JPS59166816A - Flow monitor device with optical sensing chamber - Google Patents

Abstract

(57) [Summary] This bulletin contains application data before electronic filing, so abstract data is not recorded.

Description

DETAILED DESCRIPTION OF THE INVENTION Field of the Invention The present invention relates generally to flow monitoring devices, and more particularly to an improved droplet monitoring system including improved lens capabilities necessary to simplify droplet collection and measurement. The present invention relates to a gravity feed rate control device and a urine output monitoring device, each using size measurement technology.

BACKGROUND OF THE INVENTION In the development of fluid flow monitoring devices, early flow monitoring devices were simple drop recorders known as drop counters, now known as flow monitoring and control devices. Flow monitoring devices are used to monitor urine formation by a patient. Other flow rate monitoring devices are 1■
It is used to monitor and control the administration of fluid to a patient, such as by injection. Additionally, mechanical and electronic infusion pumps and controls are now used for parenteral and enteral applications.

There are basically three classes of devices for 1v infusions: gravity 1v dosing systems, infusion reservoir 1j control devices, and infusion pumps.

Gravity 1v dosing systems use a conventional bag or pin containing the fluid or drug and a flexible dosing device. Typically, flow control for this dosing device is provided by a manual flange of the screw or roll type. The height of the bottle provides the pressure head that allows the fluid to overcome the venous pressure and allow the drug to enter the venous system. However, recently, the effectiveness of gravity-based systems has been questioned due to the inaccuracy of flow rates.

The injection control device also operates at 1 gravity, similar to the 1v system, and does not apply pressure. The controller electronically counts the droplets and mechanically and electronically pushes out a volume of fluid.

Because these infusion control devices have relatively few moving parts, they are less complex and typically less expensive than infusion pumps, and have fewer maintenance problems.

Infusion control devices are divided into two categories: volumetric and non-volumemetric. In the case of non-capacitive control devices, accuracy is determined by the droplet delivery rate. The key difference from typical 1V devices is that in capacitive control devices, the flow rate is adjusted automatically rather than manually.

Infusion pumps differ from other methods in that they do not rely on gravity to provide the pressure necessary to inject the drug. Pressure is provided by a syringe, a constrictor or roller device, or an electric pump motor that operates a fillable chamber calibrated to deliver a defined amount of fluid. Most pumps are volumetric and can be adjusted to deliver medication under different pressures. Among the many problems associated with infusion pumps are air intrusion despite the use of filters, dry IV bath solution bags, clogged catheters, and lack of filtration. Fluid overflow, phlebitis, 1v
This can cause problems such as pain in the area.

Recently, there has been interest in providing highly accurate gravity-type 1v dosing control devices. An example is 5adller
His U.S. Patents No. 105,02g and MarX
No. 'I,/73.22'1. These patents suggest a solution to make drop recorders and control devices more accurate.

For urine volume monitoring devices, a number of techniques have been developed to monitor urine volume, including measuring the amount of fluid collected and the fluid level using ultrasound, and measuring when urine is collected in a bag. This includes techniques such as metering, the use of spin turbines, and other similar techniques.

In intensive care, it is important to accurately monitor the amount of urine excreted by a patient in order to facilitate diagnosis of the medical condition the patient is suffering from. Additionally, it is important to accurately know the urine volume in order to make clinical decisions regarding the appropriate fk amount and type of intravenous fluid to be administered to the patient. Therefore, the urine flow rate at various times is an important parameter for the clinician to evaluate.

Therefore, there is a need for a gravity feed 1 injection control device that uses improved droplet size measurement techniques and includes accurate lens capabilities to simplify droplet collection and measurement.

Similarly, there is a need for a urine output monitoring device that includes an optical sensing chamber and an electronic monitor that can accurately measure droplet volume and flow rate. The present invention is directed to meeting these needs.

SUMMARY OF THE INVENTION Seven features of the present invention reside in a gravity feed rate control system with an optical sensing chamber and an electronic controller capable of accurately measuring droplet volume and flow rate. Another feature of the invention resides in a urine volume monitoring device that also includes an optical sensing chamber and electronic circuitry for accurately measuring droplet volume and flow rate.

Essentially, the gravity-fed feed rate controller comprises a microcontroller that responds to parametric information sent to the system via the keyboard and changing information detected by a novel droplet diameter detector. . The electronic controller causes a linear actuator to control the diameter of the flexible silicone constriction tube in response to parameter information sent thereto and changing information. The seven types of silicone include the silicone found in the 1 system. Under one mode of operation, the diameter of the constriction tube is adjusted to control the droplet size. In another mode of operation, The diameter of the constriction tube is adjusted to control the time interval between droplets.By selectively combining the two modes of operation, precise [17] IV fluids are administered to the patient. .

Also forming part of the system are audible and visual alarms that indicate the volume injected, the presence of air in the 1v line,
Provides indications of low battery voltage conditions, system failure, no flow, and injection completion.

In the case of a urine volume monitoring device, the system basically uses parameter information sent to the system via the keyboard;
and a microcontroller responsive to changing information detected by the novel droplet diameter detector. The urine output monitoring device measures the size of the urine output formed by the droplet detector in response to the noclameter information and changing information sent to it, and uses this information to carefully and accurately measure the urine output. Monitor.

Accordingly, it is a primary object of the present invention to provide a flow monitoring device that allows IV bath solutions to accurately measure urine droplet volume and flow rate.

Another object of the invention is to provide an improved gravity feed rate control system.

Yet another object of the invention is to provide an improved urine output monitoring device.

Yet another object of the present invention is to provide an improved optical sensing chamber that facilitates accurate measurement of droplet volume and flow rate.

Yet another object of the present invention is to provide a universal disposable optical sensing device that accurately measures droplet volume.

DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS In the description of the preferred embodiments of the invention, which are illustrated in the accompanying drawings, specific terminology is used for the sake of clarity.
It is to be understood that the invention is not limited to the particular terms so chosen, but that each particular term includes all technical equivalents that function similarly to serve a similar purpose.

Supply amount #l] The basic element that makes the m device fW is the first
It is indicated generally by the reference numeral 10 in the figure. The center of the gravity-type supply control device is the microcontroller 21.
It is 2. In the preferred embodiment, this microcontroller is a ROMless microcontroller o-7 (Nat
It is used with an auxiliary EPROM (such as the product identification number CoPILt0gLS) manufactured by ional Semlconductor. However, it will be understood that this ROM-less microcontroller and its auxiliary FROM may be replaced by a general microcontroller that includes a ROM. The keyboard control section 14 is a microcontroller 12.
It is designed to provide information to This control panel is used to give several commands to the microcontroller like start, pause, change flow rate, etc. Some other information such as dosing schedule is also provided to the microcontroller via the control panel.

Also forming part of the feed and clear control system is a novel droplet diameter detector 16, which will be described in detail below. Suffice it to say here that the detector 16 provides information to the microcontroller via line 18. This fW 4 is a signal representative of the presence of a driftwood droplet as it passes through the IV device and is a function of its diameter.

Once informed by key date 14 and droplet diameter detector 16, microcontroller 12
The motor drive 22 activates a linear actuator in the form of a step motor 24 to determine the size of the droplet passing the droplet detector or the size of the droplet passing the droplet detector. Vary the diameter of the silastic tube by changing the time interval.

Automatic motor stop circuit 85 communicates with microcontroller 12. As discussed in more detail below, when the motor stops, the microcontroller is notified that power has been removed. The microcontroller 2 then supplies the cage from the battery, which in effect causes the motor 24 to tighten and close the silastic tube.

The delivery rate i [i controller is 7
used as a part. Referring to diagram Ω, gravity formula 1v
Describe the administration system. Basically, this system
A conventional bag or bottle 30 containing a fluid stimulant and a dispensing device 32 are provided. The needle 34 is provided so as to enter the fluid container 3o. A rung such as a roller cranometer 36 is arranged downstream of the needle 34. Further downstream, an injection location 38 is defined within the PVC tubing. Below this injection site, the PVC tubing terminates at point 40, where the PVC tubing is secured to a 0T cast tube 42 of silastic or other type in a conventional manner such as by friction or adhesive.

The other end of this silastic tube is similarly fixed to the upper part of the droplet volume detection chamber 44 forming part 7 of the droplet diameter detector 16 . The bottom of the chamber 44 is secured, also by friction or adhesive, to a PVC tube 46, the distal end of which can be secured to a suitable needle 48 for injection into the patient's arm. An injection site 48 can be provided anywhere on the tube 46. As the droplets pass through the droplet volume sensing chamber 44, their presence and spacing is detected by the feed rate controller 10.

The keys are driven by a suitable LCD driver 51 under signals generated by the microcontroller to enable the user to determine the type of information input to the microcontroller by the key control A'. LCD
(Liquid crystal display device) 50 is provided. Additionally, several protection features are provided, such as an air intrusion detector 52, a low battery voltage detector 54, and a door open detector 56. Each of these detectors sends information to the microcontroller 12, which sends information to the fP@detector 58.
Activate.

The sensing chamber 44 will be described in detail with reference to FIGS. 2 to 9, FIG. S, and FIG. 7. In its intended position of use, as shown in Figures 1 and 2, sensing chamber 44 is essentially an elongated hollow hole oriented vertically.
Equipped with unong.

Looking at the cross section (Figure 7), it is 1m160 outside Howsong.
is generally rectangular. The seven parts of the interior body of chamber 440 are comprised of vertically oriented walls 61-6.
It is 4. Each type has a rectangular cross section with a continuous line around one side. In construction, walls 61 and 63 are oriented generally parallel to each other, as are walls 62 and 64. The various inner surfaces are usefully curved to form t lenses 11,73,75 and 11. It is sometimes important to note that these lenses are molded to match dimensionally and that these lenses are often approximately 2
It is a point exhibiting a focal length of inches.

A number of splash walls 361 are arranged inside the bag.
These serve two main functions:

(1) Minimize droplet formation on the lens surface.

Reduces internal nitrogen volume, thus reducing potential dose and reducing time between tube occlusions.

A hole 68 is centrally located in the hole 66 of the chamber 44.

Extending downwardly from this hole is a hollow projection 10.

This protrusion 10 is fixed to one end of the PVC tube 46,
Provide fluid communication between the tube and the interior of the cavity.

At the upper part of the chamber 44, a force plate or character f72 is provided. The inside of the cap is the internal volume 4 of the chamber 44.
Define the final surface constituting 5. A hole 74 is located in the center of the cap. Projecting upwardly from this hole is a hollow protrusion 76. This protrusion is connected to one end of the silastic tube 42 and provides fluid communication between the interior of the sensing chamber 44 and the silastic tube.

With reference to Figures S, 6a and 6b, details of the structure housing the feed rate control device will now be described.

How song 300 is generally divided into Ω parts. As shown in FIG. The left side portion 304 of the housing defines a portion that receives the electronics associated with the operation of the common supply control system, and provides a control channel including the heat source 14 and the table 75 device 50 (+-).

Door 306 is hinged so that it swings freely back and forth and in its open position, cavity 308 is
A droplet volume detection chamber 44 is mounted here. In its closed position, door 306 has cavity 308 .
to secure the droplet volume sensing chamber 44 within the cavity 308.

The cavity 308 is configured to receive the small volume detection chamber 44 in one direction. This is the droplet volume/direction chamber 44
This is accomplished by providing keys 310 and 312 on the top of the. These keys are located on the I41 wall 31 of the cavity 308.
The key grooves 314 and 316 provided in the parts 8 and 320 are fitted into the key grooves 314 and 316, respectively. Channel 3 is located at the top and bottom of chamber 308.
22 and 324 are provided to allow insertion of an administration device associated with the IV system. At the top of the cavity 308, an actuator motor 240 and a
6 is formed. This planter moves to the right or left as shown in Figures S and 6b. This grand luster is
When this is moved to the left, Silastic Tube 4
2 against anvil 330 and provides a convenient means of controlling compression of tube 42.

The rear surface (not shown) of the main body 300 includes a conventional flange arrangement for securing the feed layer controller housing to a conventional 1V stand.

In use, sensing chamber 44 is positioned within the feed rate control device in the orientation shown in Figures S and 6b.

When placed in the supply rate control device and used for one time, an infrared LED (light emitting diode) 80 is inserted into the slit 82.
A beam of light is transmitted through the The light beam passes through the lens 71'j
The light passes through the lens 13 and is received by the phototransistor 84. As can be seen in FIGS. 3 and 6b, these lenses are arranged to form a series of parallel rays 86 within the chamber cavity 45.

Having described the details of the sensing chamber above, details of other elements of the feed layer controller will now be described.

The center of the supply layer control device t10 is the microcontroller 1
It is 2. In the preferred embodiment, the microcontroller is manufactured by National Semlconductor under product designation C0PI (74'LS Ro
It is a microcontroller without M. A menu and keyboard 14 are provided for the user to interface with the microcontroller. The nine keys on the keyboard are 2. Y! Each of the 11 three lines is connected by a general direction. The /th set of lines 81 are connected to three bidirectional 110 (input/output) ports provided on the microcontroller. 2nd set of 3 lines 8
3 is yet another 31 provided in the microcontroller.
Connected to a hard bidirectional I10 boat. Several commands can be given to the microcontroller via the keyboard, such as start, stop, and change direction.

Refreshingly, the prestige to be administered is established. This dose is monitored by pressing the appropriate keys. Additionally, a test key is provided for testing and calibration during manufacturing. A frequency of approximately =109 MHz is provided by the clock source to operate the system oscillator of the microcontroller 12.

The memory 86 forms part of the feed rate control device.
It is. This memory, in the preferred embodiment, is N
It is in the form of an erasable programmable memory, such as product designation NMC, 2'7G, 7.2, manufactured by ational Semlconductor. Such memory and ROM, microcontroller
It will be appreciated that any known microcontroller containing a fiROM may be substituted. Memory is erasable and electrically reprogrammable 1lKUV EF
It is a ROM. This memory is enabled by signals received on line 88 from the microcontroller.

g 1f61 bidirectional ROM address data port is provided in the microcontroller, which also
It receives data information and transfers address information via line 90. Address information is g bit latch 92
After passing through, it was sent to EPRCM with a 2-in 94. On the other hand, Gata passes through Fin 96, which joins Line 9o, and then E.
Uke is taken from P R0IVI. The microcontroller further includes additional ROM address outputs ip, which provide address information to the memory via lines 98.

A door sensor 100 consisting of a light emitting diode that illuminates a phototransistor is generally located in the lower corner of the receiving cavity 308. Door sensor 100, line 10
2 is used to send signals to the microcontroller's general purpose power 104. A high level signal appearing on line 102 indicates that the supply layer controller door is closed.

Another line 106 is general purpose input 1 of the microcontroller.
Connected to 08. Lines 102 and 106 are connected together via diode D/. The anode of the diode is connected to line 102. line 10
6 is then connected to the cathode of diode D2, and its anode is connected to the anode of diode D3.

The cathode of diode D3 is connected via line 112 to a further general purpose power source 110.

The junction of the anodes of diodes D2 and D3 is on/off.
Center connection 114 of off switch 116 and diode D4
connected to the cathode of The anode of diode D is then connected to the input of voltage A rectifier 118. In the preferred embodiment, the voltage regulator is an S Volt Lenz three terminal regulator, which is generally a Nati
It is called LM7gLO5ACZ manufactured by Onal 5erniconductor. The output port and common port of this voltage regulator are connected to the capacitor C3, while its common port and input port are connected to the capacitor C3 and ground. A voltage all resistor 118 is used to provide a regulated supply voltage, 5V in the preferred embodiment.

The microcontroller includes a general purpose output 120 connected to a MOS FET-/ (Metal Oxide Semiconductor Field Effect Transistor) dart.

The drain of this FET-/ is connected to the dart of FET-co. The source of FET-7 is grounded, while the FE
The source of T-co is connected to the gate of FET-/ through resistor R2. The drain of FET-7 is connected to the input of the pressure regulating toilet. Regarding the double throw switch 116,
The lower contact of the switch is grounded, while the upper J point 130 is connected to the source of the FET-co.

When switch 116 is turned from on to off, diodes D2 and D3 conduct to interrupt lines 108 and 110. This allows the microcontroller 12 to know that power has been cut off. Then,
Microcore) o - la turn on line 120
The ON command is issued to direct the supply voltage from the battery 11T to the voltage regulator 118 via the diode D4 during the next L seconds. The V@regulated voltage from regulator 118 energizes motor 24, which is commanded to occlude silastic tube 42 and stop 1v flow to the 1v system.

After this 772 seconds, the system turns off.

Similarly, when door 306 opens, line 104 goes low. This causes diode D/ to become active, which causes lines 104 and 108 to both go low. In this way, the microcontroller knows that the door is open and not out of power. By connecting diodes D2 and D3 anode-to-anode, the microcontroller can distinguish between "door open" and "door closed."

Microcontroller 12 has bidirectional 110 port 1
40 and a general purpose output 142, which are connected to a Schmitt trigger 144, the output of which is connected to the dart of FET-3. The north of FET-3 is connected to ground, while the drain of FET-/ is connected to
connected to the input of This shift renoster, in the preferred middle 'bI column, is a g-bit a-column output serial shift register, such as a National Semlcond
The product name is MMiC/Otohiro, manufactured by Uctor. The shift resistor generates a first output signal on line 148, which is sent to linear actuator 24. Furthermore, shift reno stars are on lines 150 and 152.
These signals cause green and red light emitting diodes to be activated, respectively. In addition, the shift restor generates a signal on line 154 that activates alarm 58 (+-).

Further both the microcontroller's inbuilt 110 port 160 and general purpose output 162, along with general purpose output 142,
The LCDCD driving device 51 is connected, and this driving IJtJJ device is an LCD display device! ! An appropriate signal is generated on line 166 to activate t50.

An A/D (analog-to-digital) converter 110 also forms part of the supply control system. This converter is
In a preferred embodiment, National Semlco
Product designation number ACJCO manufactured by nductor company
g3'1. The A/D converter 110 is connected to line 1.
12, is activated by a signal applied to the serial bidirectional I10 port via the serial clock line 174 and the chip enable line 116. A/D converter, two inputs 178 for receiving and receiving analog data.
Contains ~181. Input 178 Vi bubble sensor 5
Uke loses the analog signal from 2. This bubble sensor is activated by a signal generated from the microcontroller's general purpose output 182. Air bubble sensor 52 generally has L
It is composed of a combination of an ED light source 260 and a phototransistor 262. A bubble sensor is placed in chamber 308 to monitor the flow of 1v solution through lower tube 46. Input 1γ9 receives the signal from droplet sensor 16, which sensor is actuated by a signal generated at general purpose output 184 of the microcontroller. Input 180 receives the battery low voltage reference signal l! from block 54. ! -Uke is taken.

Preferably, the input 181 receives and receives an ambient beam signal from the section beam detector 55, which is located somewhere on the exterior surface of the Hawthong 300, for example in the upper left corner adjacent to the display 5°. Placed.

410 is another 10 pieces that make up the supply conveyor # device.
This is the floating trigger commonly shown in . This 70-ring trigger basically consists of a slow resistor, a capacitor, and an operational amplifier. In particular, the output of the phototransistor 84 of the skin diameter detector 16 is transmitted to the operational amplifier 2 via a resistor R and a capacitor 06 connected in series.
into the negative input of 02. The output of this compensation circuit d202 is fed back to the negative input of the operational amplifier 202 by a parallel connection of a resistor Rg and a capacitor CG.
It is also connected to the positive input of the arithmetic amplifier 62o6.

The output of the operational amplifier 206 is sent to the dual 110 port 212 of the microcontroller. The output of the malfunction diameter detector is also sent to the power of the operational amplifier 204 via the resistors R10 and R/O which are connected in series. capacitor c1
0 is connected in parallel with resistor R/B.

The output of operational amplifier 200 is sent to the positive input of operational amplifier 204 and fed back to the negative input of operational amplifier 200. The positive input of the operational amplifier 200 is a resistor R2.
It is grounded through a parallel connection of J and capacitor C/2. Output V′i of operational amplifier 204/pair series resistance R
/g and grounded via R20. The series connection of these resistors is connected to the negative input of the 1ytX amplifier 206.

The output u of the operational amplifier 204 is also sent to the positive input of the IAN-amplifier 202. The negative input of the operational amplifier 204 is connected to the positive input of the operational amplifier 202 via a grinding resistor R/da.

The idea behind the floating trigger is to provide a signal representative of droplet size or droplet time interval regardless of changes in the VCE of phototransistor 84.

A common phenomenon in light emitting diodes and phototransistors is electrical drift, which causes the collector emitter pressure, or VCE, to also drift. Such a VCE
The drift of will affect the measurement accuracy of the droplet time interval. Additionally, power supply drift occurs in the electronic circuitry found in supply control devices. When the power supply drifts, the LED and phototransistor also drift, which adversely affects the VCE of the phototransistor 84.

Refreshingly, the presence of fluid or droplets thereof on the sidewall or lens of the disposable droplet sensing chamber 44 causes a change in VCE.

The output of the phototransistor 84 of the irregular diameter detection 416 is sent to the negative input of the arithmetic amplifier 4202 via a resistor H6 and a capacitor C. A bias voltage of approximately +2.0 volts is also sent to the positive input of operational amplifier 200 through resistor R23. The output of the operational amplifier 200 is approximately θ port and the capacitor c/.

It is sent as a bias voltage to the parallel series of resistors R/B, and also to the positive input of the operational amplifier 204.

The resulting DC voltage is distributed between resistor R10 and R/A and appears at the positive input of operational amplifier a 202.

The droplet time interval signal from droplet sensor 16 is amplified through resistor R and capacitor C until such time as the voltage level is set via resistor R/g and R20. The AC power is coupled to the purchased capacity of the container 202. Arithmetic amplifier 2
The above trigger voltage sent to the negative input of 06 is j KAC(i
Pickoff point 75 on No. f; floats up and down in the opposite direction. In this way, the droplet spacing is insensitive to electronic drift in general and VCE drift in particular.

The elements constituting the supply rate control device have been explained in detail above, but in the preferred implementation of the supply rate control device, 1. Please read below. No. 31, No. 6b and No. 7
Referring to the figure, a light source 80 generates a beam beam 81;
This light beam passes through the slit 82 and passes through the small sensing chamber 44.
]81 lens. Lenses 71 and 73 are configured to generate parallel light; #86' within the nozzle. After the light cliff of the LED light passes through a lens and a slit, it is received by a phototransistor 84. The output of this phototransistor, in combination with a floating trigger, provides an input signal to the microcontroller. The light source 80 and phototransistor 84 thus define a beam plane through which the tube passes, in contrast to the phototransistor 82. As the droplet traverses the beam plane, the output of the phototransistor appears as an analog signal that rises when the droplet enters the parallel beam. The output of the phototransistor is constant while the droplet is contained in the parallel beam, but gradually decreases as the droplet exits the parallel beam. This signal is sent to the floating trigger 210, and the trigger 210 with
generates a square wave whose time width (in milliseconds) is proportional to the diameter of the small end quotient. In particular, the output of the floating bird is at a high level when no droplet is present, and at a low level when the droplet passes through a boundary defined by a parallel beam of light.

Figure 2a? For reference, 1/ represents the time required for the droplet to reach the distance from the orifice O. hour 115
t2 represents the time required for the droplet to travel a distance equal to its lK diameter d. Therefore, a known free fall equation and gravitational constant "a" are used. Therefore, it becomes. If L is chosen smaller than d, T becomes y/U d
2 is equal to y, that is, T - becomes D.

The volume of the droplet is controlled by 1' for a narrow range of values.For the volume of a small cylinder within a narrow range, the linear approximation of
becomes.

The square wave 1g generated at the output of the floating trigger is approximately 20 milliseconds in duration and is sent to the microcontroller. The microcontroller can solve the equation for a volume equal to TK. Once the correct volume is known, the microcoit roller generates a signal to the shift register 46, which causes the linear actuator 24 to move inward or outward to constrict or open the silastic tube 40, thus When a droplet is introduced into the droplet volume chamber 44, it can be shut off. In this embodiment, the microcontroller 2
A distorts the time interval between individual droplets so as to maintain an unobtrusively accurate volumetric flow rate. By measuring the droplet size centrally, the opening interval by the linear actuator can be easily varied and thus the desired flow rate can be easily maintained.

With the exception of the VC, the linear actuator motor 24 and drive 22 work under two 7-parameters that are controlled by a microcontroller. First, the microcontroller generates a signal that causes the linear actuator to completely constrict the silastic tube. The microcontroller then controls l in small predetermined steps until a droplet is detected by the droplet diameter detector 16.
Generates a signal to move the J near actuator outward.

The number of steps 6 it took to detect the first droplet is placed in memory within the microcontroller and used as a reference for each person's droplet. Therefore, determining the time interval between droplets is based on two factors: In other modes of operation of the present invention, the set flow rate desired by the user and the time interval actually measured in milliseconds is determined by the droplet flow rate, rather than the time interval between droplets. The size of can be changed. The microcontroller 12 causes the linear actuator 24 to completely constrict the silastic tube 42 . The microcontroller then generates a signal to move the IJ near actuator back. The microcontroller then checks to see if droplet sensor 16 detects a droplet. . If not detected, the linear actuator will
Commanded to step back. This continues until a droplet is sensed by the droplet sensor 16. When a droplet is sensed, the microcontroller senses and measures the volume of the large droplet and then moves the linear actuator three steps to stop the flow. After a predetermined time interval that remains constant throughout a particular operation, the microcontroller moves the linear actuator outward three steps until a droplet is detected. The volume of the droplet is then measured, and if it is larger than desired, the linear actuator is moved further in the droplet reduction direction to make the cross-sectional area of the silastic tube 40 smaller and the next droplet volume smaller. The volume of the droplet should be very small. The droplet-to-droplet spacing is thus held constant and the volume of each droplet is measured and used to adjust the degree of compression of the tube. If the droplet becomes smaller than expected from the equation, the position of the motor is adjusted to increase the volume of the next droplet. Similarly, if the droplet volume is measured and exceeds it, then the motor is started to adjust to reduce the size of the next droplet. Therefore, the flow rate can be maintained accurately.

Before the first droplet is passed through the droplet volume measurement chamber 44, the motor 24 closes the silastic tube 42 as much as possible. The motor 24 then moves 7 degrees/step (approximately 0.002 inch-o,
osraa) and waits for the tube to open enough to pass fluid through the tube and cause a droplet to form and fall.1.When the first droplet is detected, the motor moves its Knowing the motor relative position (MRP), fluid flow can be stopped completely with only one or three steps (compared to 39 steps from the complete fluid cutoff position to find the first droplet). I need).

From this point, the motor moves backwards at preset intervals to allow the droplet to fall.

Therefore, compensation by the motor adjusts the "effective orifice size" to maintain uniform droplet volume. This, combined with constant droplet frequency, provides constant flow rate control. In this way, the feed rate control device can take advantage of the effects of gravity feed pressure.

In order to administer the correct amount of 1.5 solution, one important thing happens at the same time in the feed rate controller 10. If the droplet size changes slightly (e.g. θ, Og,
2cc to 0.0g6cc), the microcontroller 12 increases the time interval when the next drop is to be formed and then actually operates the motor 24 in the tube opening direction at that time. Therefore, as the volume of the droplet increases, the time interval increases, thereby maintaining a constant 1v solution infusion rate to the patient.

However, it is important to have a feed rate control device, not just for varying time intervals, but for certain conditions to vary the droplet size (volume) to maintain a constant injection flow rate. . The mechanism for varying the droplet size and thus the droplet volume is implemented by varying the effective size of the internal orifice of the pincer tube 42. Droplet size increases by 50% or more due to various fluid formats, viscosities, temperatures, stepper motor actuation, droplet attachment to droplet formation orifices, and formation of trailing or extra droplets. was found to change rapidly. If an extra droplet of 1V fluid enters the measurement chamber 44 at an inappropriate - or unexpected time (due to a sudden change in head length etc.), it can be removed by moving the stepper motor 24 one position (i.e. , by decreasing the effective orifice diameter) the motor relative position (MRP) is changed. If the entrainment (7E) misalignment is very large, i.e. more than 70% of the normal droplet, then the M
RP can be changed.

In addition to compensating for droplets other than the intended droplets, the feed rate control device normally controls when the droplets formed are too large or too small, i.e. when the droplets are 70% Adjust the droplet size and flow rate even when the concavity is exceeded. If the main droplet being observed is larger than 0.099 cc, l'lRP will be pushed in the in direction by 7 positions. The king droplet is o, ob.

If CC is smaller, the MRP is pulled out seven positions and the self-acting internal orifice of tube 42 is widened. Even if this 0. ObO~0,099c
Even if the main droplet is within the range of c/small droplet, if the main droplet is larger or smaller than f: 110% of the last normal main droplet, the MRP is pushed inward by 7 positions. Or again tj, pulled in the out direction. 'Gushing' (,2
If more than one primary droplet adheres to each other in a shape other than spherical), the floating trigger 210;
o, obo to 0.090 cc/droplet/step.

Under the control@j signal from microcontroller 12, linear actuator or stepper motor 24 operates as follows to effectively control droplet volume and flow rate through a system. The initial actuator of the quantity control device, the plunger 326 of the Tanabata 24, is pushed as hard as possible and further and further into the tube 42 and the anvil 330, so that no driftwood flows at all. ,
The tube is placed in a completely fluid-tight state, when the start button is pressed, the motor moves in the out direction in increments/steps until the first droplet is observed by the droplet diameter detector 1ti. When the motor is moved in the 3-step in direction, this position of the motor is called the motor relative position (MRP), and an arbitrary value g is specified. Based on the value of the first sensed and measured droplet volume, and taking into account the other factors mentioned above for droplets other than the intended droplets, the next K (1) The next time interval is calculated by the microcontroller.G
2) The motor is g, which represents the number of steps from completely blocking the tube to barely inserting the tube.
The value is in MRP. and when the time interval is exceeded, the motor 24 moves in the out direction by 3 steps (in 7 degrees/step each droplet is observed every Oms), and when the droplet is detected by the droplet diameter detector, The step motor is pushed back three steps.

If a droplet is detected by the droplet detector 16 at a predetermined time, the motor moves J steps in the out direction, and then the motor moves three steps in to keep the MRP in place. However, if the pressure head changes slightly and the motor moves in the out direction by three steps, during which the canister does not enter the chamber 44, the motor 24 will no longer move.
Move out by a step and the droplet detector observes the droplet. Therefore, the motor immediately moves in the in direction by 3 steps, which changes to pMRPti (i.e.,
The effective orifice of tube 42 opens an additional step or approximately 0.002 inch).

If MRP is set to g, the reverse is also true. If a predetermined time interval has elapsed and the motor is moved in the out direction by a /step (first costep of three steps), no droplet is observed, and the motor is moved a further /step (first costep of three steps). ) in the out direction and a droplet is observed. Immediately the motor is moved three steps in the in direction. As a result, the effective internal orifice equal to the new MRPt47 is closed and a new MRP is established. As mentioned above, the MRP is in a position where the tube is fused and occluded. From this position the tube is opened at each step and the controller waits to see if a /JS drop has been observed by the droplet detector. Other conditions may occur, but these are taken into account by the feed rate controller. Assume that MRP is equal to , but that coagulation occurs at location 1 and therefore no fluid flow occurs. When the time interval has elapsed (a droplet is expected to come, but it cannot come because of the coagulation at location 1), the motor 24 moves in the out direction for the first three steps, and No droplets detected by the drop detector. The motor then continues to move in the out direction in 7 degree/step increments, the controller observes the drop, the motor steps again, and the cycle repeats until the motor has moved a full step in the out direction. At this point, a ``resister down'' and ``flow change'' are issued, and the motor is immediately moved completely in the in direction as in the initial or rest state.

In summary, feed controller 10 typically operates as follows. Once the predetermined time interval has elapsed, the squeezing motor 24 is moved in the out direction in steps (typically three steps total) until a droplet is formed. As soon as the droplet crosses the light detection plane 86 of the droplet measurement chamber 44, the feed rate controller begins measuring its volume. After the droplet volume is measured, the controller determines whether the droplet volume is within the ±70% window established by the controller. Regardless of whether the droplet volume is within the specified window, the motor moves in the in direction by /step. The controller then determines whether the droplet passing the droplet detector is part of the jet stream. Thereafter, the motor moves in the in direction by a costep. In this respect, the controller controls the motor relative position (MR
Determine whether P) should be varied based on droplet volume. If so, the relative motor positions are changed. The controller then calculates the time interval when the next droplet should be formed.

Rather than being arranged to operate against the fluid conduit 46 extending from the bottom of the lj-barrel chamber to the patient injection site 48, the constriction motor of the delivery control device The droplet forming section 76 squeezes the tube at the top.
is placed above.

The purpose of the feed rate controller is to control the droplet size to maintain a given flow rate. Therefore, in this control device, the plunger and the anvil are connected to the droplet measurement chamber 2.
Before changing the opening of the tube 42 leading to the tube 14, the droplet volume is measured. 'Based on the droplet volume measurements, the tube leading to the droplet chamber is actuated by a plunger and an anobil to control the size of the droplet ultimately formed in this chamber.

In the feed rate control device, the tube 42 is not completely constricted, but is occluded to such an extent that friction within the tube prevents the formation of additional droplets in the droplet chamber. It's just that. Referring to FIGS. 1 and 2, only the tube 42 connecting the droplet volume detection chamber 44 and the conventional 1θ bag or bottle 3o is squeezed or acted upon by the motor 24 and anvil 330. The tube 46 leading from the droplet volume detection chamber 44 to the 1V needle 48 is then unchanged.

The operating procedure of the preferred embodiment will now be briefly described with reference to FIGS. 1, 3, and 7.

If a hospital uses its own 1■ device, it is desirable to use a macro (approx./S droplet/-) non-vented administration device. Referring to Figure 1, the system is first set up by closing the roller clamp 36 of the dosing device. Insert the 1 inch tube 46 into the far end of the droplet volume sensing chamber 44. The other end of the sensing chamber 44 is connected to the IV solution container 3°. 1. Hang the solution container on a regular rack and purge air from the dosing device.

The sensing chamber 44 is tilted about 1, and the lawn clamp 3G is opened to fill the sensing chamber up to the filling line 55 shown. If the dosing device includes a droplet chamber, turn it over and allow it to completely fill to prevent air from accidentally setting off the line alarm. Must be. The roller clamp must then be closed against the 1v tube 32. the administration device is then connected to the injection device;
Droplet flow must be adjusted with roller clamps.

Next, turn switch 116 to the on position. At this time,
The display device 5o displays as shown in FIG. 1θ. Next, the door 30B of the device is opened. In this state, the display device displays as shown in FIG.

With the door open, connect the sensing chamber 44 to the receptacle 308.
Place it in A silastic tube 42 is then placed within the channel 322 above the sensing chamber. Then close the door. With the door closed, place the feed rate controller in sleep mode. The LCD display device 50 displays as shown in FIG. 1.2.

To set the flow rate, the desired increment 100.10 and/or is entered into the microcontroller by pressing the appropriate keys 331-333. In order to advance the numerical value on the display device 55, touch each key. In the preferred embodiment, when a key is touched, the numeric value on the display automatically increases by about/unit every ///2 seconds.

When touching the thousand- associated with the amount to be administered,
The display device 50 displays as shown in FIG. The feed rate controller is still in sleep mode.

The amount to be administered is set as well as the flow rate. Once you have done this, press the start button and the green light 3
40 and flashes after each fluid drop to indicate that the device is operating. The roller clamp 36 must be opened immediately after pressing the start button.

Touching the pause button causes the rate controller to stop injecting fluid. The red light 342 flashes intermittently and the rate controller generates an audible tone every few seconds to notify the operator that the rate controller is not injecting fluid.

If the start button is not pressed within a predetermined period of time, the feed rate controller activates the alarm device 58.

Touching the Pause button again provides the operator with an intermittent audible alarm for a predetermined period of time, such as an additional Ω minute period.

To check the injection amount, press the button labeled // y 1 II. The display device 50 displays the injection amount in milliliters. To reset the injection volume to zero milliliters, press the pause button, then press the v1 button and leave the valve closed for a predetermined period of time.

To change the flow rate, press button "C84" to put the device into rest mode and the display will read as shown in Figure 11I. The new flow rate will be changed in the same manner as the original flow rate set as described above. The start button is pressed to activate the feed rate controller at this new flow rate.

To change the amount to be administered, press the pause button to put the microcontroller into sleep mode. The dose button is then pressed and the display will display as shown in Figure 1S. Enter the new amount as described above and press the start button to reactivate the feed rate controller.

To replace the sensing chamber 44 or 1 tube, or to interrupt operation, press the pause button. then 1
Close the roller clamp 36 against the v-tube 32.

Then touch the pause button twice and open the door 306. The display device 50 displays as shown in FIG.

Droplet volume sensing chamber 44 can then be removed. If a new chamber is used, the procedures described above for purging and filling the sensing chamber must be followed. Then close the door and press the start button to reactivate the control.

1) If operation is to be interrupted, simply turn off the feed rate controller after closing the door.

To replace the IV solution container 30, the supply rate controller 10 is put into a dormant state. Remove the empty 1■ solution container,
Exchange is done in the general and υ way.

The rate controller also incorporates a series of sensors and associated alarms that measure changes in flow rate, air admission, door open status, battery low voltage, no flow rate, and fill completion. .

When the rate controller senses seven of these alarm conditions, the audible and visual alarms are activated and the display 50 indicates the reason for the alarm, unless the injection is complete. Audible alarm 58 is deactivated by touching the pause button. The visual alarm 342 continues to flash a red light beam at predetermined intervals for each light.

The display device 50 is also combined with a black light (250) formed by an electric fluorescent lamp, which is connected to a voltage amplifier 35.
2. When the ambient light is below that level - which is sensed by sensor 55 - the microcontroller generates a line 254 furnace signal which triggers the Schmitt trigger 356 and field effect transistor pair 35.
B activates amplifier 352, providing 200 volts to lamp 350.

In the preferred embodiment, one flow controller issues an alarm when the infusion volume equals the Norset volume to be administered and sets the flow rate to an open-hold flow rate (Kee) of 5 WLl/hr.
open rate ) and continue injecting at this new flow rate.

When the flow rate changes by more than the rate controller 100 control range, audible and visual alarms are activated and the rate controller automatically stops injecting.

To stop the alarm sound, touch the pause button.

1. When air is present in the tube, the feed rate controller will stop injection and issue an audible and visual alarm. The alarm can be stopped by pressing the pause button. If the door to the supply rate control device is opened while it is operating,
The control device provides audible and visual signals. Approximately 7 hours before battery life is reached, the feed rate controller will stop infusion and provide an audible and visual alarm. If no action is taken within a predetermined period of time, the microcontroller will deactivate.

Although the present invention has been described above in terms of a supply rate control device, the implementation of the present invention as a urine monitoring device will now be described.

The basic elements that make up the urine output monitoring device are indicated generally by the reference numeral 210 in FIG. The heart of the urine monitoring device is the microcontroller 212. This microcontroller, in the preferred embodiment, is an FtOM-less microcontroller (National Semlc
Product identification number manufactured by onductor COP
￥04' LS-like cover, this is an auxiliary EPROM
Used with 286. However, this ROMless microcontroller and its auxiliary EPROM are
It will be understood that a general microcontroller incorporating M may be replaced.

The keyboard control panel 214 is connected to the microcontroller 2
12 to provide information.

This control panel provides start, measured quantity display, elapsed time display,
It is used to give some commands to the microcontroller, such as

Also forming part of the urine output monitoring device is the novel droplet diameter detector 16 described above. Detector 16 provides information to the microcontroller via 2-in 18. This information may be a signal representing the presence of urine droplets as they pass through the urine volume monitoring device and is a function of their diameter.

Urine volume monitoring devices are used as part of a urine collection system. FIG. 19 schematically shows a urine collection system according to the invention. Basically, the system includes a catheter 242, one end (not shown) of which is inserted into the patient. The other end of the catheter 230 is attached to the droplet diameter detector 16 in a conventional manner such as by friction or adhesion.
It is fixed to the upper part of the droplet amount detection chamber 244 that forms the section.

The bottom of the chamber 244 is secured to the bag 2 by a tube 246 that collects urine from the patient, also by friction or adhesion.
47 or other suitable container.

As the urine temperatures pass through the drop volume chamber 244, their presence and spacing is detected by the urine volume monitor 210.

Referring to FIG. 17, a suitable LCD driver 251 is used under signals generated by the microcontroller to enable the user to determine the format of information to be input to the microcontroller by means of a keyboard control panel. A driven LCD (liquid crystal display) 25o is provided.

Additionally, several protection features are provided, such as a low battery voltage detector 254 and a door open detector 256. Each of these detectors provides information to the microcontroller '112, which in turn provides alarm 2
58 is activated.

With reference to FIGS. 20 to 217, the sensing chamber 244°0
The individual parts are described below. In the intended position of use as shown in Figures 2/2 and 2q, the sensing chamber 24
4' The embodiment shown here is the same as that already described for the feed rate control device (similar elements are designated by the same reference numerals), with the following differences. As with the feed rate controller, the sensing chamber 244 has vertically oriented walls 61-64. The can wall has a square section 7
The surroundings of two sides are related. Walls 61 and 63 are wall 6
As with 2 and 64, they are oriented generally parallel to each other when assembled. There are nine lenses 7 on the inside of the can wall.
1.73.75 and 77. However, the sensing chamber 244 is the same as the sensing chamber 4.
It does not include nine splash walls 361 as seen in No. 4. □The bottom 66 of the chamber 244 has a hole 68 in its center. Extending downwardly from this hole is a hollow protrusion 70.

This protrusion 70 is fixed to one end of the PVC tube 46,
Fluid communication is provided between the tube and urine collection bag 247 .

In another embodiment (FIGS. 20 and 23), chamber 2
A cover plate or cap 272 is provided on top of 44, which cap is 30" relative to the cross-sectional plane of the sensing chamber.
tilted at an angle of The inner surface of the camp defines the final surface constituting the interior 45 of the chamber 244. Offset to one side of the cap is hole 214. A hollow protrusion γ6 protrudes upward from this hole at an angle o0. This protrusion is connected to one end of catheter 242 and provides fluid communication between the interior of sensing chamber 44 and the catheter.

Details of the structure housing the urine output monitoring device will now be described with reference to FIGS. 23 and 21It.

This structure is similar to the housing of the feed rate controller and therefore similar elements are designated with the same reference numerals. Housing 300 is generally divided into two parts. Second
Viewed in the orientation of FIG. 3, the right side portion 302 of the housing provides the general area for receiving the droplet volume sensing chamber 244. The left side portion 304 of the housing defines a portion that receives electronic equipment associated with the operation of the urine monitoring device and includes a keyboard 21.
4 and a control spring/L with display device 250.

The door 306 is hinged and swings freely back and forth so that in its open position it exposes the cavity 308 in which the droplet volume sensing chamber 244 is mounted.

In its closed position, door 306 covers cavity 30B and secures droplet volume chamber 244 within cavity 308.

Cavity 308 is configured to receive droplet volume chamber 44 in one direction. This is accomplished by providing keys 310 and 312 at the top of droplet volume chamber 44.

These keys fit into keyways 314 and 316 provided in side walls 318 and 320 of cavity 308, respectively.

These keyways are configured to receive sensing chambers 244 according to both embodiments, as shown in FIGS. Channels 322 and 32 are located at the top and bottom of chamber 308.
4 is provided so that a catheter 242 can be inserted. The rear surface (not shown) of the main body 300 includes a conventional clamping device for securing the urine monitoring device housing to the bed of the entire patient.

In use, sensing chamber 44 is positioned within the urine volume monitoring device in the orientation shown in FIG. 2'1. As seen in FIG. 23, for another embodiment, the housing and chambers 244 therein have several longitudinal axes approximately 30° to the vertical axis V.
It is tilted at an angle of . The reason for this is that when the urine volume monitoring device is attached to the patient's bed, the urinary catheter and chamber 244 must be located at a lower position than the patient. Move the housing 30 degrees from the perpendicular line.
The angle of tilt makes it easier for nurses to check the operation of the urine collection system.

Infrared #
An LED (light emitting diode) 80 transmits a light beam through a slit 82. The light beam passes through the lens 11 and enters the lens 13, where it is received by the phototransistor 84. Second
2 figures and! , 24, these lenses are arranged to form a series of parallel rays 86 within the chamber cavity 245.

Having described the details of the sensing chamber above, details of other elements of the urine output monitoring device will now be described.

The center of the urine volume monitoring device 210 is the microcontroller 21
It is 2. In the preferred embodiment, the microcontroller is the same as that used in the feed rate controller. A keyboard 214 is provided for user interfacing with the microcontroller. The six keys of the keyboard are connected in a conventional manner by lines 281 to six bidirectional I10 (input/output) ports provided on the microcontroller. The keyboard can give several commands to the microcontroller, such as start, start, and display various items. Additionally, a test key is provided for testing and calibration during manufacturing.

A frequency of approximately 209 MHz is provided by the clock source to operate the system oscillator of microcontroller 212.

Memory 286 forms part of the urine monitoring device.
It is. This memory, in the preferred embodiment, is of the same type as that used in the feed rate controller. This memory is enabled by signals received on line 88 from the microcontroller.

Five bidirectional ROM address and data ports are provided in the microcontroller and these are connected to line 90.
The multi-address information received through the transfer is transferred. Address information is passed through g-bit latch 92 and sent to EFROM via line 94. Meanwhile, data is received from the EFROM via line 96 which joins line 90. Microcontroller is yet another ROM
These include address outputs, which provide address information to the memory via line 98.

A door sensor 100, consisting of a light emitting diode that illuminates a phototransistor, is generally located in the lower left corner of the receiving cavity 308. Door Senna 100 is line 10
2t- is used to send signals to the microcontroller's general purpose power 104. The height signal appearing on line 102 indicates that the urine output monitor door is closed.

When the door is open, a signal is sent from the microcontroller via output line 400 to LED display 402 indicating that the door is open.

Also forming part of the electrical equipment for the urine output monitoring device is voltage regulator 118, which is a three terminal regulator in the S volt range, National Sem.
LM by 1couductor company? gLθ5A
It is called CZ.

This voltage v4! The output port and common port of the jf device are connected to capacitor CIC, while the common port and input port are connected to capacitor C3 and ground. Voltage regulator 118 is used to provide a regulated supply voltage, S volts in the preferred embodiment shown. This regulated voltage input is connected to the center pole 114 of the on/off switch 116. Also connected to this center pole 114 is a green LED 420 that is turned on when the monitoring device is operating.

In the microcontroller 212, the bidirectional 11
02 port 160 and general-purpose output 162 are general-purpose output 142
and is connected to an LCD driver 251 which in turn generates an appropriate signal on line 166 to activate the LCD display 250.

A further component block of the urine output monitoring device is the floating trigger 410, which is similar to that already described for the delivery control device. For this reason, similar elements are designated with the same reference numerals.

As with the delivery control device, the idea behind the floating trigger in this urine monitoring device is to
The purpose is to provide a signal representative of droplet size or droplet spacing regardless of changes in the VCE of phototransistor 84. This is done in the urine volume monitoring device in the same way as already described for the supply rate control device.

The output of phototransistor 84 of droplet diameter detector 16 is:
It is sent to the negative input of operational amplifier 202 via resistor R6 and capacitor C6. A bias voltage of approximately 120 volts is supplied to the positive input of operational amplifier 200 through resistor P, 23. The output of the operational amplifier 200 is approximately θ port, and is applied as a bias voltage to the parallel connection of the capacitor CIO and the resistor R/l.
It is also given to the positive input of 4. The resulting DC voltage is divided between resistors P10 and R/'4 and appears at the positive input of operational amplifier 202. Information including droplet spacing from droplet sensor 16 is transferred to operational amplifier 202 via resistor R6 and capacitor C6 until such time as the trigger voltage level is set via resistor R20. It is connected to AC. The above trigger voltage sent to the negative input of operational amplifier 206 floats so that the pickoff point on the AC signal moves up and down in the opposite direction to compensate for changes in the VC of phototransistor 84. In this way, the droplet spacing is insensitive to electronic drift in general and 'V CE drift in particular.

Having described the elements that make up the urine volume monitoring device in detail above, we will now discuss how to accurately measure the amount of urine flowing through the system in a preferred embodiment of the urine volume monitoring device. Referring to Figures 1g, 22 and 29,
Light source 80 generates a light beam 81 that passes through slit 82 and through the lens of droplet sensing chamber 244 . Lenses T1 and 73 are configured to generate parallel light rays 86 within the housing. The light beam from the LED is received by a phototransistor 84 after passing through a lens and a slit. The output of this phototransistor, in combination with a floating trigger, provides an input signal to the microcontroller. Thus, light source 80 and phototransistor 84 together with slit 82 define a beam plane through which the urine temperature passes. When the droplet crosses the ray plane,
The output of the phototransistor appears as an analog signal that rises when the droplet enters the collimated beam. The output of the phototransistor remains constant while the droplet is contained within the collimated beam, but gradually decreases as the droplet exits the collimated beam. This signal is sent to floating trigger 410,
This trigger 410 generates a square wave whose duration (in milliseconds) is proportional to the diameter of the urine temperature. In particular, the output of the floating trigger will be at a high level in the absence of urine temperature and at a low level when the droplet passes through the boundary defined by the parallel light beam.

Referring to FIG. 2a, t/ represents the time required for the urine temperature to reach the distance from the orifice O. time t
2 represents the time required for the urine temperature to travel a distance equal to its diameter d. The calculation of droplet volume is therefore the same as described for the feed rate controller.

The square wave signal generated at the output of the floating trigger, approximately 20 microseconds in duration, is sent to the microcontroller. The microcontroller can solve the equation for a volume equal to T.

The precise operation of the preferred embodiment will now be described with reference to FIGS. 19, 23, and 2j.

The urine collection system is first set up by inserting one end of the catheter 242 into the patient and securing the other end to the top of the sensing chamber 244. Next, the sensing chamber 24
The other end of tube 24 leads to urine collection bag 247.
Fixed at 6.

The control keys of the urine volume monitoring device are as follows. The Current 7 Hour Flow Key (PR) invokes a urine flow display that is updated instantaneously every 70 minutes. Another key (VC) brings up the display of the total cumulative volume during the time that urine is flowing into the sensing chamber. The key labeled (LR) corresponds to the current 7-hour collection flow rate. This happens at the end of the 7 hour cycle.
'θ1 and start accumulating again, while the total cumulative amount (VC) continues to accumulate all for at least 24 hours. Last 7 Hour Volume is the amount of urine collected over the most recent 7 hours of operation of the monitoring device, which is stored in memory 286.

The elapsed time button (ET) allows display in minutes and hours.

Turn switch 116 to the on position. Next, the display device 250 displays "1FFF" as shown in FIG.

Next, the door 30ε of the device is opened. With the door open,
Sensing chamber 244 is placed into receptacle 308. Then,
Catheter 242 is placed within channel 322 above the sensing chamber. Then close the door. Start normal operation with the door closed.

The actual operation of the urine volume monitoring device 21.0 is as follows.

Unless this monitoring device is operated in collection volume mode,
The flow rate at that time is always displayed at 47 o'clock on the display device 250. Under all conditions, the display is updated every 70 minutes. During the first 70 minutes of operation time, there is nothing to update and display, so the LCD display 250 will display "FFF" mt1 o'clock.
When the key labeled VC) is touched, the total collection amount can always be displayed in milliliters (-).

Similarly, when the key labeled (ET) is touched, the elapsed time is displayed. Its display units are hours and minutes.

The key labeled (LR) displays the flow rate for the last 7 hours.
Display at lZ time. The flow rate is updated every 7 hours after the monitor has been activated for 60 minutes. Touched and released the key 5
After seconds the monitor switches to display the current flow rate.

Optionally, three small plastic balls 451-453 are placed within the disposal chamber 244, each ball being filled with a different specific gravity. Room 244
When urine is present, one, two or three balls will float or sink depending on the specific gravity of the urine. The clinically important specific gravity range of urine is 10θ0 to 104tO.

The specific gravity of the three balls /″:) is 70/θ.Second
The third ball has a specific gravity of 1010, and the third ball has a specific gravity of 7030. Therefore, the nurse only has to open the room door, observe the waste sensing chamber 244, and determine which of the three balls is floating or sinking (forced); The specific gravity can be determined. By using three balls, this particular parameter or specific gravity can be easily observed, avoiding the need to dispose of the urine and preventing it from spilling. This is important because if the specific gravity of a patient's urine is, say, 1005, the clinician can decide to administer more salt into the intravenous solution; if the specific gravity is 0. , the clinician can decide to give the patient water that is less salty; therefore, the specific gravity measurement provides an indication of the patient's dilution status.

The urine output monitoring device is also combined with a series of sensors and associated alarms 258. These are the door open sensor 402 and the low voltage sensor 254. There are also a bag full LED, D display device 461, a low flow LED display device 463, and a no flow LED display device 465.

When the urine output monitoring device senses one of these alarm conditions, audible alarm 258 and visual alarm 342 are activated;
Display device 250 informs the reason for the alarm. Audible alarm 2
58 can be stopped by touching the alarm off key (AO).

A visual alarm 34 in the form of an LED until the condition is corrected.
2, the red light will continue to flash, and the audible alarm will emit an alarm sound at predetermined intervals.

If the urine output from the patient drops below 30-7 o'clock or if the urinary system is constrained in a way that reduces the urine flow, a low urine flow alarm will be alerted and "LOW FLOW" will flash. . The alarm sound can be turned off. Similarly, if the flow rate is 3 #
+7! / hour is lower than υ, a -no flow alarm is sounded and the LED is turned on. You can also kill this alarm by turning off the sound. Whisper door open〃The alarm is a 9 minute alarm (
It is audible and has a red LED.)
. This alarm sound can be turned off, but if the whisper door open condition is not corrected, the alarm sound will be emitted again. When the chamber becomes full, an audible and visual alarm is activated. 1 Battery low voltage alarms are also audible and visual alarms.

From the foregoing description, it will be apparent that many modifications and variations may be made in light of the above technique without departing from the scope of the invention. It is therefore to be understood that, within the scope of the appended claims, the invention may be practiced otherwise than as described above.

[Brief explanation of the drawing]

FIG. 1 is a block diagram showing the main elements of an embodiment of a supply rate control device using the technology of the present invention, and FIG. 2 is a schematic diagram of a supply rate control device used in a gravity-type intravenous administration device. Figure 2a is a schematic diagram used to explain the calculation of droplet volume as the droplet passes through the droplet sensing chamber, and Figure 3 is used to explain how the presence of a droplet in the sensing chamber is detected. Schematic diagrams, FIG. 9 shows a sensing chamber employing the technique of the invention in perspective with its cover removed; FIG. Perspective view, Figure 6a is a front view of the instrument shown in Figure S with the door closed, Figure 6b is a front view of the sensing chamber receiver with the sensing chamber attached, Figure 7 is the supply 3 is a longitudinal sectional view of the sensing chamber of FIG. 3 with the cover in place; FIG. FIGS. 10 to 76 are diagrams illustrating various stages of the visual display device at various times during operation of the feed rate control device; FIG. 77 is a cross-sectional view taken along line 9; FIG. A block diagram showing the main elements of an embodiment of the urine volume monitoring device, FIG. 1g is a circuit diagram showing parts of an electronic circuit combined with the urine volume monitoring device, and FIG. 19 is a urine volume monitoring device used in a urine collection system. FIG. 20 is a perspective view of another sensing chamber according to the present invention used in a urine volume monitoring device with its cover removed, and FIG. 21 is schematically shown in FIG. 19. FIG. 22 is a longitudinal sectional view of the sensing chamber taken along the line 22-22 of FIG. 27, and FIG.
The figure is a perspective view of the front of the instrument forming part 7 of the urine volume monitoring device, and the second figure is a front view of the sensing chamber receptacle of the urine volume monitor with the sensing chamber attached. DESCRIPTION OF SYMBOLS 10... Feed rate control device 12... Microcontroller 14... Keyboard control panel 16... Droplet diameter detector 22... Motor drive device 24... Step motor 30... Bag or bottle 32... Dosing device 36... Roller clamp 38... Injection site 42... Flexible tube 44... Droplet volume detection chamber 46... PVC tube 48... Needle 50... LCD 51...LCD drive device 52...Air detector 54...Battery low voltage detector 56...Door open detector 58...Alarms 61-64...Wall 71.73.75 .77 Lens 68 Hole 70 Protrusion 72 Cover plate or cap 74 Hole 76 Hollow protrusion 300 Housing 306 Door 308
・Cavity 361...Engraving of the splash wall drawing (
No change in content) F/6 / FI6.3 302 F/θ, 6b FI6.24 Commissioner of the Patent Office Kazuo Wakasugi Display of Y 1982 Patent Application No. 243o 2Oq
Name of 夛1明 Flow rate monitoring device with optical sensing chamber-1
Relationship with ``The person who does the right thing''Distributor's name Name: Ari I Love Incorporated F℃ Rito

Claims (9)

[Claims] (1) A flow rate monitoring device for measuring a precise amount of fluid, which includes a sensing chamber including a hollow nozzle defining a cavity, and a beam of light directed into said cavity as a beam plane defined by a series of parallel beams. orifice means for introducing fluid into the cavity in a series of droplets, the orifice means being oriented such that the droplets pass through the ray plane under gravity. A flow rate monitoring device characterized by: (2) said lens means extends from a pair of opposing walls of said housing, these walls defining a portion of said nine sides;
The walls are formed by a pair of opposing rays selected to cause the rays passing through them to be configured as a series of parallel rays defining the ray plane perpendicular to the path defined by the passing droplet. Claim No. 1 in the form of a lens
Flow rate monitoring device described in section ). (3) means for forming a beam of light, means for directing said beam of light onto said lens means, receiving said beam after it has passed through said lens means, and an intensity of said beam after passing through said lens means; and means for generating a signal proportional to
1) The flow rate monitoring device described in item 1). (4) Means for receiving and/or taking said signal; and means for evaluating said signal to determine the exact amount of the droplet as it passes through said beam plane. Flow rate monitoring device described in section. (5) a sensing means for sensing the passage of a droplet of fluid through said chamber; a measuring means for measuring the volume of the droplet sensed by said sensing means; means for determining whether the volume is within a predetermined droplet volume range; and a flexible tube having one end in fluid communication with the chamber and the other end connected in fluid communication with a source of fluid. , an actuator for varying the cross-sectional size of the hollow interior of the flexible tube in response to a control signal such that the size of the droplet formed by the droplet forming means is proportional to the cross-sectional size of the flexible tube; means for generating the control signal and varying the time interval between droplets when the measured droplet volume is within the predetermined range while the system is dispensing 1v solution; and and control means for actuating said actuator means to change the droplet volume when the measured droplet volume is not within said predetermined range. flow rate monitoring device. (6) means for generating a droplet volume signal representative of the volume of a droplet passing through the beam plane; The flow rate monitoring device according to claim 1, further comprising compensation means. (7) light sensing means within said housing for sensing the passage of a droplet of 1V solution through said chamber and disrupting the flow of droplets through said chamber when ambient light enters said nozzling; The flow rate monitoring device according to claim 1, further comprising means. (8) A flexible tube having a variable cross-sectional area, one end of which is in fluid communication with the sensing chamber, and the other end of which is connected in fluid communication with a source of fluid. Flow rate monitoring device according to scope item (3). (9) further comprising: anvil means in contact with the outside of the tube; and movable plunger means disposed opposite the anvil means such that the tube is inserted therebetween, the grunger being adapted to cut the tube. The flow rate monitoring device according to claim 1 (8), which operates to move closer to or further away from the anvil so as to change its area. al A flow monitoring device according to claim 9, further comprising step motor means for moving said plunger in a desired direction in predetermined increments. αη means for receiving and receiving said signal; means for evaluating said signal to determine the precise volume of the droplet as it passes through said parallel beam array; and a control for varying the cross-sectional area of said tube in response to said signal. The flow rate monitoring device according to claim 8, further comprising means. (b) The gravity-type intravenous administration system according to claim Ql), wherein the control means changes the interval between droplets. (to) The control means, while changing the volume of the individual droplets,
10. The gravity intravenous delivery system of claim 09, wherein the time interval between droplets is maintained constant. a4 A flow rate monitoring device according to claim (1); 1) sensing means for sensing passage of a droplet of fluid in the form of a solution into said chamber; one end in fluid communication with said chamber; a flexible tube with the other end connected in fluid communication with a source of 1V solution; actuator means for constricting or opening the hollow interior of the flexible tube in response to a control signal; an intravenous administration system characterized in that it comprises control means for generating said control signal and actuating said actuator means such that said hollow interior never constricts into light while the system administers a 1v solution; . 042. The system of claim 041, wherein the system is in fluid communication with the droplet chamber and includes means for injecting the 1v solution into the user's body. (to) further comprising detection means for detecting an abnormality in the flow of the 1V solution through said system and generating a signal indicative of said abnormality, said control means responsive to said signal generated by said detection means said The system of claim a0, wherein the flexible tube is constricted by an actuator. 07) The system according to claim 06, wherein the abnormality is air within the system. 0 keg Prior to the passage of a droplet into the sensing chamber, a first control signal generated by the control means causes the actuator means to completely constrict the flexible tube. The device described. A third control signal generated by the control means causes the actuator means to release the constriction of the flexible tube by a predetermined amount until a droplet is detected by the sensing means. Apparatus according to paragraph 1E9. Further control signals are provided for causing said actuator means to constrict or open the hollow interior of said flexible tube to form droplets of various sizes within said chamber. The device according to claim C1, which is generated by the control means. Apparatus as claimed in claim 01, wherein further control signals are generated by said control means to form droplets within the chamber. □Go to +