition, the three-way valve 460 can be controlled by the solenoid actuator 465 built into the viscosity measuring part 400, the control part 160 is a three-way valve 460 through the solenoid actuator 465 ) Can be controlled.

A plurality of optical sensors 440 and 450 are provided respectively corresponding to the positions where the vertical resistance tubes 412 and 414 are mounted. For example, these optical sensors 440 and 450 are configured as LED-CCD arrays. Can be. The optical sensors 440 and 450 are for measuring a change in the surface of blood, which is repeatedly rising and falling in the vertical resistance tubes 412 and 414, and are used for detecting height change or speed change over time. Can be provided.

In this embodiment, the viscosity measuring part 400 is provided in a structure that can be opened and closed by the lower end is connected to the hinge 405, a plurality of optical sensors (440, 450) to the rear of the vertical resistance tubes (412, 414) It is provided in a vertical arrangement. The front cover 405 of the viscosity measuring part 400 corresponding to the optical sensors 440 and 450 is provided with a reflector plate or a reference plate 442 for operating the LED-CCD array sensor, and the front cover 405 is closed. Under the conditions, that is, in the state of completely blocking all the light coming from the outside can further increase the sensitivity of the optical sensor (440, 450). Of course, also in this case, an optical sensor in which the light emitting portion and the light receiving portion are located on opposite sides of the vertical resistance tube may be used.

Hereinafter, a process of measuring the viscosity of blood stored in the vacuum storage container 20 by using the automatic viscosity measuring device 100 will be described.

FIG. 21 is a flowchart illustrating a process of measuring viscosity using an automatic viscosity measuring device according to the present embodiment, FIG. 22 is a front view illustrating a process of operating the viscosity measuring part, and FIG. 23 is a view illustrating a viscosity measuring part. It is a graph showing the results using the optical sensor.

Referring to FIG. 21, the disposable U tube 410 is mounted on the fixing bracket 419 of the viscosity measuring part 400 (S11), and the information of the disposable U tube 410 is recognized. In this embodiment, the RFID tag 470 may be mounted at one end of the U tube 410, and the viscosity measuring part 400 is not shown, but the degree of the U tube 410 through the RFID reader, for example, Information such as the resistance tube and capillary size and length may be input (S12).

There is a temperature measuring sensor in the fixed bracket (419) or other parts of the viscosity measuring part 400 to determine whether the U tube 410 is 37 degrees or a predetermined temperature (S13), if the measurement conditions are confirmed, the blood transfer part automatically 200 may start operation (S14).

First, the supplied blood passes through the measuring cell 520 of the hematocrit measuring apparatus 500, and the hematocrit of the blood may be measured while measuring the electrical conductivity while supplying a square wave to the blood (S15).

At this time, the three-way valve 460 connects the left vertical resistance tube 412 first, and receives the blood passing through the hematocrit measuring part 500 (see FIG. 22A). In this case, blood may be supplied to a predetermined reference height 416 predetermined to the left vertical resistance tube 412 (S16) (see FIG. 22B). The height of the blood can be checked through the optical sensor 440.

After the blood is filled in the left vertical resistance tube 412, the blood may be supplied to the right vertical resistance tube 414 through the capillary region by the operation of the valve 460 (S17) (see FIG. 22B). ). The height of blood filled in the vertical resistance tube 414 on the right side may also be limited to a predetermined height 418, and the blood height may also be checked using the optical sensor 450 (S18) (FIG. 22 ( c) reference). At this time, the blood height of the right vertical resistance tube 414 is preferably lower than the blood height of the left vertical resistance tube 412.

After filling the blood up to a predetermined height, the three-way valve 460 cuts off the blood supply from the transfer part 200 and connects the left and right vertical resistance pipes 412 and 414, and as a result, the left vertical resistance pipe 412. Blood flows to the right vertical resistance tube 414 from (S19) (see Fig. 22 (d)).

The change in blood height in the left and right vertical resistance tubes 412 and 414 with time can be confirmed through FIG. 23. Referring to FIG. 23, the x axis is second, and the y axis is pixel number in the optical sensors 440 and 450. Most importantly for the measurement of blood viscosity, an optical sensor (LED-CCD Array) 440 located in the left vertical resistance tube 412 detects the height change of blood as the blood is injected, and detects the height change over time. The change h (t) may be transmitted to the control part 160. Here, when the blood comes in at a too high speed, the optical sensor 440 cannot read the height change properly. In the related art, a problem occurs because a person manually pushes air into the storage container 20 with a needle. This is because, unless you are a very skilled person, you don't know how fast you should push the air slowly, and if you push it a little faster, the optical sensor 440 can't read the change in height, causing an "operational error" and measuring blood viscosity. Because you can't. Conversely, if you push the air too slowly, you will get an "operation error" as well, because the entire blood viscosity calculation algorithm is designed to complete in three minutes, because it measures the position of the pixel every 0.02 seconds and transmits the data. If you spend too much time injecting blood too slowly into the left vertical resistance tube, you will not be able to complete the required height changes in three minutes and you will not be able to measure blood viscosity.

For reference, in FIG. 23, A is a point at which blood starts to enter the left vertical resistance tube 412 from the transfer part 200, and B is a point where the blood reaches a predetermined position 416 in the left vertical resistance tube 412. It's a moment of arrival. The inclination of A and B here should not be too large or too small to allow the optical sensor 440 to measure the correct height. To this end, the transfer part 200 should put air into the vacuum storage container 20 at the optimum speed through the control of the control part 160, blood is left vertical at the speed most suitable for the optical sensor 440 to operate. It should be injected into the resistance tube 412 to allow stable height measurement without "operational error."

After point B, the three-way valve 460 connects the transfer part 200 with the capillary region 430, and blood flows from the reservoir 20 through the capillary region 430 to the right vertical resistance tube 414. Move. Thus, from the point B to the point C, the height of the left vertical resistance tube 412 does not change any more and appears as a parallel line. During this time, the right vertical resistance tube 414 may have a height of zero because blood has not yet arrived. Point C is a moment when blood arrives at a predetermined reference height 418 at the right vertical resistance tube 414, and the three-way valve connects the left vertical resistance tube and the right vertical resistance tube. From this moment, blood moves from the left vertical resistor tube through the capillary region 430 to the right vertical resistor tube 414. Therefore, the height of the blood in the left vertical resistance tube gradually decreases, on the contrary, the height of the blood in the right vertical resistance tube 414 gradually increases.

24 is a configuration diagram of an automatic measuring device for explaining another embodiment of the present invention.

Referring to FIG. 24, the blood supply member may be connected in series or in parallel with the hematocrit measuring part and the viscosity measuring part. For example, as shown in (a), the hematocrit measuring part 500 may be connected to be located later than the viscosity measuring part 400. At this time, the viscosity measuring part 400 is first supplied with blood from the storage container 20 through the blood supply member, the blood in the process of discharging the blood after measuring the viscosity of the measuring cell 520 of the hematocrit measuring part 500 ) Can be passed.

Also, as shown in (b), the hematocrit measuring part 500 may be connected in parallel with the viscosity measuring part 400. In this case, the blood may be supplied to both the viscosity measuring part 400 and the hematocrit measuring part 500 through the central valve, or blood may be sequentially supplied sequentially.

As described above, although described with reference to the preferred embodiment of the present invention, those skilled in the art various modifications and variations of the present invention without departing from the spirit and scope of the invention described in the claims below I can understand that you can.

100: automatic viscosity measuring device 120: cover
130: Stage 140: Display parts
150: input part 160: control part
200: blood supply member 210: base plate
220: container accommodation member 230: needle transfer member
240: liquid supply member 250: pressure gas supply member
300: dual needle 310: internal needle
320: external needle 330: fixed body
400: viscosity measurement part 410: U tube
412 and 414: vertical resistance tube 430: capillary region
440 and 450: optical sensor 460: valve
500 ： Hematocrit Measuring Part

Claims (16)

In the oxygen supply capacity index automatic measuring device for automatically extracting blood from the storage container storing the blood to measure the oxygen supply capacity index of the blood,
A container receiving member for receiving the storage container;
A blood supply member for supplying blood from the storage container accommodated in the container receiving member;
A viscosity measuring member for measuring the viscosity of the blood using blood supplied from the blood supply member;
A hematocrit measuring member for measuring hematocrit of the blood using blood supplied from the blood supply member; And
And a control unit for calculating an oxygen supply capacity index of blood using the viscosity of the blood and the hematocrit value obtained from the viscosity measuring member and the hematocrit measuring member. The method of claim 1,
Blood supplied from the blood supply member is passed through the hematocrit measuring member is delivered to the viscosity measuring member, characterized in that the automatic oxygen supply capacity index of blood. The method of claim 1,
At least a portion of the blood supplied from the blood supply member, the oxygen supply capacity index automatic measurement apparatus of the blood, characterized in that the viscosity is used in the viscosity measurement member and then supplied to the hematocrit measurement member. The method of claim 1,
The viscosity measuring member and the hematocrit measuring member is connected in parallel, the blood oxygen supply capacity index automatic measuring device, characterized in that the blood supply from the blood supply at the same time or sequentially. The method of claim 1,
The blood supply member includes a needle portion located adjacent to the storage container accommodated in the container receiving member and a needle fixing portion for fixing the needle portion,
A needle transfer member for inserting a portion of the needle portion into the storage container by adjusting a distance between the storage container and the needle portion, and a pressure gas supply member for supplying pressure gas into the storage container through the needle portion; Automatic oxygen supply capacity index measuring device comprising a. The method of claim 5,
The vessel receiving member is mounted on the needle transfer member, and the needle transfer member inserts or separates the needle portion into the storage container by approaching or retracting the vessel receiving member to the needle portion. Supply index automatic measuring device. The method of claim 5,
The needle part,
Elongated hollow inner needles;
An outer needle receiving the inner needle to form a flow path for the inner needle and the pressure gas; And
A fixed body for independently providing a flow path for connecting the inner needle and the external viscosity measuring device and a flow path for connecting the pressure gas supply member and a flow path for the pressure gas, and fixing the inner needle and the outer needle;
Automatic oxygen supply capacity index measuring apparatus comprising a blood. The method of claim 1,
The hematocrit measuring member includes a measuring cell including a working electrode and a receiving electrode spaced apart from each other in the measuring space.
The control unit includes a signal generator for supplying a bipolar signal to the working electrode, and a data analyzer for calculating the electrical conductivity between the electrodes using an electrical signal measured from the receiving electrode in response to the bipolar signal,
Blood oxygen supply capacity index automatic measuring device, characterized in that for measuring the hematocrit of the blood by using the measured electrical conductivity. 9. The method of claim 8,
The signal generation unit generates a square wave (square wave), the oxygen supply capacity index automatic measurement device of blood. 10. The method of claim 9,
The square wave is a blood oxygen supply capacity index automatic measurement device, characterized in that the low frequency signal of less than 10kHz. 9. The method of claim 8,
And the operating electrode and the receiving electrode in the measuring cell are arranged horizontally. The method of claim 1,
The storage vessel is a vacuum vessel automatic oxygen supply capacity index measuring apparatus, characterized in that the vacuum vessel. The method of claim 1,
And said storage container contains an anticoagulant for preventing the coagulation of liquid during the measurement of the viscosity of the blood. The method of claim 13,
The anticoagulant is ethylenediamine tetraacetic acid (EDTA), heparin (heparin) or sodium citrate (sodium citrate) characterized in that the blood oxygen supply capacity index automatic measuring device. The method of claim 1,
The viscosity measuring member,
Two vertical resistance pipes of which lower ends are interconnected, a valve for supplying blood to the vertical resistance pipe, a capillary region provided at the vertical resistance pipe or a connecting portion thereof, and are mounted adjacent to the vertical resistance pipe, Automatic measurement device of oxygen supply capacity index of blood, characterized in that it comprises an optical sensor for measuring the height of the change over time. 16. The method of claim 15,
The valve is a three-way valve, and sequentially supplies the blood supplied from the blood supply member to the two vertical resistance tubes, respectively, so that the level of blood supplied to the two vertical resistance tubes to form a constant difference, Automatic measurement of oxygen supply capacity index of blood, characterized in that the supply of the vertical resistance tube is cut off from the blood supply member and the vertical resistance tube is interconnected to allow blood of a relatively high level to move to low level blood. Device.

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