CN110152117B - Venous transfusion detection device and detection method thereof - Google Patents

Venous transfusion detection device and detection method thereof Download PDF

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Publication number
CN110152117B
CN110152117B CN201910344550.8A CN201910344550A CN110152117B CN 110152117 B CN110152117 B CN 110152117B CN 201910344550 A CN201910344550 A CN 201910344550A CN 110152117 B CN110152117 B CN 110152117B
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resistor
voltage
power supply
arc
adjusting
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CN110152117A (en
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许明
孙森
陈国金
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Hangzhou Dianzi University
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Hangzhou Dianzi University
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/168—Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body
    • A61M5/16804—Flow controllers
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/168—Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body
    • A61M5/16886—Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body for measuring fluid flow rate, i.e. flowmeters
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/168—Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body
    • A61M5/16886—Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body for measuring fluid flow rate, i.e. flowmeters
    • A61M5/1689—Drip counters
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14—Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/168—Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body
    • A61M5/172—Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body electrical or electronic
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00—General characteristics of the apparatus
    • A61M2205/18—General characteristics of the apparatus with alarm

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  • Health & Medical Sciences (AREA)
  • Vascular Medicine (AREA)
  • Engineering & Computer Science (AREA)
  • Anesthesiology (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Hematology (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Physics & Mathematics (AREA)
  • Fluid Mechanics (AREA)
  • Infusion, Injection, And Reservoir Apparatuses (AREA)

Abstract

The invention discloses a venous transfusion detection device and a detection method thereof. In the process of intravenous drip, people must be detected, and the infusion instrument cannot automatically judge whether the infusion is finished. The invention relates to a venous transfusion detection device which comprises a disposable transfusion device, a vibration detection assembly, a battery and a signal conversion circuit. The side of the drip cup is provided with a piezoelectric piece insertion groove. The vibration detection assembly comprises a piezoelectric sheet, a first arc-shaped plate and a second arc-shaped plate. One end of the piezoelectric sheet is fixed with the inner side surface of the first arc-shaped plate. The first arc-shaped plate is hinged with one side edge of the second arc-shaped plate. The signal conversion circuit comprises an operational amplifier chip and an exclusive-OR gate. The operational amplifier chip comprises a first operational amplifier and a second operational amplifier. The invention detects the vibration signal generated when the liquid drops drop in the drip cup through the piezoelectric sheet, and judges whether the infusion is finished or not, thereby realizing the automatic real-time monitoring in the venous infusion and providing the most comfortable and safe infusion experience for patients.

Description

Venous transfusion detection device and detection method thereof
Technical Field
The invention belongs to the technical field of medical auxiliary equipment, and particularly relates to a venous transfusion detection device and a detection method thereof.
Background
Intravenous infusion therapy is an important treatment means in medical care, and is widely applied in various medical institutions nowadays due to its rapid drug effect, small irritation and rapid drug administration. By observing and analyzing the current iv procedure, two problems are summarized with the existing iv instruments: firstly, in the process of intravenous drip, people must detect, and the infusion instrument cannot automatically judge whether the infusion is finished and timely inform medical personnel to treat, so that dangerous conditions such as blood return and the like occur to patients. Secondly, the flow rate regulator can not automatically regulate the flow rate, and after the medicine liquid drops, the flow rate can not be timely regulated to be low, so that blood return is caused.
Disclosure of Invention
The invention aims to provide a venous transfusion detection device and a detection method thereof.
The invention relates to a venous transfusion detection device which comprises a disposable transfusion device, a vibration detection assembly, a battery and a signal conversion circuit. The disposable infusion apparatus comprises a drip cup. And a piezoelectric piece insertion groove is formed in the side part of the drip cup. The piezoelectric piece insertion groove is communicated with the external environment and is not communicated with the inner cavity of the drip cup. The vibration detection assembly comprises a piezoelectric sheet, a first arc-shaped plate and a second arc-shaped plate. One end of the piezoelectric sheet is fixed with the inner side surface of the first arc-shaped plate. The first arc-shaped plate is hinged with one side edge of the second arc-shaped plate.
The signal conversion circuit comprises a charge amplification chip, a voltage comparison chip and an exclusive-OR gate. The non-inverting input end of the charge amplification chip is connected with the first wiring end of the piezoelectric patch and is grounded; the inverting input terminal is connected with the second terminal of the piezoelectric sheet, one end of the capacitor C2 and one end of the resistor R7. The other end of the capacitor C2 and the other end of the resistor R7 are connected with the output end of the charge amplification chip. The positive power supply voltage end of the charge amplification chip is connected with a positive power supply; the negative supply voltage is connected with the negative power supply.
The voltage comparison chip comprises a first operational amplifier and a second operational amplifier. The positive power supply voltage end of the voltage comparison chip is connected with the positive power supply, and the negative power supply voltage end of the voltage comparison chip is connected with the negative power supply; the non-inverting input end of the first operational amplifier in the voltage comparison chip is grounded, the inverting input end of the first operational amplifier is connected with the output end of the charge amplifier U1, and the output end of the first operational amplifier is connected with the anode of the diode D2 and one end of the resistor R8; the cathode of the diode D2 is connected with the first input end of the exclusive-OR gate; the other end of the resistor R8 is connected with a positive power supply; the non-inverting input end of a second operational amplifier in the voltage comparison chip is connected with the output end of the charge amplification chip, the inverting input end of the second operational amplifier is grounded, and the output end of the second operational amplifier is connected with the anode of the diode D3 and one end of the resistor R9; the cathode of the diode D3 is connected with the second input end of the exclusive-OR gate; the other end of the resistor R9 is connected with the positive power supply.
Furthermore, the venous transfusion detection device also comprises an alarm circuit. The alarm circuit comprises a resistor R1, a resistor R2, a resistor R3, a resistor R6, a capacitor C1, a voltage regulator tube D1, a buzzer, a first field effect tube M1 and a second field effect tube M2. One end of the resistor R1 is connected with the output end of the exclusive-OR gate, and the other end is connected with the gate of the first field effect transistor M1. The drain of the first field effect transistor M1 is connected with one end of a resistor R6, and the other end of the resistor R6 is connected with one end of a resistor R2, one end of a capacitor C1 and the cathode of a voltage regulator tube D1. The sources of the first and second fets M1 and M2 and the other end of the capacitor C1 are grounded. The other end of the resistor R2 is connected with the button switch and one end of the resistor R3. The other end of the resistor R3 is connected with the positive terminal of the buzzer. The negative wire of the buzzer is connected with the drain electrode of the second field effect transistor M2. The resistor R2 and the capacitor C1 form an RC charging circuit; the charging constant of the RC charging circuit is greater than or equal to 4 s; the stable voltage of the voltage regulator tube D1 is 0.5-0.8 times of the output voltage of the battery.
Furthermore, the venous transfusion detection device also comprises a controller and a flow rate adjusting mechanism. The flow velocity adjusting mechanism comprises an adjusting base, an adjusting slide block and an adjusting driving assembly. An infusion tube channel is arranged in the adjusting base. The infusion hose on the disposable infusion set passes through the infusion tube channel on the adjusting base. The adjusting slide block and the adjusting base form a sliding pair. The adjusting slide block is provided with a flow adjusting pressure head. The flow regulating pressure head extends into the infusion tube channel and props against the infusion hose. The bottom surface of the transfusion tube channel is not parallel to the axis of the adjusting screw rod; the control interface of the adjusting motor is connected with the control output interface of the controller through a motor driver. And the signal input end of the controller is connected with the output end of the exclusive-OR gate.
Further, the controller and the upper computer are in wireless communication through the wireless module.
Further, the adjusting drive assembly comprises an adjusting lead screw and an adjusting motor. The adjusting screw rod is supported on the adjusting base. The adjusting slide block and the adjusting screw rod form a screw pair; the adjusting motor is fixed on the adjusting base, and the output shaft is fixed with one end of the adjusting screw rod.
Furthermore, the venous transfusion detection device also comprises a vibration power generation circuit. The vibration power generation circuit comprises a rectifier bridge and a voltage comparator. And the first input end and the second input end of the rectifier bridge are respectively connected with the first terminal and the second terminal of the piezoelectric sheet. The positive output end of the rectifier bridge is connected with one end of a capacitor CE1, one end of a resistor RE1, a positive power supply voltage end of a voltage comparator, one end of a resistor RE3, one end of a resistor RE4 and the source electrode of a fourth field-effect tube M4, and the negative output end of the rectifier bridge is connected with the other end of the capacitor CE1, one end of a resistor RE2, the negative power supply voltage end of the voltage comparator, the source electrode of a third field-effect tube M3, one end of the capacitor CE2 and the negative electrode of the battery. The inverting input end of the voltage comparator is connected with the other ends of the resistor RE1 and the resistor RE2, the non-inverting input end of the voltage comparator is connected with the anode of the battery, and the output end of the voltage comparator is connected with the grid of the third field effect transistor M3 and the other end of the resistor RE 3. The drain of the third fet M3 is connected to the gate of the fourth fet M4 and the other end of the resistor RE 4. The grid of the fourth field effect transistor M4 is connected to the other end of the second capacitor CE2 and the positive electrode of the battery.
Further, the type of the exclusive-or gate is 74LS 86. The model of the voltage comparator is LM 393. The model of the charge amplification chip is OP 37; the model of the voltage comparator U4 is LM 393; the model of the rectifier bridge is MB 6S.
Furthermore, permanent magnets and iron blocks are respectively embedded at the edges of the other sides of the first arc-shaped plate and the second arc-shaped plate; the first arc-shaped plate and the second arc-shaped plate encircle the drip cup. The piezoelectric sheet extends into the piezoelectric sheet insertion groove, and the top surface of the piezoelectric sheet is in contact with the upper side surface of the piezoelectric sheet insertion groove. The width of the piezoelectric sheet is smaller than that of the piezoelectric sheet insertion groove; the length of the piezoelectric sheet is less than the depth of the piezoelectric sheet insertion groove and greater than the radius of the drip cup.
Furthermore, the positive power supply is obtained by a positive voltage output by the positive electrode of the battery through a voltage stabilizing chip; the negative power supply is obtained by a positive power supply through a polarity reversal power supply converter. The polarity reversing power converter is model ICL 7660S.
The detection method of the venous transfusion detection device is as follows:
step one, after the medical staff pricks the needle for the patient by using the disposable infusion apparatus, the piezoelectric sheet in the vibration detection assembly is inserted into the piezoelectric sheet insertion groove on the drip cup, and the first arc-shaped plate and the second arc-shaped plate are closed.
And step two, continuously dripping the medicine drops in the drip cup, vibrating the piezoelectric sheet when the medicine drops drip, and outputting a high level by the XOR gate. The controller continuously receives the signal output by the exclusive-OR gate and records the duration time of low level; and when the controller detects that the time for the exclusive-or gate to continuously output the low level exceeds 5s, the step three is entered.
And step three, the controller controls the adjusting motor to rotate, so that the infusion hose is pressed tightly.
The invention has the beneficial effects that:
1. the invention detects the vibration signal generated when the liquid drops drop in the drip cup through the piezoelectric sheet, and judges whether the infusion is finished or not, thereby realizing the automatic real-time monitoring in the venous infusion and providing the most comfortable and safe infusion experience for patients.
2. The invention can collect the energy in the dropping process of the liquid medicine to charge the battery, thereby greatly enhancing the continuous capability of the invention. Particularly, in the technical scheme of the first embodiment, because a controller is not used, processing and identification and automatic alarm of the vibration signal can be realized through low-energy-consumption electronic elements such as an amplifier, a logic gate, a capacitor and a field effect transistor, the power consumption is extremely low, and the infinite endurance can be approached by matching with piezoelectric sheet vibration power generation.
3. The flow rate adjusting mechanism can enable a nurse station to realize remote infusion speed control, automatically stop infusion after liquid medicine is exhausted, and avoid the occurrence of blood return under the condition that a nurse does not timely replace the liquid medicine.
4. The disposable infusion set is separable from other components; therefore, the disposable infusion set can be discarded independently, and other components can be reused.
Drawings
FIG. 1 is a block diagram of a system according to embodiment 1 of the present invention;
FIG. 2 is a schematic view of a drip chamber in embodiments 1 and 2 of the present invention;
fig. 3 is a schematic view of a vibration detecting assembly in embodiments 1 and 2 of the present invention;
fig. 4 is a schematic circuit diagram of a vibration power generation circuit in embodiments 1 and 2 of the present invention;
fig. 5 is a circuit schematic diagram of a signal conversion circuit in embodiments 1 and 2 of the present invention;
fig. 6 is a schematic circuit diagram of an alarm circuit in embodiment 1 of the present invention;
FIG. 7 is a block diagram of a system according to embodiment 2 of the present invention;
FIG. 8 is a schematic view of a flow rate adjustment mechanism in embodiment 2 of the invention;
Detailed Description
The invention is further described below with reference to the accompanying drawings.
Example 1
As shown in fig. 1, 2 and 3, the intravenous infusion detection device comprises a disposable infusion set, a vibration detection component, a vibration power generation circuit 6, a battery BT1, a signal conversion circuit 4 and an alarm circuit 5. The disposable infusion apparatus comprises an intravenous needle, an injection needle, a needle head protective cap, an infusion hose, a liquid medicine filter, a flow rate regulator, a drip cup, a bottle stopper puncture outfit and an air filter. The side of the drip cup is provided with a piezoelectric piece insertion groove 201. The piezoelectric piece insertion groove 201 is communicated with the external environment and is not communicated with the inner cavity of the drip cup.
As shown in fig. 3, the vibration detecting assembly includes a piezoelectric sheet 101, a first arc plate 102, and a second arc plate 103. One end of the piezoelectric sheet 101 is fixed to the inner side surface of the first arc-shaped plate 102. The width of the piezoelectric sheet 101 is smaller than that of the piezoelectric sheet insertion groove 201; the length of the piezoelectric sheet 101 is smaller than the depth of the piezoelectric sheet insertion groove 201 and larger than the radius of the drip chamber. The first arc plate 102 is hinged with one side edge of the second arc plate 103. Permanent magnets and iron blocks are respectively embedded at the edges of the other sides of the first arc-shaped plate 102 and the second arc-shaped plate 103; the first arc-shaped plate 102 and the second arc-shaped plate 103 encircle the drip chamber. The piezoelectric sheet 101 is inserted into the piezoelectric sheet insertion groove 201, and the top surface of the piezoelectric sheet 101 is in contact with the upper side surface of the piezoelectric sheet insertion groove 201. After the permanent magnet is attracted with the iron block, the shapes of the inner side surfaces of the first arc-shaped plate 102 and the second arc-shaped plate 103 correspond to the shape of the drip cup. When the liquid medicine drops are dripped from the liquid inlet 202 at the top of the drip cup, the liquid medicine drops are dripped on the piezoelectric plate insertion groove 201, and in the process, the piezoelectric plate 101 vibrates and sends out a pulse signal.
As shown in fig. 4, the vibration power generation circuit 6 includes a rectifier bridge DE1 and a voltage comparator U4. The rectifier bridge DE1 is model MB 6S. Voltage comparator U4 is model LM 393. A first input terminal (pin 1) and a second input terminal (pin 3) of the rectifier bridge DE1 are connected to a first terminal and a second terminal of the piezoelectric patch 101, respectively. A positive output end (pin 2) of the rectifier bridge DE1 is connected to the capacitor CE1, one end of the resistor RE1, a positive power supply voltage end of the voltage comparator U4, one end of the resistor RE3, one end of the resistor RE4, and a source of the fourth field-effect transistor M4, and negative output ends (pin 4) are connected to the other end of the capacitor CE1, one end of the resistor RE2, a negative power supply voltage end of the voltage comparator U4, a source of the third field-effect transistor M3, one end of the capacitor CE2, and a negative electrode (i.e., a ground line) of the battery BAT 1. The inverting input end of the voltage comparator U4 is connected with the other ends of the resistor RE1 and the resistor RE2, the non-inverting input end is connected with the positive pole VCC of the battery BAT1, and the output end is connected with the grid of the third field effect transistor M3 and the other end of the resistor RE 3. The drain of the third fet M3 is connected to the gate of the fourth fet M4 and the other end of the resistor RE 4. The grid of the fourth field effect transistor M4 is connected to the other end of the second capacitor CE2 and the positive electrode VCC of the battery BT 1. The remaining pins of the voltage comparator U4 are floating.
As shown in fig. 5, the signal conversion circuit 4 includes a charge amplification chip U1, a voltage comparison chip U2, and an exclusive or gate U3. The model of the charge amplification chip U1 is OP 37. The signal of the voltage comparison chip U2 is LM 393. The exclusive-or gate U3 is 74LS 86. The non-inverting input terminal (pin 3) of the charge amplification chip U1 is connected to the first terminal P1 of the piezoelectric plate 101 and the ground GND, and the inverting input terminal (pin 2) is connected to the second terminal P2 of the piezoelectric plate 101, the capacitor C2 and one end of the resistor R7. The other ends of the capacitor C2 and the resistor R7 are connected with an output end (6 pins) of the charge amplification chip U1. The positive supply voltage end (pin 7) of the charge amplification chip U1 is connected with a positive power supply + V, and the negative supply voltage end (pin 4) is connected with a negative power supply-V. The positive power supply + V (5V voltage) is obtained by a positive voltage output by the positive electrode of the battery BT1 through a voltage stabilizing chip; the negative power supply-V is obtained by a positive power supply + V through a polarity reversal power supply converter. The polarity reversing power converter is model ICL 7660S.
The voltage comparison chip U2 includes a first operational amplifier and a second operational amplifier. A positive power supply voltage end (pin 8) of the voltage comparison chip U2 is connected with a positive power supply + V, and a negative power supply voltage end (pin 4) is connected with a negative power supply-V; the non-inverting input end (pin 3) of a first operational amplifier in the voltage comparison chip U2 is grounded GND, the inverting input end (pin 2) is connected with the output end (pin 6) of the charge amplifier U1, and the output end (pin 1) is connected with the anode of the diode D2 and one end of the resistor R8; the cathode of the diode D2 is connected with the first input end of the XOR gate U3; the other end of the resistor R8 is connected with a positive power supply + V; the non-inverting input end (pin 5) of a second operational amplifier in the voltage comparison chip U2 is connected with the output end (pin 6) of the charge amplification chip U1, the inverting input end (pin 6) is grounded GND, and the output end (pin 7) is connected with the anode of the diode D3 and one end of the resistor R9; the cathode of the diode D3 is connected with the second input end of the XOR gate U3; the other end of the resistor R9 is connected with a positive power supply + V.
As shown in fig. 6, the alarm circuit 5 includes a resistor R1, a resistor R2, a resistor R3, a resistor R6, a capacitor C1, a voltage regulator tube D1, a buzzer B1, a first field effect tube M1, and a second field effect tube M2. One end of the resistor R1 is connected to the output end P3 of the XOR gate U3, and the other end is connected to the gate of the first FET M1. The drain of the first field effect transistor M1 is connected with one end of a resistor R6, and the other end of the resistor R6 is connected with one end of a resistor R2, one end of a capacitor C1 and the cathode of a voltage regulator tube D1. The sources of the first field effect transistor M1 and the second field effect transistor M2 and the other end of the capacitor C1 are all grounded. The other end of the resistor R2 is connected with one end of the button switch S1 and the resistor R3. The other end of the resistor R3 is connected with the positive terminal of the buzzer B1. The negative wire of the buzzer B1 is connected with the drain of the second field effect transistor M2. The resistor R2 and the capacitor C1 form an RC filter circuit; the charging constant of the RC filter circuit (i.e. the product of the resistance value of the resistor R2 and the capacitance value of the capacitor C1, which represents the time required for the voltage across the capacitor C1 to reach 0.63 times the maximum value) is 5 s. The stable voltage of the voltage regulator tube D1 is 0.63 times of the output voltage of the battery; therefore, if the charging time and time constant of the capacitor C1 are long; the zener D1 will not break down.
The intravenous infusion detection device has the following working principle:
after a medical worker pricks a needle for a user by using the disposable infusion apparatus, the piezoelectric sheet 101 in the vibration detection assembly is inserted into the piezoelectric sheet insertion groove on the drip cup, and the first arc-shaped plate 102 and the second arc-shaped plate 103 are closed; the push switch S1 is pressed so that the resistor R2 and the resistor R3 are connected to the positive electrode of the battery.
When the push button switch S1 is pressed, the connection of the first operational amplifier and the second operational amplifier are opposite; therefore, when the piezoelectric plate vibrates, the output ends of the first operational amplifier and the second operational amplifier are necessarily high level and low level no matter the vibration direction, and the high level can be output after the output ends pass through the XOR gate; therefore, as long as the piezoelectric sheet vibrates, the exclusive-or gate outputs high level; the exclusive-or gate outputs a low level only when the piezoelectric sheet does not vibrate. Therefore, the XOR gate can output a high level every time the medicine drops are dripped in the drip cup. When the xor gate outputs a high level, the first fet M1 is turned on, so that the capacitor C1 starts to charge.
Therefore, as long as the infusion bottle still contains the liquid medicine, the liquid medicine drops are continuously dripped into the drip cup at intervals; the exclusive-OR gate can continuously output square wave signals, and the dropping time interval of two drops of medicine in the transfusion can not exceed 5 seconds; therefore, the output time of the exclusive-OR gate does not exceed five seconds in the infusion process.
After the liquid medicine is not dripped into the drip cup any more, the two input ends of the exclusive-OR gate simultaneously input low level; the output end of the exclusive-or gate continuously outputs high level, so that the voltage at the two ends of the capacitor C1 is increased to the battery voltage; the voltage regulator tube D1 breaks down, and the second field effect tube M2 is conducted; the buzzer makes a sound.
Example 2
As shown in fig. 2, 3 and 7, the intravenous infusion detection device comprises a disposable infusion set, a flow rate adjusting mechanism, a vibration detection component, a vibration power generation circuit 6, a signal conversion circuit 4 and a controller 7. The disposable infusion set comprises an intravenous needle, an injection needle, a needle head protective cap, an infusion hose 305, a liquid medicine filter, a drip cup, a bottle stopper puncture outfit and an air filter. The outer side surface of the drip cup is provided with a piezoelectric piece insertion groove 201. The piezoelectric piece insertion groove 201 is communicated with the external environment and is not communicated with the inner cavity of the drip cup.
As shown in fig. 3, the vibration detecting assembly includes a piezoelectric sheet 101, a first arc plate 102, and a second arc plate 103. One end of the piezoelectric sheet 101 is fixed to the inner side surface of the first arc-shaped plate 102. The width of the piezoelectric sheet 101 is smaller than that of the piezoelectric sheet insertion groove 201; the length of the piezoelectric sheet 101 is smaller than the depth of the piezoelectric sheet insertion groove 201 and larger than the radius of the drip chamber. The first arc plate 102 is hinged with one side edge of the second arc plate 103, and the other side edge. Permanent magnets and iron blocks are respectively embedded at the edges of the other sides of the first arc-shaped plate 102 and the second arc-shaped plate 103; the first arc-shaped plate 102 and the second arc-shaped plate 103 encircle the drip chamber. The piezoelectric sheet 101 is inserted into the piezoelectric sheet insertion groove 201, and the top surface of the piezoelectric sheet 101 is in contact with the upper side surface of the piezoelectric sheet insertion groove 201. After the permanent magnet is attracted with the iron block, the shapes of the inner side surfaces of the first arc-shaped plate 102 and the second arc-shaped plate 103 correspond to the shape of the drip cup. When the liquid medicine drops are dripped from the liquid inlet 202 at the top of the drip cup, the liquid medicine drops are dripped on the piezoelectric plate insertion groove 201, and in the process, the piezoelectric plate 101 vibrates and sends out a pulse signal.
As shown in fig. 8, the flow rate adjustment mechanism includes an adjustment base 301, an adjustment screw 302, an adjustment slider 303, and an adjustment motor 304. An infusion tube channel is arranged in the adjusting base 301. An infusion hose 305 on the disposable infusion set passes through an infusion tube channel on the adjustment base 301. The infusion hose 305 is an interference fit with the infusion tube channel to ensure that there is no relative movement between the adjustment base 301 and the infusion hose 305. The adjusting spindle 302 is supported on the adjusting base 301. The adjusting motor 304 is fixed on the adjusting base 301, and the output shaft is fixed with one end of the adjusting screw 302. The adjusting slide block 303 and the adjusting base 301 form a sliding pair. The adjusting slide block and the adjusting screw rod form a screw pair; the adjusting slide block 303 is provided with a flow adjusting pressure head. The flow regulating ram extends into the infusion tube channel and is urged against the infusion hose 305. The bottom surface of the infusion tube channel is not parallel to the axis of the adjusting screw 302; the distance from the axis of the adjusting screw 302 to the bottom of one end of the infusion tube channel is equal to the distance from the axis of the adjusting screw 302 to the end part of the flow adjusting pressure head; the distance from the axis of the adjusting screw 302 to the bottom of the other end of the infusion tube channel is equal to the sum of the distance from the axis of the adjusting screw 302 to the end of the flow adjusting pressure head and the outer diameter of the infusion hose 305.
When the adjustment screw 302 rotates, the adjustment slider 303 slides in the axial direction of the adjustment screw 302. Because the infusion hose 305 and the adjusting screw 302 form a certain angle, when the adjusting slide block 303 moves along the direction of the adjusting screw 302, the pressing force of the outer end part of the adjusting slide block 303 on the infusion hose 305 changes, so that the cross-sectional area of the flow channel at the contact position of the infusion hose 305 and the adjusting slide block 303 changes, and the flow rate is adjusted.
As shown in fig. 4, the vibration power generation circuit 6 includes a rectifier bridge DE1 and a voltage comparator U4. The rectifier bridge DE1 is model MB 6S. Voltage comparator U4 is model LM 393. A first input terminal (pin 1) and a second input terminal (pin 3) of the rectifier bridge DE1 are connected to a first terminal and a second terminal of the piezoelectric patch 101, respectively. A positive output end (pin 2) of the rectifier bridge DE1 is connected to the capacitor CE1, one end of the resistor RE1, a positive power supply voltage end of the voltage comparator U4, one end of the resistor RE3, one end of the resistor RE4, and a source of the fourth field-effect transistor M4, and negative output ends (pin 4) are connected to the other end of the capacitor CE1, one end of the resistor RE2, a negative power supply voltage end of the voltage comparator U4, a source of the third field-effect transistor M3, one end of the capacitor CE2, and a negative electrode (i.e., a ground line) of the battery BAT 1. The inverting input end of the voltage comparator U4 is connected with the other ends of the resistor RE1 and the resistor RE2, the non-inverting input end is connected with the positive pole VCC of the battery BAT1, and the output end is connected with the grid of the third field effect transistor M3 and the other end of the resistor RE 3. The drain of the third fet M3 is connected to the gate of the fourth fet M4 and the other end of the resistor RE 4. The grid of the fourth field effect transistor M4 is connected to the other end of the second capacitor CE2 and the positive electrode VCC of the battery BT 1. The remaining pins of the voltage comparator U4 are floating.
As shown in fig. 5, the signal conversion circuit 4 includes a charge amplification chip U1, a voltage comparison chip U2, and an exclusive or gate U3. The model of the charge amplification chip U1 is OP 37. The signal of the voltage comparison chip U2 is LM 393. The exclusive-or gate U3 is 74LS 86. The non-inverting input terminal (pin 3) of the charge amplification chip U1 is connected to the first terminal P1 of the piezoelectric plate 101 and the ground GND, and the inverting input terminal (pin 2) is connected to the second terminal P2 of the piezoelectric plate 101, the capacitor C2 and one end of the resistor R7. The other ends of the capacitor C2 and the resistor R7 are connected with an output end (6 pins) of the charge amplification chip U1. The positive supply voltage end (pin 7) of the charge amplification chip U1 is connected with a positive power supply + V, and the negative supply voltage end (pin 4) is connected with a negative power supply-V. The positive power supply + V is obtained by passing positive voltage output by the positive electrode of the battery BT1 through a voltage stabilizing chip; the negative power supply-V is obtained by a positive power supply + V through a polarity reversal power supply converter. The polarity reversing power converter is model ICL 7660S.
The voltage comparison chip U2 includes a first operational amplifier and a second operational amplifier. A positive power supply voltage end (pin 8) of the voltage comparison chip U2 is connected with a positive power supply + V, and a negative power supply voltage end (pin 4) is connected with a negative power supply-V; the non-inverting input end (pin 3) of a first operational amplifier in the voltage comparison chip U2 is grounded GND, the inverting input end (pin 2) is connected with the output end (pin 6) of the charge amplifier U1, and the output end (pin 1) is connected with the anode of the diode D2 and one end of the resistor R8; the cathode of the diode D2 is connected with the first input end of the XOR gate U3; the other end of the resistor R8 is connected with a positive power supply + V; the non-inverting input end (pin 5) of a second operational amplifier in the voltage comparison chip U2 is connected with the output end (pin 6) of the charge amplification chip U1, the inverting input end (pin 6) is grounded GND, and the output end (pin 7) is connected with the anode of the diode D3 and one end of the resistor R9; the cathode of the diode D3 is connected with the second input end of the XOR gate U3; the other end of the resistor R9 is connected with a positive power supply + V.
The control interface of the adjusting motor 304 is connected with the control output interface of the controller 7 through a motor driver. The signal input (I/O port) of the controller 7 is connected to the output P3 of the xor gate U3. The controller 7 and the upper computer 8 of the nurse station perform wireless communication via a wireless module. The upper computer 8 can control the adjustment motor 304 to rotate by sending signals to the controller 7, so that the remote control of the drip flow is realized.
The detection method of the venous transfusion detection device is as follows:
step one, after a medical worker pricks a needle for a patient by using a disposable infusion apparatus, a piezoelectric sheet 101 in a vibration detection assembly is inserted into a piezoelectric sheet insertion groove on a drip cup, and a first arc-shaped plate 102 and a second arc-shaped plate 103 are closed.
Step two, the connection method of the first operational amplifier and the second operational amplifier is opposite; therefore, when the piezoelectric plate vibrates, the output ends of the first operational amplifier and the second operational amplifier are necessarily high level and low level no matter the vibration direction, and the high level can be output after the output ends pass through the XOR gate; therefore, as long as the piezoelectric sheet vibrates, the exclusive-or gate outputs high level; the exclusive-or gate outputs a low level only when the piezoelectric sheet does not vibrate. Therefore, the XOR gate can output a high level every time the medicine drops are dripped in the drip cup.
The controller 7 continuously receives the signal output by the exclusive-or gate and records the duration of the low level; when the controller 7 detects that the time for the xor gate to continuously output the low level exceeds 5s, the process proceeds to step three. The dropping time interval of two drops of medicine in the transfusion can not exceed 5 seconds; therefore, when the output of the exclusive-or gate is low for 5s, the liquid medicine is completely dripped.
And step three, the controller 7 controls the adjusting motor 304 to rotate, so that the infusion hose is pressed tightly, and the liquid medicine can not be continuously infused into the human body. Meanwhile, the controller 7 sends a needle pulling signal to the upper computer 8; the upper computer 8 informs medical staff to help the patient to pull out the needle.

Claims (6)

1. A venous transfusion detection device comprises a disposable transfusion device; the method is characterized in that: the device also comprises a vibration detection component, a battery, a vibration power generation circuit, an alarm circuit and a signal conversion circuit; the disposable infusion apparatus comprises a drip cup; a piezoelectric piece insertion groove is formed in the side part of the drip cup; the piezoelectric piece insertion groove is communicated with the external environment and is not communicated with the inner cavity of the drip cup; the vibration detection assembly comprises a piezoelectric sheet, a first arc-shaped plate and a second arc-shaped plate; one end of the piezoelectric sheet is fixed with the inner side surface of the first arc-shaped plate; the first arc-shaped plate is hinged with one side edge of the second arc-shaped plate; permanent magnets and iron blocks are respectively embedded at the edges of the other sides of the first arc-shaped plate and the second arc-shaped plate; the first arc-shaped plate and the second arc-shaped plate encircle the drip cup; the piezoelectric sheet extends into the piezoelectric sheet insertion groove, and the top surface of the piezoelectric sheet is contacted with the upper side surface of the piezoelectric sheet insertion groove; the width of the piezoelectric sheet is smaller than that of the piezoelectric sheet insertion groove; the length of the piezoelectric sheet is less than the depth of the piezoelectric sheet insertion groove and greater than the radius of the drip cup;
the signal conversion circuit comprises a charge amplification chip, a voltage comparison chip and an exclusive-OR gate; the non-inverting input end of the charge amplification chip is connected with the first wiring end of the piezoelectric patch and is grounded; the inverting input end is connected with the second terminal of the piezoelectric sheet, one end of the capacitor C2 and one end of the resistor R7; the other end of the capacitor C2 and the other end of the resistor R7 are connected with the output end of the charge amplification chip; the positive power supply voltage end of the charge amplification chip is connected with a positive power supply; the negative power supply voltage end is connected with a negative power supply;
the voltage comparison chip comprises a first operational amplifier and a second operational amplifier; the positive power supply voltage end of the voltage comparison chip is connected with the positive power supply, and the negative power supply voltage end of the voltage comparison chip is connected with the negative power supply; the non-inverting input end of the first operational amplifier in the voltage comparison chip is grounded, the inverting input end of the first operational amplifier is connected with the output end of the charge amplifier U1, and the output end of the first operational amplifier is connected with the anode of the diode D2 and one end of the resistor R8; the cathode of the diode D2 is connected with the first input end of the exclusive-OR gate; the other end of the resistor R8 is connected with a positive power supply; the non-inverting input end of a second operational amplifier in the voltage comparison chip is connected with the output end of the charge amplification chip, the inverting input end of the second operational amplifier is grounded, and the output end of the second operational amplifier is connected with the anode of the diode D3 and one end of the resistor R9; the cathode of the diode D3 is connected with the second input end of the exclusive-OR gate; the other end of the resistor R9 is connected with a positive power supply;
the vibration power generation circuit comprises a rectifier bridge and a voltage comparator; the first input end and the second input end of the rectifier bridge are respectively connected with the first terminal and the second terminal of the piezoelectric sheet; the positive output end of the rectifier bridge is connected with one end of a capacitor CE1, one end of a resistor RE1, a positive power supply voltage end of a voltage comparator, one end of a resistor RE3, one end of a resistor RE4 and the source electrode of a fourth field-effect tube M4, and the negative output end of the rectifier bridge is connected with the other end of the capacitor CE1, one end of a resistor RE2, the negative power supply voltage end of the voltage comparator, the source electrode of a third field-effect tube M3, one end of the capacitor CE2 and the negative electrode of the battery; the inverting input end of the voltage comparator is connected with the other ends of the resistor RE1 and the resistor RE2, the non-inverting input end of the voltage comparator is connected with the anode of the battery, and the output end of the voltage comparator is connected with the grid of the third field-effect transistor M3 and the other end of the resistor RE 3; the drain of the third field effect transistor M3 is connected with the gate of the fourth field effect transistor M4 and the other end of the resistor RE 4; the grid electrode of the fourth field effect transistor M4 is connected with the other end of the second capacitor CE2 and the anode of the battery;
the alarm circuit comprises a resistor R1, a resistor R2, a resistor R3, a resistor R6, a capacitor C1, a voltage-regulator tube D1, a buzzer, a first field-effect tube M1 and a second field-effect tube M2; one end of the resistor R1 is connected with the output end of the exclusive-OR gate, and the other end is connected with the grid of the first field-effect transistor M1; the drain electrode of the first field effect transistor M1 is connected with one end of a resistor R6, the other end of the resistor R6 is connected with a resistor R2, one end of a capacitor C1 and the cathode of a voltage regulator tube D1; the sources of the first field-effect transistor M1 and the second field-effect transistor M2 and the other end of the capacitor C1 are grounded; the other end of the resistor R2 is connected with the button switch and one end of the resistor R3; the other end of the resistor R3 is connected with the positive terminal of the buzzer; the negative wire of the buzzer is connected with the drain electrode of the second field effect transistor M2; the resistor R2 and the capacitor C1 form an RC charging circuit; the charging constant of the RC charging circuit is greater than or equal to 4 s; the stable voltage of the voltage regulator tube D1 is 0.5-0.8 times of the output voltage of the battery.
2. The intravenous infusion testing device of claim 1, further comprising: the device also comprises a controller and a flow rate adjusting mechanism; the flow velocity adjusting mechanism comprises an adjusting base, an adjusting slide block and an adjusting driving assembly; an infusion tube channel is arranged in the adjusting base; an infusion hose on the disposable infusion apparatus passes through an infusion tube channel on the adjusting base; the adjusting slide block and the adjusting base form a sliding pair; a flow regulating pressure head is arranged on the regulating slide block; the flow regulating pressure head extends into the passage of the infusion tube and props against the infusion hose; the bottom surface of the transfusion tube channel is not parallel to the axis of the adjusting screw rod; the control interface of the adjusting motor is connected with the control output interface of the controller through a motor driver; and the signal input end of the controller is connected with the output end of the exclusive-OR gate.
3. The intravenous infusion testing device of claim 2, further comprising: the controller and the upper computer are in wireless communication through the wireless module.
4. The intravenous infusion testing device of claim 2, further comprising: the adjusting driving assembly comprises an adjusting lead screw and an adjusting motor; the adjusting screw rod is supported on the adjusting base; the adjusting slide block and the adjusting screw rod form a screw pair; the adjusting motor is fixed on the adjusting base, and the output shaft is fixed with one end of the adjusting screw rod.
5. The intravenous infusion testing device of claim 1, further comprising: the type of the exclusive-OR gate is 74LS 86; the model of the voltage comparator is LM 393; the model of the charge amplification chip is OP 37; the model of the rectifier bridge is MB 6S.
6. The intravenous infusion testing device of claim 1, further comprising: the positive power supply is obtained by passing positive voltage output by the positive electrode of the battery through a voltage stabilizing chip; the negative power supply is obtained by a positive power supply through a polarity reversal power supply converter; the polarity reversing power converter is model ICL 7660S.
CN201910344550.8A 2019-04-26 2019-04-26 Venous transfusion detection device and detection method thereof Expired - Fee Related CN110152117B (en)

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DE10349761A1 (en) * 2003-10-24 2005-06-09 Fresenius Kabi Deutschland Gmbh Device for regulation of flow in artificial alimentation, assembled of a movable and a stationary jaw
CN2848235Y (en) * 2004-04-10 2006-12-20 朱方文 Transfusion monitoring apparatus for medical infusion system
WO2007007961A1 (en) * 2005-07-14 2007-01-18 Yong Hwan Kim Ringer injection safety system
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