JP2007105148A - Blood purifying device and method of computing recirculation rate - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a blood purifying device capable of predicting the recirculation rate even if the flow rate of the blood flowing in an access region of a patient is smaller than the quantity of the extracorporeally circulated blood and if the recirculation rate of the actually generated recycle of blood is smaller than the detection sensitivity of a detection means; and a method of computing the recirculation rate. <P>SOLUTION: The blood purifying device has an arithmetic operation means 11 capable of operating the recirculation rate, a rate of the quantity of recirculated blood returned from a vein side blood circuit to the patient to be guided again to flow to an artery blood circuit to the quantity of the extracorporeally circulated blood, by applying a prescribed mark to the extracorporeally circulated blood and detecting the mark. The blood purifying device also has a prediction means 12 capable of computing the recirculation rate when the quantity of the extracorporeally circulated blood is temporarily increased from a prescribed flow rate, and predicting the recirculation rate when the quantity of the extracorporeally circulated blood is the prescribed flow rate based on the computed recirculation rate. <P>COPYRIGHT: (C)2007,JPO&INPIT

Description

  The present invention relates to a blood purification apparatus for purifying a patient's blood while circulating it outside the body, and a recirculation rate calculation method thereof.

  In general, in blood purification therapy such as dialysis treatment, a blood circuit composed of a flexible tube is used to circulate a patient's blood extracorporeally. This blood circuit is mainly composed of an arterial blood circuit in which an arterial puncture needle for collecting blood from a patient is attached to the tip, and a venous blood circuit in which a venous puncture needle for returning blood to the patient is attached to the tip. The dialyzer is interposed between the arterial blood circuit and the venous blood circuit to purify blood circulating outside the body.

  In such a dialyzer, a plurality of hollow fibers are arranged inside, and blood passes through the inside of each hollow fiber, and on the outside thereof (between the outer peripheral surface of the hollow fiber and the inner peripheral surface of the housing). It is set as the structure which can flow a dialysate. The hollow fiber has a blood purification membrane with micropores (pores) formed in the wall surface, and waste products of blood passing through the hollow fiber permeate the blood purification membrane and are discharged into the dialysate. At the same time, waste blood is discharged and purified blood returns to the patient's body. In the dialysis machine, a water removal pump for removing water from the patient's blood is disposed, and water removal is performed during dialysis treatment.

  By the way, for example, when an arterial puncture needle and a venous side puncture needle are punctured around the patient's shunt (access site where the artery and vein are connected by surgery) and the periphery thereof, the extracorporeal circulation is performed. Blood recirculation may occur in which blood that has been purified and returned to the patient's body is reintroduced from the arterial puncture needle without passing through the patient's organ or the like. When such blood recirculation occurs, the purified blood is further circulated extracorporeally, and the amount of extracorporeal blood that needs to be purified decreases accordingly, resulting in a problem that blood purification efficiency deteriorates. End up.

However, in the past, a steep and short-time concentration mark is added to blood circulating extracorporeally, and the mark (concentration lump) is detected by a detector, and blood concentration changes in the obtained mark are indicated. There has been proposed a dialysis apparatus capable of calculating a recirculation rate from the area ratio of detection signals (see, for example, Patent Document 1). According to the dialysis apparatus disclosed in this document, the recirculation rate can be measured in a short time.
JP-T-2001-502590

However, the conventional blood purification apparatus has the following problems.
When the flow rate of blood flowing through the access site is smaller than the extracorporeal blood volume due to stenosis at the patient's access site (access blood vessels such as shunts), Circulation is thought to occur. That is, when trying to perform extracorporeal circulation at a specified flow rate by driving a blood pump, blood flows from the venous puncture needle to the arterial puncture needle if the blood flow rate in the access blood vessel such as a shunt is insufficient. Blood recirculation occurs.

  In such a case, when blood recirculation actually occurs, but the recirculation rate is lower than the detection sensitivity of the detection means (detector), the detection means does not detect the mark and the recirculation is measured. Since the circulation rate becomes 0, there is a problem that it is difficult to always accurately measure the recirculation rate. That is, since the detection accuracy of the mark by the detecting means is limited, there may be a case where a very small amount of blood recirculation cannot be detected.

  The present invention has been made in view of such circumstances, and the flow rate of the blood flowing through the patient's access site is smaller than the extracorporeal blood volume, and the blood recirculation actually occurs. An object of the present invention is to provide a blood purification apparatus capable of predicting the recirculation rate even when the rate is smaller than the detection sensitivity of the detection means, and a method for calculating the recirculation rate.

  The invention according to claim 1 is a blood circuit comprising an arterial blood circuit and a venous blood circuit for extracorporeal circulation of blood collected from an access site of a patient, a blood pump disposed in the arterial blood circuit, A blood purification means for purifying blood flowing through the blood circuit connected between the arterial blood circuit and the venous blood circuit, and a mark for giving a predetermined mark to the blood circulating outside the body in the blood circuit An applying means; a detecting means for detecting the mark given by the mark giving means; and the blood returned to the patient from the venous blood circuit based on the mark detected by the detecting means again to the arterial blood In a blood purification apparatus comprising a computing means capable of computing a recirculation rate that is a ratio of a recirculation blood volume flowing through a circuit to an extracorporeal blood volume, the extracorporeal blood volume is controlled by controlling the blood pump A recirculation rate is calculated when the recirculation rate is temporarily increased from the specified flow rate, and a predicting means that can predict the recirculation rate when the extracorporeal blood volume is set to the specified flow rate based on the recirculation rate is provided. It is characterized by that.

The invention according to claim 2 is the blood purification apparatus according to claim 1, wherein the predicting means is a recirculation rate (α) in an extracorporeal blood volume (Qb) temporarily increased from a specified flow rate (Qb ₀ ). calculates the, along with determining the recirculation rate (alpha) from a blood flow through the patient's access site shunt flow (Qf), extracorporeally circulating blood flow based on the shunt flow (Qf) is defined flow rate (Qb ₀ ) And calculating the recirculation rate (α ₀ ).

According to a third aspect of the present invention, in the blood purification apparatus according to the second aspect, the prediction means is shunt flow rate (Qf) = (1−recirculation rate (α)) × (extracorporeal blood volume (Qb)). The shunt flow rate (Qf) in the extracorporeal circulating blood volume (Qb) temporarily increased by the arithmetic expression is obtained, and the recirculation rate when the extracorporeal circulating blood volume is set to the specified flow rate (Qb ₀ ) by the arithmetic expression. (Α ₀ ) is calculated and predicted.

  According to the fourth aspect of the present invention, blood collected from a patient's access site is circulated extracorporeally in a blood circuit composed of an arterial blood circuit and a venous blood circuit, and between the arterial blood circuit and the venous blood circuit. The blood purification means connected to the blood circuit purifies the blood and gives a predetermined mark to the blood circulating extracorporeally in the blood circuit, while detecting the mark from the venous blood circuit In the recirculation rate calculation method of the blood purification apparatus for calculating the recirculation rate, which is the ratio of the recirculation blood volume that the blood returned to the patient is guided to the arterial blood circuit again to the extracorporeal blood volume, the extracorporeal circulation It calculates the recirculation rate when the blood volume is temporarily increased from the specified flow rate, and predicts the recirculation rate when the extracorporeal blood volume is set to the specified flow rate based on the recirculation rate. To.

The invention according to claim 5 is the method for calculating the recirculation rate of the blood purification device according to claim 4, wherein the recirculation rate (αb) in the extracorporeal blood volume (Qb) temporarily increased from the specified flow rate (Qb ₀ ). ) And a shunt flow rate (Qf), which is a blood flow rate flowing through the patient's access site, is obtained from the recirculation rate (α), and the extracorporeal blood volume is determined based on the shunt flow rate (Qf). ₀ ), the recirculation rate (α ₀ ) is calculated and predicted.

The invention according to claim 6 is the method for calculating the recirculation rate of the blood purification device according to claim 5, wherein shunt flow rate (Qf) = (1−recirculation rate (α)) × (extracorporeal blood volume (Qb)). The shunt flow rate (Qf) in the extracorporeal blood volume (Qb) temporarily increased by the following arithmetic expression is obtained, and recirculation is performed when the extracorporeal blood volume is set to the specified flow rate (Qb ₀ ) by the arithmetic expression. It is characterized by calculating and predicting the rate (α ₀ ).

  According to the present invention, the recirculation rate when the extracorporeal blood volume is temporarily increased from the specified flow rate is calculated, and the recirculation rate when the extracorporeal blood volume is set to the specified flow rate based on the recirculation rate is calculated. Since the circulation rate is predicted, the flow rate of blood flowing through the patient's access site is smaller than the extracorporeal blood volume, and although the blood recirculation actually occurs, the recirculation rate is smaller than the detection sensitivity of the detection means. Even in this case, the recirculation rate can be predicted.

Hereinafter, embodiments of the present invention will be specifically described with reference to the drawings.
The blood purification apparatus according to the present embodiment is for purifying a patient's blood while circulating it extracorporeally, and is applied to a dialysis apparatus used in dialysis treatment. As shown in FIG. 1, such a dialysis machine is mainly composed of a blood circuit 1 to which a dialyzer 2 as blood purification means is connected, and a dialysis machine body 6 for removing water while supplying dialysate to the dialyzer 2. . As shown in the figure, the blood circuit 1 is mainly composed of an arterial blood circuit 1a and a venous blood circuit 1b made of a flexible tube. The arterial blood circuit 1a and the venous blood circuit 1b A dialyzer 2 is connected between them.

  The arterial blood circuit 1a has an arterial puncture needle a connected to the tip thereof, and an iron-type blood pump 3 and first detection means 5a disposed in the middle. On the other hand, a venous puncture needle b is connected to the distal end of the venous blood circuit 1b, and a second detection means 5b and a drip chamber 4 for removing bubbles are connected to the venous blood circuit 1b.

  When the blood pump 3 is driven in a state where the arterial puncture needle a and the venous puncture needle b are punctured into the patient's shunt (access site where the artery and vein are connected by surgery), the blood of the patient is After being collected from the access site, it reaches the dialyzer 2 through the arterial blood circuit 1a, blood purification is performed by the dialyzer 2, and the patient passes through the venous blood circuit 1b while being defoamed in the drip chamber 4. Return to your body. That is, the blood of the patient is purified by the dialyzer 2 while circulating outside the body by the blood circuit 1.

  The dialyzer 2 is formed with a blood introduction port 2a, a blood outlet port 2b, a dialysate inlet port 2c, and a dialysate outlet port 2d in the casing. Among these, the blood inlet port 2a has an arterial blood circuit 1a. The base end of the venous blood circuit 1b is connected to the blood outlet port 2b. The dialysate introduction port 2c and the dialysate lead-out port 2d are connected to a dialysate introduction line L1 and a dialysate discharge line L2 extending from the dialyzer body 6, respectively.

  A plurality of hollow fibers are accommodated in the dialyzer 2, the inside of the hollow fibers is used as a blood flow path, and the flow of dialysate is between the hollow fiber outer peripheral surface and the inner peripheral surface of the housing. It is considered a road. A hollow fiber membrane is formed in the hollow fiber by forming a large number of minute holes (pores) penetrating the outer circumferential surface and the inner circumferential surface, and impurities in the blood are passed through the membrane in the dialysate. It is comprised so that it can permeate | transmit.

  On the other hand, as shown in FIG. 2, the dialysis machine main body 6 bypasses the dual pump P formed across the dialysate introduction line L1 and the dialysate discharge line L2 and the dual pump P in the dialysate discharge line L2. It is mainly comprised from the connected bypass line L3 and the water removal pump 8 (marking provision means) connected to this bypass line L3. One end of the dialysate introduction line L1 is connected to the dialyzer 2 (dialyte introduction port 2c), and the other end is connected to a dialysate supply device 7 for preparing a dialysate having a predetermined concentration.

  One end of the dialysate discharge line L2 is connected to the dialyzer 2 (dialysate outlet port 2d), and the other end is connected to a waste fluid means (not shown). The dialysate supplied from the dialysate supply device 7 After reaching the dialyzer 2 through the dialysate introduction line L1, it is sent to the waste fluid means through the dialysate discharge line L2 and the bypass line L3. In the figure, reference numerals 9 and 10 denote a heater and a deaeration means connected to the dialysate introduction line L1.

  The dewatering pump 8 is for removing water from the blood of the patient flowing through the dialyzer 2. That is, when the dewatering pump 8 is driven, since the duplex pump P is a fixed type, the volume of liquid discharged from the dialysate discharge line L2 is larger than the amount of dialysate introduced from the dialysate introduction line L1. Thus, water is removed from the blood by the large volume. In addition, you may make it remove a water | moisture content from a patient's blood by means other than this water removal pump 8 (for example, what utilizes what is called a balancing chamber etc.).

  Here, the water removal pump 8 as the mark providing means of the present embodiment can perform water removal abruptly and in a short time in addition to water removal necessary for dialysis treatment. That is, water removal at a constant rate performed during dialysis treatment is temporarily stopped (however, extracorporeal circulation is performed), and when the measured hematocrit value is stabilized, the water removal pump 8 is driven rapidly and for a short time. By performing water removal, it is configured so that a peculiar peak can be given to a change in blood concentration (hematocrit value) during that time. Here, the term “abrupt and short time” in the present invention means a size and time enough to confirm the pulse applied after passing through the circuit, and “specific” means fluctuations in the pump and the body of the patient. It can be distinguished from fluctuation patterns due to other factors caused by movement.

  More specifically, as shown in FIG. 3, at a time t1, water removal at a constant rate (normal water removal) is stopped, and thereafter, when the measured hematocrit value reaches a stable time t2. The water pump 8 is driven at a higher speed than usual until time t3. The time t2 to t3 is a minute time. Thereby, compared with normal water removal, water removal can be performed rapidly and in a short time, and for example, a specific peak can be given in the hematocrit value as shown in FIG.

  The first detection means 5a and the second detection means 5b are disposed in the arterial blood circuit 1a and the venous blood circuit 1b, respectively, and detect the concentration (specifically, hematocrit value) of blood flowing through these circuits. Is used to detect the mark given by the water removal pump 8 (a specific peak given to a change in blood concentration (hematocrit value) by rapid and short-time water removal). These first detection means 5a and 5b are composed of a hematocrit sensor. The hematocrit sensor includes, for example, a light emitting element such as an LED and a light receiving element such as a photodiode, and irradiates the blood with light from the light emitting element. A hematocrit value indicating the blood concentration of the patient is detected by receiving the transmitted light or the reflected light with a light receiving element.

  Specifically, a hematocrit value indicating the blood concentration is obtained based on the electrical signal output from the light receiving element. That is, each component of blood such as red blood cells and plasma has its own light absorption characteristics, and this property is used to quantify the red blood cells necessary for measuring the hematocrit value electro-optically. Thus, the hematocrit value can be obtained. More specifically, near infrared rays irradiated from the light emitting element are incident on blood, are affected by absorption and confusion, and are received by the light receiving element. The light absorption / scattering rate is analyzed from the intensity of the received light, and the hematocrit value is calculated.

  Since the first detection means 5a configured as described above is disposed in the arterial blood circuit 1a, it detects the hematocrit value of blood collected from the patient via the arterial puncture needle a during dialysis treatment. Since the second detection means 5b is disposed in the venous blood circuit 1b, the second detection means 5b detects the hematocrit value of the blood purified by the dialyzer 2 and returned to the patient. That is, the specific peak given by the water removal pump 8 is first detected by the second detection means 5b (see FIG. 4), and then the blood reaches the artery side blood circuit 1a again and is recirculated. The first detection means 5a can detect the characteristic peak remaining in the recirculated blood (see FIG. 5).

  Accordingly, it is possible to confirm whether or not a specific peak has been given by the water removal pump 8 by the second detection means 5b, and it is possible to detect the presence or absence of recirculated blood by the first detection means 5a. That is, since it is possible to confirm whether or not a specific peak has been given by the water removal pump 8, it is possible to detect blood recirculation more reliably and accurately than in the case where the detection means is provided only in the arterial blood circuit. It can be done.

  Further, the first detection means 5a and the second detection means 5b are electrically connected to the calculation means 11 provided in the dialyzer body 6 as shown in FIG. The calculation means 11 is constituted by, for example, a microcomputer, and compares the hematocrit values (specific peaks) detected by the first detection means 5a and the second detection means 5b and flows through the arterial blood circuit 1a. The ratio of the recirculated blood in the blood can be calculated. In other words, the calculation means 11 determines that the blood returned from the venous blood circuit 1b to the patient based on the specific peaks (marks) detected by the first detection means 5a and the second detection means 5b is again the arterial blood circuit 1a. It is possible to calculate a recirculation rate that is a ratio of the recirculating blood volume that is guided and flows to the extracorporeal circulating blood volume.

  Specifically, when there is blood recirculation, the time from when a specific peak (mark) is given by the water removal pump 8 until the blood reaches the second detection means 5b (time t5 in FIG. 4). And the time (t7 in FIG. 5) from the recirculation to the first detection means 5a is predicted, and the second detection means 5b is passed when the time t5 has elapsed after the application of the specific peak by the water removal pump 8. The computing means 11 compares the hematocrit value detected by the above and the hematocrit value detected by the first detecting means 5a when the time t7 has elapsed.

  Thus, by predicting the time t5 until the blood reaches the second detection means 5b and the time t7 until the blood reaches the first detection means 5a after recirculation, the cardiopulmonary recirculation (the purified blood becomes the heart Or a phenomenon of being pulled out of the body without passing through other tissues or organs) and recirculation to be measured. Instead of this method, the calculation means 11 recognizes that the hematocrit value detected by the first detection means 5a and the second detection means 5b exceeds a predetermined value, and the hematocrit values exceeding the value are May be compared.

  Then, based on the time-hematocrit value graphs as shown in FIGS. 4 and 5, the change in the hematocrit value of the first detection means 5a and the second detection means 5b is obtained, and the time portion to be compared as described above ( The area of the change part is calculated by a mathematical method such as an integration method. For example, the area of the changed portion (the portion from t5 to t6 in FIG. 4) by the second detecting means 5b is Sv, and the area of the changed portion (the portion from t7 to t8 in FIG. 5) is Sa. In other words, the ratio of recirculated blood (recirculation rate) Rrec is obtained by the following arithmetic expression.

  Rrec (%) = Sa / Sv × 100 (Equation 1)

  Here, the time of the change part by the first detection means 5a (time interval from t7 to t8) is diffused in the process in which the blood to which a specific peak is given flows from the second detection means 5b to the first detection means 5a. In view of this, it is set to be larger than the time of the changed portion (time interval from t5 to t6) by the second detection means 5b. The obtained ratio of recirculated blood is displayed on a display means (not shown) disposed in the dialyzer body 6 so that a medical worker such as a doctor can visually recognize it. When there is no blood recirculation, the above Sa is 0, so the numerical value displayed as the recirculated blood ratio is 0 (%). Thereby, in addition to the presence or absence of blood recirculation, the ratio can be recognized by the medical staff, and subsequent treatments (re-puncture the puncture needle or re-shunt formation to suppress blood recirculation) Etc.).

  By the way, the flow rate of blood flowing through the patient's access site (hereinafter referred to as shunt flow rate (Qf)) is smaller than the prescribed flow rate of the extracorporeal circulating blood volume, and the blood recirculation actually occurs. When the specific peak is smaller than the detection sensitivity of the first detection means 5a and 5b because the rate is small, the measured recirculation rate becomes an inaccurate value (for example, 0). Therefore, in the present embodiment, the prediction unit 12 is configured to be able to predict the recirculation rate in the above state.

Specifically, as shown in FIG. 6, the prediction unit 12 is, for example, a microcomputer or the like electrically connected to the first detection units 5 a and 5 b and the blood pump control unit 13 that controls the driving of the blood pump 3. When the blood pump 3 is controlled by the blood pump control means 13 and the extracorporeal blood volume is temporarily increased from a specified flow rate (hereinafter referred to as a specified flow rate (Qb ₀ )). The recirculation rate (hereinafter referred to as recirculation rate (α)) is calculated, and the recirculation rate when the extracorporeal blood volume is set to the prescribed flow rate (Qb ₀ ) based on the recirculation rate (α). (Hereinafter referred to as the recirculation rate (α ₀ )).

That is, when the shunt flow rate (Qf) is smaller than the prescribed flow rate (Qb ₀ ) of the extracorporeal blood volume due to constriction of the access site (shunt), blood recirculation is performed to satisfy the insufficient extracorporeal blood volume. Therefore, when the blood recirculation flow rate is Qr and the extracorporeal blood volume is Qb, the following arithmetic expression is established.
Qb = Qf + Qr (Equation 2)

On the other hand, since the recirculation rate (α) is the ratio of the recirculation blood volume (Qr) to the extracorporeal circulation blood volume (Qb), the relational expression α = Qr / Qb is established, and this relational expression is expressed by the above calculation formula. Substituting into 1, the following arithmetic expression holds.
Qb = Qf + α · Qb
Qf = (1-α) Qb (Equation 3)

However, the extracorporeal blood volume (Qb) temporarily increased from the specified flow rate (Qb ₀ ) is set to a flow rate at which a specific peak (marker) can be detected by the detection means 5a and 5b. Based on the detection signals of the means 5a and 5b, the recirculation rate (α) can be calculated using the above calculation formula 1. Further, since the extracorporeal blood volume (Qb) is grasped by the driving amount of the blood pump 3 (that is, control by the blood pump control means 13), the extracorporeal blood volume (Qb) and the calculation formula 1 are obtained. By substituting the obtained recirculation rate (α) into the calculation formula 3, the shunt flow rate (Qf) at the extracorporeal blood volume (Qb) can be obtained.

When the shunt flow rate (Qf) is obtained as described above, the recirculation rate (α) when the extracorporeal circulating blood volume is the prescribed flow rate (Qb ₀ ) can be obtained. That is, since the shunt flow rate (Qf) is always constant regardless of the change in the extracorporeal blood volume, if the known Qf and Qb ₀ are substituted into the equation 3, α which is an unknown can be obtained. is there. Thereby, the recirculation rate (α) when the extracorporeal blood volume is set to the prescribed flow rate (Qb ₀ ) can be predicted by calculation.

According to the predicting means 12, the recirculation rate (α) when the extracorporeal blood volume is temporarily increased from the specified flow rate (Qb ₀ ) is calculated, and the extracorporeal circulation rate (α) is calculated based on the recirculation rate (α). Since the recirculation rate (α ₀ ) when the circulating blood volume is the specified flow rate (Qb ₀ ) is predicted, the flow rate of the blood flowing through the patient's access site is smaller than the extracorporeal circulating blood volume, and actually the blood recirculation Even if circulation occurs, the recirculation rate (α ₀ ) can be predicted even when the recirculation rate is lower than the detection sensitivity of the detection means.

In addition, according to the above embodiment, the predicting means 12 can predict the recirculation rate (α ₀ ) simply by controlling the blood pump 3 to temporarily increase the extracorporeal circulating blood volume. Although the blood recirculation actually occurs, the recirculation rate (α ₀ ) can be predicted even when the recirculation rate is smaller than the detection sensitivity of the detection means. Furthermore, by using two of the first detection means 5a and the second detection means 5b, both detection values can be compared without water removal, and these calibrations can be automatically performed. In addition, since the 1st detection means 5a and the 2nd detection means 5b are each arrange | positioned at the entrance side and exit side of the dialyzer 2, the water removal performance of the dialyzer 2 can be monitored.

  In the dialysis apparatus, one in which a pressure measuring means is disposed upstream of the blood pump 3 of the arterial blood circuit 1a is widely used. Such pressure measuring means can measure the negative pressure upstream of the blood pump 3 of the arterial blood circuit 1a, and the extracorporeal circulating blood volume estimated from the driving amount of the blood pump 3 based on the measured value is the actual blood pressure. Since it can be determined whether or not it is equal to the extracorporeal blood volume, it can be monitored whether or not accurate blood removal is achieved. However, the recirculation rate can be predicted with higher accuracy if the calculation by the prediction unit is performed on the condition that accurate blood removal is achieved by the pressure measurement unit.

  As mentioned above, although this embodiment was described, this invention is not limited to this, For example, a specific peak is provided by rapid and short-time water removal like the water removal pump 8, and this is used as a mark. Instead of the above, other forms of mark providing means may be used. That is, it suffices to provide a predetermined mark for blood extracorporeally circulated in the blood circuit 1 to detect recirculated blood. In addition to the concentration of blood as in this embodiment, physiological saline The blood concentration may be diluted rapidly and in a short time by injection or the like, or the temperature change may be applied rapidly and in a short time.

  In the present embodiment, the two detection means 5a and 5b detect the mark given by the mark giving means. Instead of this, the single detection means provided in the blood circuit 1 replaces the mark. May be detected. In addition, as long as it can detect a mark (a peculiar peak), you may comprise a detection means other than a hematocrit sensor (for example, a sensor which detects a hemoglobin density | concentration, a sensor which detects the density | concentration of protein etc.).

  Furthermore, when the ratio of recirculated blood (recirculation rate) exceeds a predetermined value, an alarm or the like may be sounded to alert the medical staff. In the present embodiment, the dialysis device body 6 is composed of a dialysis monitoring device that does not incorporate a dialysate supply mechanism, but may be applied to a personal dialysis device that incorporates a dialysate supply mechanism. .

  A blood purification device that calculates a recirculation rate when the extracorporeal blood volume is temporarily increased from a specified flow rate and predicts the recirculation rate when the extracorporeal blood volume is a specified flow rate based on the recirculation rate If the recirculation rate calculation method is used, it can be applied to other treatments (blood filtration therapy, hemofiltration dialysis therapy, etc.) that perform blood purification while circulating extracorporeally, or those that have other functions added. can do.

1 is an overall schematic view showing a blood purification apparatus according to an embodiment of the present invention. Schematic showing the dialysis machine body in the blood purification device It is a graph which shows control of the water removal pump in the blood purification apparatus, Comprising: The graph which shows performing water removal rapidly and in a short time The graph which shows the change of the hematocrit value detected by the 2nd detection means in the blood purification apparatus The graph which shows the change (when there exists recirculation) of the hematocrit value detected by the 1st detection means in the blood purification apparatus The block diagram which shows the connection relation of the 1st detection means in the blood purification apparatus, 2nd detection means, a calculation means, a blood pump control means, and a prediction means.

Explanation of symbols

DESCRIPTION OF SYMBOLS 1 ... Blood circuit 1a ... Arterial side blood circuit 1b ... Vein side blood circuit 2 ... Dializer (blood purification means)
3 ... blood pump 4 ... drip chamber 5a ... first detection means (detection means)
5b ... 2nd detection means (detection means)
6 ... Main body of dialyzer 7 ... Dialysate supply device 8 ... Water removal pump (marking means)
DESCRIPTION OF SYMBOLS 9 ... Heater 10 ... Deaeration means 11 ... Calculation means 12 ... Prediction means 13 ... Blood pump control means

Claims (6)

A blood circuit comprising an arterial blood circuit and a venous blood circuit for extracorporeal circulation of blood collected from a patient access site;
A blood pump disposed in the arterial blood circuit;
Blood purification means connected between the arterial blood circuit and the venous blood circuit and purifying blood flowing through the blood circuit;
Mark applying means for applying a predetermined mark to blood circulating extracorporeally in the blood circuit;
Detecting means for detecting the mark given by the mark giving means;
Based on the mark detected by the detection means, the recirculation is the ratio of the recirculated blood volume that the blood returned to the patient from the venous blood circuit is led to the arterial blood circuit again and flows. A computing means capable of computing the rate;
In the blood purification apparatus comprising
The recirculation rate when the extracorporeal blood volume is temporarily increased from the specified flow rate by controlling the blood pump, and the recirculation when the extracorporeal blood volume is the specified flow rate based on the recirculation rate A blood purification apparatus comprising a predicting means capable of predicting a rate. The predicting means calculates a recirculation rate (α) in the extracorporeal blood volume (Qb) temporarily increased from the prescribed flow rate (Qb ₀ ), and flows from the recirculation rate (α) to the patient's access site. Obtaining a shunt flow rate (Qf), which is a blood flow rate, and calculating and predicting a recirculation rate (α ₀ ) when the extracorporeal blood volume is a specified flow rate (Qb ₀ ) based on the shunt flow rate (Qf) The blood purification apparatus according to claim 1. The predicting means is configured to calculate the shunt flow rate (Qf) = (1−recirculation rate (α)) × (extracorporeal blood volume (Qb)) in the extracorporeal blood volume (Qb) temporarily increased by the arithmetic expression with obtaining the shunt flow (Qf), according to claim 2, wherein the predicting extracorporeally circulating blood volume by the arithmetic expression is calculated to define the flow rate (Qb ₀₎ recirculation rate when the (alpha ₀₎ Blood purification device. A blood purification means connected between the arterial blood circuit and the venous blood circuit while extracorporeally circulating blood collected from the patient's access site through a blood circuit comprising an arterial blood circuit and a venous blood circuit The blood is purified, and a predetermined mark is given to the blood circulating extracorporeally in the blood circuit, and the blood returned to the patient from the venous blood circuit is again detected by detecting the mark. In the recirculation rate calculation method of the blood purification apparatus for calculating the recirculation rate that is a ratio of the recirculation blood volume that is guided by the arterial blood circuit and flows to the extracorporeal blood volume,
Calculates the recirculation rate when the extracorporeal blood volume is temporarily increased from the specified flow rate, and predicts the recirculation rate when the extracorporeal blood volume is the specified flow rate based on the recirculation rate The recirculation rate calculation method of the blood purification apparatus. The recirculation rate (α) in the extracorporeal blood volume (Qb) temporarily increased from the specified flow rate (Qb ₀ ) is calculated, and the shunt that is the blood flow rate flowing through the patient's access site from the recirculation rate (α) together determine the flow rate (Qf), wherein, wherein the predicting the extracorporeally circulating blood flow based on the shunt flow (Qf) is calculated recirculation rate (alpha ₀₎ when the prescribed flow rate (Qb ₀₎ Item 5. The method for calculating the recirculation rate of the blood purification device according to Item 4. Shunt flow rate (Qf) in the extracorporeal blood volume (Qb) temporarily increased by the arithmetic expression of shunt flow rate (Qf) = (1−recirculation rate (α)) × (extracorporeal blood volume (Qb)) together determine the re extracorporeal circulation blood volume by the arithmetic expression is specified flow rate (Qb ₀₎ recirculation rate (alpha ₀₎ blood purification apparatus according to claim 5, wherein the predicting by calculating the time of Circulation rate calculation method.

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