KR100914569B1 - Compression treatment system - Google Patents

Abstract

A compression treatment system (10) is provided that includes a first bladder (46a, 46b, 46c, 48a, 48b, 48c) supported about a limb. A second bladder is supported about the limb. The bladders are in fluid communication with a fluid source (50) and the bladders are inflated such that the first bladder is inflated for a first time period and the second bladder is inflated for a second time period. The second time period is initiated within the first time period. A single pressure sensor communicates with the first bladder and the second bladder.

Description

Compression Processing System {COMPRESSION TREATMENT SYSTEM}

FIELD OF THE INVENTION The present invention generally relates to the field of vascular therapy for application around the limbs of the body, and more particularly to a compression processing system having a controller for regulating fluid flow.

A major concern for people such as immobile patients is medical conditions that form clumps of blood, such as deep vein thrombosis (DVT) and peripheral edema. Such patients and persons include those who have experienced long periods of rest in surgery, anesthesia, and bed. Such blood coagulation conditions generally occur in the deep veins of the lower body and / or pelvis. Veins such as the iliac, femoral, popiteal and tibia return oxygenated blood to the heart. For example, when blood circulation in such veins is slowed down due to illness, injury or lethargy, blood tends to accumulate or accumulate. Static pools of blood are ideal for forming clumps of blood. The main risk associated with this condition is that it interferes with cardiovascular circulation. Most seriously, blood clots loosely break and travel from place to place. Pulmonary emboli can be formed to block major pulmonary arteries that can be life threatening.

Conditions and the resulting risks associated with a patient's inability to move can be controlled or mitigated by applying intermittent pressure to the limbs of the patient, such as the legs, including the thighs, caps, and feet, thereby aiding blood circulation. Known devices have been used to aid blood circulation, such as single piece pads and compression maneuvers. See, for example, US Pat. Nos. 6,290,662 and 6,494,852.

For example, a sequential compression device has been used that consists of an air pump connected to a pad around a disposable waist by a series air tube. The waist pad is configured to be positioned around a portion of the patient's leg, such as a thigh, a calf or a foot. Multiple pads may be mounted to the legs to cover the various portions of the legs. Air is then sequentially pushed into other parts of the waist pad, creating pressure around the thighs, caps or legs, thus improving venous regression.

Such known devices may suffer from various disadvantages due to their volume and inconvenient properties. These drawbacks reduce comfort and flexibility and can adversely hinder the patient's mobility as the postoperative recovery progresses.

Such known sequential compression devices also generally include assemblies that regulate air flow and pressure in the waist pad. The controller assembly can be mounted to a bed and plugged into a wall outlet for power during use. However, such an arrangement may reveal difficulties when the patient needs to perform some task, for example when needing to do a bath, physical therapy, and the like. In this situation the pads are typically removed, thus adversely stopping vascular treatment. Accordingly, this controller assembly suffers from a variety of disadvantages because the controller assemblies are not generally applicable to inflation of the thighs, caps and foot pads without simplifying patient movement or mobility.

It is therefore possible to overcome the disadvantages and disadvantages of the prior art using a compression treatment system that is applicable to inflating thighs, caps and foot sleeves and has a controller that provides continuous vascular treatment by simplifying patient movement and mobility. Would be preferred. It would be highly desirable if the system automatically detected the types of sleeves connected to it. It would be highly desirable if the system included an air pressure circuit that facilitates blood pressure monitoring with a single pressure sensor to achieve the advantages of the present invention. Compression processing systems are believed to be easily and efficiently manufactured.

1 is a front view of one detailed embodiment of a compression processing system in accordance with the principles of the present invention.

2 is a side view of the compression processing system shown in FIG.

3 is a plan view of the compression processing system shown in FIG.

4 is a rear view of the compression processing system shown in FIG.

5 is a schematic diagram of an air pressure circuit of the compression processing system shown in FIG.

6 is a plan view of the sleeve of the depicted compression processing system of FIG. 1 disposed around the limbs.

FIG. 7 is an alternative embodiment of the sleeve shown in FIG.

FIG. 8 is another alternative embodiment of the sleeve shown in FIG.

Accordingly, to overcome the disadvantages and disadvantages of the prior art, there is provided a compression treatment system that is applicable to inflating thighs, caps and foot sleeves and provides continuous vascular treatment by simplifying patient movement and mobility. Preferably the system automatically detects the type of sleeve connected thereto. Most preferably the system includes an air pressure circuit that facilitates blood pressure monitoring using a single pressure sensor to achieve the advantages of the present invention. The compression processing system is easily and efficiently manufactured.

In accordance with the principles of the present invention, a compression processing system may provide intermittent air compression for the prevention of DVT. The compression processing system may also include venous refill detection, as discussed, and may provide small, quiet, lightweight and battery power. The compression processing system also has the ability to provide each compression limb with a sequential compression gradient individually, and the flexibility to provide compression to various sleeves including, for example, three bladders. The sleeve may comprise a knee length sleeve and a thigh length stripped configuration as discussed. In addition, the compression treatment system can provide higher pressure and slow compression to the foot sleeve. The compression treatment system provides continuous DVT prevention without stopping as the system is used throughout the treatment instrument, and the patient can wear and continue to use the treatment system for the entire risk period.

The compression processing system may be portable to provide continuous treatment while the patient is at risk with DVT. This configuration facilitates continuous vascular treatment during the activity and work of the patient, such as, for example, testing, bathing, physical therapy, and the like. Thus, the compression processing system will be comfortable, compact and lightweight enough to prevent interruptions during treatment by providing a battery operated controller when not plugged in, and to move with the patient whenever needed.

The compression processing system includes a controller, a pipe set, and a sleeve. For example, the compression treatment system delivers air to each limb through a set of piping to a pair of sleeves. The sleeve may have three bladders, the bladder corresponding to the ankle, the cap and the thigh, respectively. The compression processing system independently compresses one of the limbs, left or right. When the two limbs are connected, swelling occurs alternately between the two limbs. As an alternative, only one sleeve may be connected.

Alternatively, the compression processing system is used as a slow compression foot device. In this configuration the compression treatment system includes a pair of single patient, single bladder disposable foot garments instead of a sleeve. Single foot garments may also be used. The compression treatment system also provides for use of the foot garment on the first limb and the sleeve on the second limb.

The compression processing system includes a tubing set connector port that locks together in a mating configuration on the tubing set. When the compression processing system is initially powered up, air remains until the system knows which ports are connected to the sleeve and which type of sleeves (eg, leg sleeves or foot garments) are connected to such ports, Passed through the port. Compression therapy is delivered to a port that connects with a suitable sleeve.

For example, the compression treatment system provides clinical parameters for vascular treatment, such as a second swelling cycle of 11 seconds, followed by aeration cycle of 20 seconds to 60 seconds depending on the venous refill measurement. The second compression time of 11 seconds is sequential. At 0 seconds the first bladder begins to inflate. The second bladder begins to inflate at 2.67 seconds and the third bladder begins to inflate at 5.67 seconds. After 11 seconds, all three bladders are vented. The pressure during the inflation period must be maintained such that the first bladder is larger than the second bladder and the second bladder is larger than the third bladder. For example, the end of the periodic pressure may be 45 mmHg in the first bladder, 40 mmHg in the second bladder, and 30 mmHg in the third bladder. Compression continues in this periodic pattern until the compression processing system is turned off or the controller issues a warning.

As another non-limiting example, the foot compression parameter may include an inflation period of five seconds prior to the same aeration period period as provided above during sleeve compression (20-60 seconds). The end of the cycle pressure on the foot sleeve will have a set pressure target of 130 mmHg until the end of the 5 second inflation cycle.

Intravenous refill detection can be used as a compression treatment system. Vein refill detection involves trapping some air in the described second bladder and monitoring the pressure rise as the vein in the limb of the patient is refilled with blood. As the compression treatment system reaches the set pressure, every 30 minutes thereafter the controller measures venous refill and adjusts the aeration time between swelling cycles for individual limbs from 20 to 60 seconds. Measuring venous refill for longer periods from the extremities will be used to control aeration time.

The compression processing system benefits from several advantages including a compact, lightweight, battery driven controller for portability. The compression processing system may also be used with one or two limbs and provide slow compression to the foot garment. The compression processing system can also detect the type of sleeve connected and automatically apply the appropriate compression.

The compression processing system also includes a pneumatic circuit designed for use with the compression processing system to enable bladder inflation and pressure monitoring using only one sensor. Pressure monitoring from the solenoid valve manifold side contributes to the pressure drop between the valves with the added advantage of requiring only one sensor to monitor the connected bladder. This configuration makes it possible to manufacture at lower manufacturing costs and advantageously alleviates the maintenance requirements, particularly with respect to sensor calibration.

In one embodiment, according to the principles of the present invention, the compression processing system includes a first bladder supported around a limb. The second bladder is also supported around the limb. The bladders are in fluid communication with a fluid source, the bladders are inflated such that the first bladder is inflated for a first time period and the second bladder is inflated for a second period. The second period begins within a first time period. The single pressure sensor is in communication with the first bladder and the second bladder. The pressure sensor is configured to monitor the pressure of each bladder.

The compression processing system may include a controller in communication with a pressurized fluid source and a pressure sensor. The controller is configured to monitor and regulate the pressure in the bladder. The controller can be disposed with a housing that is portable. The housing may include a plurality of ports connectable to the plurality of bladders.

The pressure sensor determines whether the bladder is connected to the port by monitoring the pressure of each of the plurality of ports and sends a signal to the controller indicating whether the bladder is connected to the port. The controller may include a separate valve to control the inflation of the bladder. The compression processing system may define an air pressure circuit. The pressure sensor can be coupled to a pneumatic circuit and can be disposed between the pressurized fluid source and the valve in the pneumatic circuit.

The compression processing system may include a third bladder supported around the foot. The third bladder is in fluid communication with the fluid source and the single pressure sensor is in communication with the bladder. The pressurized fluid source can alternately inflate bladder disposed around the limbs and bladder disposed around the foot.

In an alternate embodiment the compression processing system includes a first plurality of bladders disposed about the first limb. A second plurality of bladder is supported around the second limb, the bladders in fluid communication with the fluid source. The first bladder of the first plurality of bladders is inflated for a first time period and the second bladder of the first plurality of bladders is inflated for a second time period. The second time period is initiated within the first time period.

A first bladder of the second plurality of bladders is inflated for a third time period and a second bladder of the second plurality of bladders is inflated for a fourth time period. The fourth time period begins within the third time period. A single pressure sensor communicates with the bladder. The pressurized fluid source may alternately inflate the bladder disposed around the first limb and the bladder disposed around the second limb.

In another alternative embodiment, the compression processing system includes a first plurality of bladder supported around the first limb and a second plurality of bladder supported around the second limb. Each bladder of the first plurality of bladders and the second plurality of bladders has a separate valve in communication with them. The valve is in fluid communication with a fluid source.

The first valve is opened to inflate a first bladder of the first plurality of bladders for a first time period and the second valve is opened to open a second bladder of the first plurality of bladders during a second period of time. Inflated The second period is initiated within the first time period. The third valve is opened such that the first plurality of third bladders are inflated for a third time period. The third time period is initiated within the second period.

The fourth valve is opened such that the first bladder of the second plurality of bladders is inflated for a fourth time period and the fifth valve is opened so that the second bladder of the second plurality of bladders is fifth Inflate during the cycle. The fifth time period begins within the fourth time period. The sixth valve is opened such that a sixth bladder of the second plurality of bladders is inflated for a sixth time period. The sixth time period is initiated within the fifth time period. A single pressure sensor communicates with the bladder.

The objects and configurations of the invention believed to be novel are described in detail in the appended claims. The present invention can be better understood by referring to the following description in connection with the accompanying drawings, which are described below with respect to the construction and manner of operation together with other objects and advantages.

Exemplary embodiments of the compression treatment system and the disclosed method of operation are suitable for inflating the thighs, caps, ankles and foot sleeves, more particularly in the context of vascular therapy comprising a prophylactic compression device for application to the body limbs. Discussion is made in terms of a compression processing system having a controller that simplifies patient movement and mobility. It is contemplated that compression processing systems can be used to prevent and overcome the risks associated with a patient's inability to move. It is also contemplated that compression processing systems alleviate conditions arising from stationary movement of the patient, for example to prevent DVT, peripheral edema and the like. It is contemplated that compression processing systems according to the present invention may contribute to any type of venous compression system, including but not limited to preventive sequential compression devices. The term "prophylaxis sequential" is not to be construed as limited to the general venous compression treatment system described herein. However, the present invention, for example, with various conditions in which people and patients are immobile, such as those who have undergone surgery, anesthesia, resting in bed for long periods of time, obesity, old age, malignancy, previous thromboembolism, and the like. I would like to find something that applies.

In the following discussion the term "proximal" refers to a portion of the structure that is closer to the subject's body and the term "distal" refers to a portion farther from the body. As used herein, the term "subject" refers to a patient experiencing vascular treatment using a compression treatment system. According to the present invention, the term "practitioner" refers to an individual who manages a compression processing system that may include supporting an individual.

The following description includes a description of the compression processing system, followed by an example method description for operating the compression processing system in accordance with the principles of the present invention. DETAILED DESCRIPTION Exemplary embodiments and disclosures described in conjunction with the accompanying drawings will be mentioned in detail.

Referring now to the drawings, like parts are designated by like reference numerals throughout the several views. 1 through 5, a compression processing system 10 constructed in accordance with the principles of the present invention is described. The compression processing system 10 includes a housing 12. The housing 12 encloses portions of the controller 14 disposed therein. (Shown schematically in FIG. 5)

The housing 12 has a semicircular configuration and has handle cuts 16 along its vertices 18 to facilitate movement and object mobility. The housing 12 is intended to be variously constructed and dimensioned, such as, for example, rectangular, spherical, or the like. In addition, the housing 12 is intended to be assembled by any suitable process such as, for example, snap matching, adhesives, soluble weldments, thermal welds, ultrasonic welds, screws, rivets, and the like. Alternatively, the housing 12 may be integrally formed or integrally assembled into multiple housing parts, substantially transparent or opaque, and the like. Housing 12 may include ribs, ridges, and the like to facilitate manipulation of compression processing system 10.

Portions of the housing 12 may be made from materials suitable for medical applications, such as metals such as polymers or stainless steel, depending on the particular medical application and / or clinician's preference. Semi-rigid and rigid polymers as well as elastic materials, such as molded medical polypropylene, are contemplated in the manufacture. However, those skilled in the art will also recognize that other materials and methods of manufacture suitable for assembly and manufacture in accordance with the present invention will also be appropriate.

The housing 12 is portable to facilitate continued vascular treatment for the subject. The housing 12 includes a housing 12 and a bracket 20 that facilitates removable mounting of, for example, hospital beds, tables, and the like. The bracket 20 extends from the rear portion 22 of the housing 12 and provides a hook configuration for hanging the housing 12 from the object bed or the like. It is contemplated that the bracket 20 may be hung from various configurations for removable mounting of the housing 12, or alternatively that the housing 12 does not include a bracket and may be located on a floor or other support surface. I think.

Alternatively, the housing 12 includes a shoulder strap 24 as shown in FIG. 2 that allows the subject or the practitioner to wear the housing 12 during movement. Shoulder strap 24 may be used with or without bracket 20 and may be secured to any portion of housing 12 including handle 16, for example.

The compression processing system 10 uses an electrical alternating current / direct current power supply for the operation of those parts. The power cord 26 is connected to the housing 12 to conduct power to the portions of the controller 14. The power cord 26 accesses an AC power supply via an electrical outlet and the like. Controller 14 may include a transformer or other electronic device for connecting to the power supply. The power cord 26 is intended to be wrapped around the bracket 20 for storage and for movement and object mobility. It is also intended that the compression processing system 10 can include a storage capture mechanism that holds the power cord 26 with the housing 12. Storage capture mechanisms may include rubber bands, pulleys, and the like.

The compression processing system 10 also uses a battery 28 to power portions of the controller 14 to facilitate movement and object mobility. The battery 28 is disposed in the battery compartment 30 of the housing 12. It is contemplated that battery 28 may include one or a plurality of cells. The battery cell may be lithium-ion type or the like. It is contemplated that battery 28 is rechargeable and can be used for a variety of operating times, such as, for example, 6 hours, 8 hours, 10 hours, and the like. For example, the power cord 26 can be pulled out and captured by the storage capture mechanism of the housing 12. The compression processing system 10 then operates on battery 28 power and the subject is walking.

The battery 28 is intended to be mounted on or detached from an outer surface of the housing 12. Compression processing system 10 is also intended to include alternative power sources such as, for example, solar, non-electrical power, and the like, or may not include battery power as an alternative means. The housing 12 has a control panel 32 disposed on its front face 34. Control panel 32 includes controls and indicators for operation of compression processing system 10. The control panel 32 provides LED indications that provide status indications, messages and the like of various parts of the system 10 such as, for example, power, battery, sleeve identification and connection, inflation, aeration, venous recharge, errors and the like. Apparatus 36 is provided. Control panel 32 also includes a switch that is manually activated to drive system 10 and the like. Such switches are thought to be membrane type driven by acupressure and the like.

The rear portion 22 of the housing 12 defines ports 38 and 40 (FIG. 4). The ports 38 and 40 respectively represent output ports 38a, 38b and 38c and output ports 40a and 40b, respectively. 40c). The output ports 38a, 38b, 38c and the output ports 40a, 40b, 40c are respectively the inflatable chambers 46a, 46b, 46c of the compression sleeve 46 and the inflatable chambers 48a, of the compression sleeve 48, respectively. And in fluid communication with 48b and 48c, the respective chambers are configured to mate around the subject's legs via coupling connector 42 and tubing set 44 as discussed. Output ports 38a, 38b, 38c, 40a, 40b, 40c are configured for connection to piping set 44. Each port 38, 40 is connectable to a particular compression sleeve, such as a leg sleeve, a foot sleeve and the like.

Ports 38 and 40 are also connected to portions of controller 14 disposed within housing 12 to simplify inflation of the selected compression sleeve as described in the pneumatic circuit shown in FIG. The controller 14 includes a pressurized fluid source, such as a pump 50 in fluid communication with the valve manifold 52, for connection with the ports 38, 40, as discussed. The pump 50 includes a motor that compresses air to the valve manifold 52 via piping or the like. The speed of the pump motor is electrically controlled to provide a compressor speed corresponding to each respective output pressure. It is contemplated that a power supply board comprising the necessary electronics, circuit elements, software and the like known to those skilled in the art will be connected to the pump motor and other parts of the controller 14 to regulate the power thereto. The pump 50 is intended to be a diaphragm pump.

The controller 14 also includes a check valve 54 that prevents air back-leak through the pump 50 when monitoring bladder pressure while detecting venous refill as discussed. The pressure relief valve 56 is arranged with an air pressure circuit to cope with excessive pressure in the compression sleeve. The pressure safety valve 56 is configured to flow excess air pressure if necessary. For example, it is contemplated that various types of valves may be used, such as spring loaded plunger valves.

The valve manifold 52 includes solenoid valves 58a, 58b, 58c, 60a, 60b, 60c, each solenoid valve being coupled to output ports 38a, 38b, 38c, 40a, 40b, 40c. Solenoid valves 58a, 58b, 58c, 60a, 60b, 60c each have an associated solenoid electrically driven via the control processor of controller 14. The solenoid is coupled to the valve seat of each particular solenoid valve 58a, 58b, 58c, 60a, 60b, 60c so that the seat operates to open and close each solenoid valve when driving the solenoid. See, for example, the solenoid valve described in US Pat. No. 5,876,359 to Bock et al. The control processor of the controller 14 includes necessary electronics, circuit elements, software, and the like, which are known to those skilled in the art, to condition changes in the compression processing system 10 and portions of the controller 14. It is believed that the solenoid valves 58a, 58b, 58c, 60a, 60b, 60c are operated in accordance with other indications and measurements sensed by them. One or a plurality of solenoid valves may be used or alternative types of valves may be used.

Solenoid valves 58a, 58b, 58c, 60a, 60b, 60c and their associated valve portions are mounted to ports 38, 40 on the interior of housing 12. Solenoid valves 58a, 58b, 58c, 60a, 60b, 60c are two-position and three-way normally closed valves, each of which has holes 62a, 62b, 62c, 64a, 64b, 64c. In the open position, air flows through the apertures 62a, 62b, 62c, 64a, 64b, 64c to the associated output ports 38a, 38b, 38c, 40a, 40b, 40c and the inflatable chamber of the compression sleeve 46 ( 46a, 46b, 46c and the expandable chambers 48a, 48b, 48c of the compression sleeve 48. In the closed position, the openings 62a, 62b, 62c, 64a, 64b, 64c are blocked and the air from the compression sleeves 46, 48 is removed from the output ports 38a, 38b, 38c, 40a, 40b, 40c and associated valves. The inflatable chambers 46a, 46b, 46c, 48a, 48b, 48c are depressurized by flowing back through the vent ports 66a, 66b, 66c, 68a, 68b, 68c.

The solenoid valves 58a, 58b, 58c, 60a, 60b, 60c are sequentially operated to apply pressure to the inflatable chambers 46a, 46b, 46c, 48a, 48b, 48c and their under the control processor of the controller 14 Provides sequential pressurization and aeration of the chambers. The solenoid valves 58a, 58b, 58c, 60a, 60b, 60c may be selectively driven when a cooling operation of the sleeve is required. (See, eg, US Pat. No. 5,876,359 to Bock et al.)

The solenoid valves 58a, 58b, 58c, 60a, 60b, 60c are driven by signals whose pulse widths are provided by the control processor of the controller 14. The solenoid drive signal is initially at a higher output power level, thereby realizing a faster amount of drive of the solenoid valve. After the initial drive, for example, the drive signal can be reduced to about 70% to maintain valve activation and thus reduce power consumption. Solenoid valves 58a, 58b, 58c, 60a, 60b, 60c are intended to be deactivated as desired. In addition, the control processor of the controller 14 is intended to include the capability to verify the state of the solenoid valves 58a, 58b, 58c, 60a, 60b, 60c. As the state of the solenoid valves 58a, 58b, 58c, 60a, 60b, 60c changes, the control processor verifies the state. For example, if a particular valve is detected to be shorted or open, the compression processing system 10 will enter a specific error mode as discussed.

The controller 14 also includes a pressure sensor 66 disposed within the housing 12. The pressure sensor 66 is coupled to the pneumatic circuit and disposed between the pump 50 and the solenoid valves 58a, 58b, 58c, 60a, 60b, 60c via piping or the like. The pressure sensor 66 is in fluid communication with the inflatable chambers 46a, 46b, 46c, 48a, 48b, 48c to monitor the pressure in each of the inflatable chambers 46a, 46b, 46c, 48a, 48b, 48c. The control processor of the controller 14 causes the pressure sensor 66 to measure any inflatable chambers 46a, 46b, 46c, 48a, 48b, 48c, which chambers are connected to their respective solenoid valves and thus In fluid communication with Placing the pressure sensor 66 on the manifold side of the air pressure circuit, in front of the solenoid valve, facilitates the use of only a single pressure sensor to measure the pressure in the inflatable chamber. This configuration facilitates inflation of one or a plurality of inflatable chambers. This configuration contributes to the compact and lightweight design of the compression processing system 10 by reducing the volume of the controller 14, promotes mobility and patient mobility, and reduces manufacturing costs.

For example, during the selected compression period, solenoid valves 58a, 58b, 58c, 60a, 60b, 60c are sequentially driven to sequentially pressurize inflatable chambers 46a, 46b, 46c, 48a, 48b, 48c. Driven to the open position. In the open position, the solenoid valves 58a, 58b, 58c, 60a, 60b, 60c allow the path of air from the pump 50 to the inflatable chamber through the respective output ports 38a, 38b, 38c 40a, 40b, 40c. To make it possible. The pressure sensor 66 monitors the pressure of each inflatable chamber 46a, 46b, 46c, 48a, 48b, 48c of the air pressure circuit and provides electrical signal input to the control processor of the controller 14 for feedback control. .

At the end of the selected compression cycle the solenoid valves 58a, 58b, 58c, 60a, 60b, 60c simultaneously deactivate to the closed position to disconnect the pump 50 from the sleeves 46 and 48. In the closed position, the pump 50 air is shut off and the solenoid valves 58a, 58b, 58c, 60a, 60b, 60c open the vent ports 66a, 66b, 66c, 68a, 68b, 68c on the valve manifold 52. To vent the sleeve pressure to the atmosphere. It is contemplated that the compression processing system 10 can alternately inflate the chamber between the first limb and the second limb. It is also contemplated that the compression processing system 10 can inflate each bladder individually.

6, a compression processing system 10 similar to that described above is assembled and packaged for use. In operation, the compression processing system 10 includes a controller 14 and a sleeve 112 disposed with the housing 12 described above. Sleeve 112 includes femoral bladder 114, cap bladder 116, and ankle bladder 118. The sleeve 112 includes a connector 120 mating with a mating connector 42, which is connected to the port 38 via a pipe 44. The connector 120 is in fluid communication with the chamber of the sleeve 112 via a tubing set 122. This arrangement thus facilitates fluid communication between bladder 114, 116, 118 and pump 50. It is contemplated that connector 120 may further include a valve mechanism for controlling fluid flow.

Sleeve 112 is provided and manipulated for placement about the subject leg L. FIG. The connector 120 is engaged with the mating connector 42 to form fluid communication between the sleeve 112 and the pneumatic circuit. Sleeve 112 is wrapped around leg L and secured to the leg via hook and loop pads 124, 126. It is contemplated that the compression processing system 10 may differ from the second leg of the subject with a compression sleeve similar to the sleeve 112 via a connection to the port 40. The second leg is treated as an alternating compression period with respect to the compression period described below for handling the leg L, as described in the following alternative means.

The portable configuration of the housing 12 and controller 14 described above provides a compression processing system 10 that facilitates movement and object mobility. This advantageous configuration provides uninterrupted DVT prevention as the system is used throughout the treatment facility and can continue to be worn and used by the subject for the duration of the overall risk. The compression processing system 10 facilitates continued vascular treatment during work and activity of the subject, such as, for example, movement for testing, bathing, physical therapy, and the like. The compression processing system 10 provides a controller 14 to operate with the battery 28 when the power cord 26 is not plugged in, thereby preventing treatment interruptions and also being comfortable enough to move with the subject whenever needed. It will be compact and lightweight.

Manually activated switches of the control panel 32 of the controller 14 cause the compression processing system 10 to be powered on to drive them. The compression processing system 10 is initially powered on and a series of self-diagnosis is performed by the control processor of the controller 14. The LED indicator of the display unit 36 illuminates and audible indications are heard to verify visual and audible indicator operability. The display 36 shines to verify display operability. The controller 14 also verifies the operability of the software of the control processor. If any verification fails, the error code provides a representative audible and / or visual indication.

It is contemplated that an error code will be triggered if the control processor of the controller 14 cannot normally continue the software execution process. This causes the compression processing system 10 to reset and restart normal operation. Sleeve 112 will diverge during the restart procedure. Audible and visual signs can also be met to express the condition.

It is believed that an error code will occur if the control processor of the controller 14 cannot continue normal software execution. This causes the compression processing system 10 to be reset to resume normal operation. Sleeve 112 will be synchronized during the restart process. Audible and visual indications may also be combined to indicate the above conditions.

When the self test sequence compression for the processing system 10 is complete, the controller 14 determines the type of sleeve attached to the ports 38, 40 by initiating a sleeve detection process. Sleeve detection is done during the first inflation (detection) period after controller 14 is initially powered on. During this detection period, air is alternately delivered through ports 38 and 40 using pump 50, which operates for 2 seconds or until the pressure reaches a baseline value. After one second, the pressure sensor 66 makes a pressure measurement to determine whether the bladder is connected to a particular output port 38a, 38b, 38c, 40a, 40b or 40c under sleeve detection.

For example, the detection process is performed for bladder 114, 116, 118 for each sleeve port 38, 40. If there is no back pressure at a particular outlet port for connection with the bladder, then the control processor of controller 14 determines that the bladder is not used at that particular outlet port. The control processor thus adjusts the compression treatment for the detected sleeve configuration. Back pressure is detected at bladder 114, 116, 118 when connected with controller 14 for three bladder sleeves. If no sleeve is detected at each port 38 or 40 or if the detected configuration is not recognized, it is believed that a low pressure error occurs with the corresponding audible indication. It is also contemplated that various timing periods may be used for detection bloat and pressure measurements, depending on the requirements of the particular application.

Alternatively, the femoral bladder 114 is removable from the cap bladder 116. For example, the cap bladder 116 is detachably connected to the femoral bladder 114 through a puncture attachment. (See sleeve described in US patent application Ser. No. 10 / 784,607, filed Feb. 23, 2004, the entire contents of which are incorporated herein by reference.) Controller 14 for removable femoral bladder 114 The control processor of performs a similar sleeve detection process as described above. The control processor will detect the three bladder sleeves due to a valve (not shown) that limits the flow that mates with the connector 120. (See flow restriction valve described in US Patent Application No. 10 / 784,639, "Fluid Piping Connector Device," filed February 23, 2004. The entire contents are described herein by reference.) When absent, the back pressure generated by femoral bladder 114 is monitored. Therefore, the transition from three bladder femoral length sleeves to two bladder knee length sleeves does not have a significant effect on the compression parameters and the controller 14 remains until the femoral bladder 114 remains intact. Continued blood vessel treatment.

In an alternative embodiment, as shown in FIG. 7, the sleeve 112 includes a femoral bladder 114 and an integral second bladder 218. The second bladder 218 has a cap portion 220 and an ankle 222. Pump 50 is sleeved via tubing 226 and 228 separated from valve connector 224 for applications similar to those described above, including selectively removing femoral bladder 114 through perforation, etc. In fluid communication with 112.

In one particular compression period for the compression processing system 10, the compression parameter includes an 11 second inflation period to inflate the bladder 114, 116, 118, and then depressurize the bladder 114, 116, 118. 60 seconds of ventilation to continue. The second inflation period of 11 seconds is sequential.

1) Initially the ankle bladder 118 is inflated during the first time period starting at 0 seconds.

2) Inflation of the cap bladder 116 then and during the first time period begins during the second period, the second time period initiation coinciding with about 2.67 seconds of the first time period duration.

3) Thereafter and during the second period, swelling of the femoral bladder 114 is initiated for a third time period, and the onset of the third time period occurs during a duration of about 3.0 seconds of the second time period and the It occurs at about 5.67 seconds of the first time period.

4) The bladder 114, 116, 118 is vented for at least 20 seconds up to 60 seconds after 11 seconds of the first time period. Examples are described in Table 1 below.

<Table 1>

Start of order Order last Ankle compression 0 sec 2 2/3 seconds Ankle / Cafe Compression Last of ankle compression 5 2/3 seconds Ankle / Cap / Thigh Compression Last of ankle / cap compression 11.0 sec Decompression / ventilation 20 seconds minimum, 60 seconds maximum

The aeration cycle is thought to be measured from the end of one inflation cycle to the start of the next inflation cycle on the leg L. It is also contemplated that both limbs of the subject can be handled and that the compression processing system 10 can alternately treat blood vessels from the leg L to the second leg. The time period from the end of the inflation period to the start of the inflation period for the second leg can be for example 4.5 seconds to 24.5 seconds.

During the initial inflation period to handle the legs L described above, the pump 50 initiates a low base voltage to avoid excessively inflating the bladder 114, 116, 118 in the initial period. The solenoid valves 58a, 58b, 58c are driven as described above such that the valves blow air into the ankle bladder 118 and then the cap bladder 116 and then the sleeve 112 using a predetermined cycle timing sequence. Open to the bladder 114. The pressure sensor 66 monitors the pressure in each of the bladders 114, 116, 118 over an 11 second compression period. At the end of the inflation cycle, the pump 50 stops and the solenoid valves 58a, 58b, 58c move to the closed position to cause the bladder 114, 116, 118 to depressurize through the vent ports 66a, 66b, 66c. Deactivated.

If the second leg of the subject is to be treated for vascular treatment, the solenoid valves 60a, 60b, 60c are driven to an open position as described above, whereby the valve uses air in a predetermined cycle timing sequence. It is disposed around the second leg and is open for delivery to a corresponding bladder of the sleeve similar to the sleeve 112. Pressure sensor 66 monitors the pressure in each corresponding bladder throughout the 11 second compression period. At the end of the inflation cycle, the pump 50 stops and the solenoid valves 60a, 60b, 60c are deactivated to the closed position, causing the corresponding bladder to depressurize through the vent ports 68a, 68b, 68c. It is also intended that the inflation period for the treatment of the second leg can begin about 24.5 seconds after completion of the inflation period for handling the leg L. This process can be repeated for cycles involving both legs. Other cycle times are considered.

In this embodiment, the pressure measured by the pressure sensor 66 during the inflation period and the corresponding signal alternated to the control processor of the controller 14 of the bladder 114, 116, 118 are the pressures of the ankle bladder 118. The gradient is maintained such that the pressure of the cap bladder 116 is greater and the pressure of the cap bladder 116 is greater than the pressure 114 of the femoral bladder. For example, the end of the periodic pressure includes 45 mmHg in the ankle bladder 118, 40 mmHg in the cap bladder 116, and 30 mmHg in the femoral bladder 114. Examples are described in Table 2 below. Compression is thought to continue in this periodic pattern until the compression processing system 10 is turned off or the controller 14 displays an error code via an audible or visible indication. Other cycle pressures are considered.

Table 2

Thigh length sleeve Knee length sleeves Pressure (mmHg) Ankle Bladder (118) Ankle Ankle 45mmHg CAP bladder (116) CAP Lower calf 40mmHg Femoral Bladder (114) Thigh Upper calf 30mmHg

Pressure feedback adjustment may be made in accordance with the pressure measurement by the pressure sensor 66 during the inflation period that follows the initial inflation period for the leg L as described above. At the completion of the initial inflation cycle for the leg L, the end of the periodic pressure in the ankle bladder 118 is measured by the pressure sensor 66 and compared with a set pressure of 45 mmHg by the control processor of the controller 14. do. If the pressure of the ankle bladder 118 is higher or lower than the set pressure, a decrease or increase in the speed of the corresponding pump 50 is necessary to reduce or increase the pressure transfer. The pump speed adjustment is based on the following calculation.

Adjustment = | 45-P | (P is the pressure at the ankle)

If the pressure is less than the set pressure, the pump speed for the next cycle is increased by the adjustment amount. If the pressure is greater than the set pressure, the pump speed for the next cycle is reduced by the adjustment amount. The adjustment process is thought to continue even after reaching the set pressure range. The compression processing system 10 can also adjust for a separate pump speed for each sleeve connected to the controller 14. Other sequential compression periods are also contemplated.

In an alternate embodiment, the compression processing system 10 performs venous refill time measurements. Venous replenishment time (VRT) measurement is an air plethysmographic technique that measures the pulse wave with air to determine when the veins of the extremities are completely refilled with blood after the compression cycle. (See, eg, the venous recharge time measurement described in US Pat. No. 6,231,352 to Watson et al., Which is described herein by reference). The VRT minimizes the time that blood remains stagnant inside the vein. As long as the VRT is between 20 and 60 seconds, the default idle time (60 seconds) can be replaced by the VRT. If the VRT is less than 20 seconds, the default 20 seconds is used. If the VRT is greater than 60 seconds, a maximum of 60 seconds is used. When the system first reaches the set pressure, a VRT measurement is taken and then every 30 minutes. VRT techniques and algorithms are believed to be used for both sleeve and foot compression.

VRT measurement uses a technique to measure pulse waves with air at low pressure applied to the cap bladder. When the vein is full of blood, the pressure in the cap bladder increases until it reaches a flat area. The time for the pressure to reach the flat region is VRT. If two sleeves are connected to the controller 14, the VRT is individually determined for each limb to be compressed and the larger of the two measurements is used as the new aeration time of the compression period. VRT measurements for each sleeve are made when each particular sleeve independently reaches the set pressure. However, the aeration time is not updated until the VRT measurement is calculated for both sleeves.

For example, the compression processing system 10 may use VRT measurements after the system starts vascular treatment. Next, after the 30 minutes have elapsed, the VRT measurement will be made at the next complete inflation cycle. After any of the sleeves described above are inflated, the bladder of the particular sleeve is vented to zero resolution as in the basic inflation period.

It is believed that the bladder pressure selected is monitored and the aeration to the bladder is closed when the pressure drops to 5-7 mmHg. If the bladder pressure in the current period is 5-7 mmHg, VRT measurements are made. If the pressure in the bladder is not vented below 5-7 mmHg, the vent time will remain at the current value and another measurement will be made within 30 minutes. If an error occurs, the corresponding warning provides an audible and / or visual indication.

The VRT measurement algorithm determines when the pressure in the selected bladder flattens after compression. VRT will be determined individually for both legs. The longer of the two recharge times will be used as the new aeration time. If compression is applied to only one leg, the VRT for that leg is used as the new aeration time. The VRT measurement algorithm starts with a time counter starting from the end of the inflation cycle, occurs after the selected bladder reaches 5 to 7 mmHg and is sufficient to keep the bladder in contact with the surface of the leg. Pressure) Aeration is stopped. The VRT measurement is started with a time counter starting from the end of the inflation period.

The pressure in the selected bladder is then monitored. By way of example, the pressure is monitored by moving the sample window for 10 seconds. The window moves at 1 second intervals. The curve reached a flat area when the difference between the first and last value in the window was less than about 0.3 mm Hg. The VRT measurement is considered complete and the time interval is determined. The end of the window is thought to be the time when the venous system in the limb has been recharged.

Irrespective of the VRT measurement, the selected bladder is allowed to vent for at least 15 seconds before the start of the next compression cycle on the same limb. 5 seconds is added to the refill time measured as a safety factor and thus the limbs are not compressed too early. Aeration time is believed to be equal to the measured recharge time plus 5 seconds. For example, the standard deviation in the sample window as a result of the patient's movement may be too large to make the measurement wrong. At this point the calculation is ignored and the previous value of the VRT is used. If at any time during the measurement the pressure in the selected bladder is less than 2 mmHg, the VRT measurement is considered to be an error and the calculation is ignored and the previous VRT value is used. This can happen if there is a leak in the system. If the pressure is greater than 20 mmHg at any time during the VRT measurement, it is believed that the old value of the VRT is used. It is also contemplated that if the VRT calculation is performed on both legs, the VRT performed for a longer time on both legs is used. If the VRT is calculated to be larger than 60 seconds, then 60 seconds will be used. If the VRT is calculated to be less than 20 seconds, a value of 20 seconds is used.

Alternatively, the compression processing system 10 may provide an audible and / or visual indication of system error or failure by using one, multiple or all subsequent error codes. These configurations enhance the safety of the subject during vascular treatment. Various error conditions may cause the compression processing system 10 to provide a warning and to stop certain compression periods. It is contemplated that the compression processing system 10 may cause the user to reset the compression processing system 10 by popping out an error indicator, voice continuous signal, and so forth. The controller 14 may provide an error warning to one, a plurality or all of the following error conditions. A high pressure error comprising such pressures detected as being above a set pressure; A low pressure error comprising such pressures detected below a set pressure if the sleeve is not detected; System pressure error; A system pressure error comprising the pressure determined within the inflation period deviating from a predetermined parameter; Valve error; Software error; Pump error; Aeration and decompression errors; Battery error; Temperature error, which includes sensing the temperature outside of certain environmental conditions.

As shown in FIG. 8, a compression treatment system 10 similar to that described above in alternative embodiments includes a foot sleeve 312 configured to provide vascular treatment to a subject's foot. Foot sleeve 312 includes bladder 314 that is inflated with air to pressurize the foot and then depressurized. (See sleeve described in US Patent Application No. 10 / 784,604 "Compression Apparatus," filed February 23, 2004, the entire contents of which are hereby incorporated by reference.)

Pump 50 is in fluid communication with foot sleeve 312. The sleeve 312 includes a connector 316 that engages with a mating connector 42 that is connected to the port 40 via a pipe 44. The valve connector 316 is in fluid communication with the bladder 314 of the sleeve 312 via piping 318. Therefore, this configuration promotes fluid communication between bladder 314 and pump 50. Foot sleeve 312 wraps around the side of the foot via hook and loop connector flaps 320 across the instep and hook and loop connector ankle straps 322.

When the self test sequence compression for processing system 10 similar to that described above is complete, controller 14 determines the type of sleeve attached to ports 38 and 40 by initiating a sleeve detection process. The back pressure is sensed by the control processor of the controller 14 in response to the bladder 314 connected to the outlet port 40b with respect to the foot sleeve 312. It is contemplated that the compression processing system 10 may process the foot of the second leg of the object with the foot sleeve 312 and also process the leg L in alternating inflation cycles as described above. In certain exemplary compression cycles for the foot sleeve 312, the compression parameter includes an inflation period of five seconds followed by 60 seconds of aeration. Examples are described in Table 3 below.

<Table 3>

Start order Last order Foot compression 0 sec 5 sec Decompression / ventilation 20 seconds minimum 60 seconds maximum

The aeration cycle is thought to be measured from the end of one inflation cycle to the start of the next inflation cycle for the subject's foot. It is also considered that both limbs of the subject are processed and the compression processing system 10 alternately performs blood vessel treatment from the leg L to the second leg. The period of time from the end of the inflation period for the leg L to the start of the inflation period for the second leg is intended to be in the range of 7.5 to 27.6 seconds.

During the initial inflation period to treat the subject's foot as described above, the pump 50 initiates a low base voltage to avoid overblowing bladder 314 in the initial cycle. Solenoid valve 60b is driven to an open position as described above so that the valve is opened to deliver air to bladder 314 using a predetermined cycle timing sequence. Pressure sensor 66 monitors the pressure in bladder 314 over a five second compression period. At the end of the inflation cycle, pump 50 stops and solenoid valve 60b is deactivated to the closed position, causing bladder 314 to depressurize through vent port 68b.

If the subject's second foot is to be treated for vascular treatment, solenoid valve 58b is activated to an open position as described above so that the valves may be evacuated using a predetermined cycle timing sequence similar to foot sleeve 312. It is intended to be open for delivery to a corresponding bladder of a foot sleeve disposed about the other leg. For example, pressure sensor 66 monitors the pressure in the corresponding bladder over a compression period of five seconds. At the end of the inflation cycle, the pump 50 stops and the solenoid valve 58b is deactivated to the closed position, causing the corresponding bladder to depressurize through the vent port 66b. The inflation period for the treatment of the second foot is also intended to be initiated about 27.5 seconds after completion of the inflation period for treating the foot treated by the foot sleeve 312. This process can be repeated for a cycle with respect to both feet or alternatively can be repeated for a cycle with respect to the foot sleeve of the first leg and the leg sleeve of the second leg. It is contemplated that the compression treatment system 10 may provide alternating compression to any combination of sleeve and foot garments, where such a combination is used, for example, a six-second buffer during the additional aeration period to provide all ventilation after the foot inflation cycle. In addition to the cycle, the overall timing is therefore considered consistent with the basic sleeve compression parameters. Other cycle times are considered.

In this embodiment, the target pressure measured by the corresponding signal relayed to the pressure processor 66 and the control processor of the controller 14 of the bladder 314 is for example 130 mm Hg. Compression is thought to continue in this periodic pattern until the compression processing system 10 is turned off or until the controller 14 displays an error code via an audible or visible indication.

Pressure feedback adjustment is made in accordance with the pressure measurement made by the pressure sensor 66 during the inflation period that follows the initial inflation period for the foot sleeve 312 described. The end of the periodic pressure in the bladder 314 when the initial inflation cycle for the foot sleeve 312 is completed is measured by the pressure sensor 66 and the set pressure of 130 mmHg by the control processor of the controller 14. Are compared. If the pressure of the bladder 314 is higher or lower than the set pressure, a corresponding increase or decrease in the speed of the pump 50 is necessary to reduce or increase the pressure transfer. Pump speed regulation is based on the following calculations.

Adjustment = | 30-P | (P is the pressure at the foot)

If the pressure is less than the set pressure, the pump speed for the next cycle is increased by the adjustment amount. If the pressure is greater than the set pressure, the pump speed for the next cycle is reduced by the adjustment amount. The adjustment process is thought to continue even after reaching the set pressure range. It is also contemplated that the compression processing system 10 can adjust for a separate pump speed for each sleeve connected to the controller 14. Other sequential compression periods are also contemplated.

It will be understood that various changes may be made to the embodiments disclosed herein. Therefore, the above description is not to be construed as limiting, but merely illustrative of various embodiments. Those skilled in the art will wish to make other modifications within the scope and spirit of the claims appended hereto.

Claims (30)

A first bladder supported around the limb, A second bladder supported around said limb, A pneumatic control circuit located in a controller separately received from said bladders, The bladders are in fluid communication with a fluid source, the first bladder is inflated for a first time period and the second bladder is inflated for a second time period, and the bladder is inflated, the second time period and additional A time period is initiated within the first time period, The pneumatic control circuit comprises the controller, a single pressure sensor, a single check valve, the fluid source and a plurality of solenoid valves, The single pressure sensor is located between the fluid source and the solenoid valve and in communication with the first bladder and the second bladder, The single check valve is operably connected to the fluid source and located between the fluid source and the solenoid valve, to prevent leakage out of the first bladder, Wherein said single pressure sensor cooperates with a controller to calculate venous refill time at said first bladder by measuring bladder pressure. The compression processing system of claim 1, further comprising the controller in communication with the fluid source and the pressure sensor, the controller configured to monitor and regulate pressure in the bladder. The compression processing system of claim 1, wherein the controller is disposed with a portable housing. 4. The compression processing system as claimed in claim 3, wherein the housing includes a plurality of ports connectable to the plurality of bladders. The method of claim 4, wherein the single pressure sensor monitors the pressure at each of the plurality of ports to determine whether the bladder is connected to the port and to control a signal indicating whether the bladder is connected to the port. Compression processing system to send to. The compression processing system as claimed in claim 2, wherein the controller includes separate valves for adjusting the inflation of the bladders. delete The compression processing system of claim 1, wherein the pressure sensor is configured to monitor the pressure of each bladder. delete A first bladder supported around the limb, A second bladder supported around said limb, A third bladder supported around the leg, A pneumatic control circuit located in a controller separately received from said bladders, The first bladder and the second bladder are in fluid communication with a fluid source, the first bladder is inflated for a first time period and the second bladder is inflated for a second time period. 2 bladder is inflated, the second time period is initiated within the first time period, The third bladder is in fluid communication with the fluid source, The pneumatic control circuit comprises the controller, a single pressure sensor, a single check valve, the fluid source and a plurality of solenoid valves, The single pressure sensor is located between the fluid source and the solenoid valve and in communication with the bladder, The check valve is operably connected to the fluid source and positioned between the fluid source and the solenoid valve, the single check valve prevents leakage to the outside of the bladder to be measured, And the single pressure sensor calculates the venous refill time at the bladder to be measured by measuring the bladder pressure in conjunction with a controller. 11. The compression processing system of claim 10 wherein said fluid source alternately inflate bladder disposed about a limb and bladder disposed around a leg. 11. The compression processing system of claim 10, further comprising a controller in communication with the fluid source and the single pressure sensor, the controller configured to monitor and regulate pressure in the bladder. 12. The compression processing system as claimed in claim 11, wherein said controller is disposed with a portable housing. 12. The compression processing system as recited in claim 11, wherein said controller includes a separate valve that regulates bulging of bladders. delete 11. The compression processing system of claim 10, wherein said single pressure sensor is configured to monitor the pressure of each bladder. A first plurality of bladders supported around the first limb, A second plurality of bladders supported around the second limb, A pneumatic control circuit located in a controller separately received from said bladders, The bladders are in fluid communication with a fluid source, The first bladder of the first plurality of bladders is inflated for a first time period and the second bladder of the first plurality of bladders is inflated to inflate for a second time period, and the second bladder is inflated. The time period is initiated within the first time period, The first bladder of the second plurality of bladders is inflated for a third time period, the second bladder of the second plurality of bladders is inflated to inflate for a fourth time period, and the first bladder is inflated for the fourth time period. A four time period is initiated within said third time period, The pneumatic control circuit comprises the controller, a single pressure sensor, a single check valve, the fluid source, a plurality of solenoid valves, The single pressure sensor is located between the fluid source and the solenoid valve and in communication with the bladder, The check valve is operably connected to the fluid source and positioned between the fluid source and the solenoid valve, the single check valve prevents leakage to the outside of the bladder to be measured, And the single pressure sensor calculates the venous refill time at the bladder to be measured by measuring the bladder pressure in conjunction with a controller. 18. The compression processing system as recited in claim 17, further comprising a controller disposed with the portable housing, said controller in communication with said fluid source and a single pressure sensor, said controller configured to monitor and regulate pressure in bladder. . 18. The compression processing system of claim 17 wherein said fluid source alternately inflate bladder disposed about said first limb and bladder disposed about said second limb. A first plurality of bladders supported around the first limb and a second plurality of bladders supported around the second limb, A pneumatic control circuit located in a controller separately received from said bladders, Each bladder of the first plurality of bladders and the second plurality of bladders has a separate valve, the separated valve communicating with the first and second plurality of bladders, The valves are in fluid communication with a fluid source, The first valve of the first plurality of bladders is inflated for a first time period by opening the first valve, and the second bladder of the first plurality of bladders is seconded by the opening of the second valve. The bladder is inflated to inflate for a third time period by inflating a third valve, the third of the first plurality of bladders being inflated during a third time period, the second period being the first time period Within a second period, and wherein the third time period begins within the second period, The first valve of the second plurality of bladders is inflated for a fourth time period by opening a fourth valve, and the second bladder of the second plurality of bladders is opened by a fifth valve by opening the fifth valve. Inflated for a period of time, wherein the second plurality of sixth bladders are inflated to inflate during a sixth time period, and the fifth time period is initiated within the fourth time period. The sixth time period is initiated within the fifth time period, The pneumatic control circuit comprises the controller, a single pressure sensor, a single check valve, the fluid source and a plurality of solenoid valves, The controller is configured to communicate with the fluid source and a single pressure sensor and to monitor and regulate the pressure in the bladders, The single pressure sensor is located between the fluid source and the solenoid valve and in communication with the bladder, the check valve is operably connected to the fluid source and positioned between the fluid source and the solenoid valve, The check valve prevents leakage to the outside of the bladder to be measured, And the single pressure sensor calculates the venous refill time at the bladder to be measured by measuring the bladder pressure in conjunction with the controller. delete delete delete delete delete The compression processing system of claim 1, wherein the check valve operates without an electrical signal to the controller. 11. The compression processing system of claim 10, wherein said check valve operates without an electrical signal to said controller. 18. The compression processing system of claim 17 wherein said check valve operates without an electrical signal to said controller. 21. The compression processing system as claimed in claim 20, wherein said check valve operates without an electrical signal to said controller. delete