# Patent

## Title
Methods and systems for auto-calibration of a pneumatic compression device

## Abstract

Systems for auto-calibrating a pneumatic compression system may include one or more manifolds from an inflation fluid source and one or more individually inflatable cells. One or more pressure sensors may be associated with the one or more manifolds and/or each of the individually inflatable cells. Each of the pressure sensors may provide either dynamic or static pressure data to a controller. A method for auto-calibrating the compression system may include introducing a portion of inflation fluid into a cell while measuring a dynamic cell pressure, stopping the introduction of fluid, measuring a static cell pressure, and comparing, by the computing device, the dynamic cell pressure and the static cell pressure. sure. The comparison between dynamic and static cell pressures may be used to calculate a dynamic target cell pressure equivalent to a desired static target cell pressure.

## Background
BACKGROUND
Diseases such as venous insufficiency and lymphedema can often result in the pooling of bodily fluids in areas of the body distal from the heart. Venous insufficiency can result when the superficial veins of an extremity empty into the deep veins of the lower leg. Normally, the contractions of the calf muscles act as a pump, moving blood into the popliteal vein, the outflow vessel. Failure of this pumping action can occur as a result of muscle weakness, overall chamber size reduction, valvular incompetence and/or outflow obstruction. Each of these conditions can lead to venous stasis and hypertension in the affected area. Lymphedema, which is swelling due to a blockage of the lymph passages, may be caused by lymphatic obstruction, a blockage of the lymph vessels that drain fluid from tissues throughout the body. This is most commonly due to cancer surgery, general surgery, tumors, radiation treatments, trauma and congenital anomalies. Lymphedema is a chronic condition that currently has no cure.
Fluid accumulation can be painful and debilitating if not treated. Fluid accumulation can reduce oxygen transport, interfere with wound healing, provide a medium that support infections, or even result in the loss of a limb if left untreated.
Compression pumps are often used in the treatment of venous insufficiency by moving the accumulated bodily fluids. Such pumps typically include an air compressor that may blow air through tubes to an appliance such as a sleeve or boot containing a number of separately inflatable cells that is fitted over a problem area (such as an extremity or torso). Such pumps may also include pneumatic components adapted to inflate and exhaust the cells, and control circuitry governing the pneumatic components. A therapeutic cycle typically involves sequential inflation of the cells to a pre-set pressure in a distal to a proximal order, followed by exhausting all the cells in concert.
While such a compression device may be used in therapy for lymphedema, other pathologies, including venous stasis ulcers, soft tissue injuries, and peripheral arterial disease, and the prevention of deep vein thrombosis may be improved by the use of such a compressor device. However, a therapeutic protocol that may be useful for lymphedema may not be appropriate for other pathologies. Improved systems and methods for implementing and controlling a pneumatic compression device to assist in a variety of therapeutic protocols would be desirable.
SUMMARY
Before the present methods, systems and materials are described, it is to be understood that this disclosure is not limited to the particular methodologies, systems, and materials described, as these may vary. It is also to be understood that the terminology used in the description is for the purpose of describing the particular versions or embodiments only, and is not intended to limit the scope.
It must also be noted that as used herein and in the appended claims, the singular forms “a,” “an,” and “the” include plural references unless the context clearly dictates otherwise. Thus, for example, reference to a “valve” is a reference to one or more valves and equivalents thereof known to those skilled in the art, and so forth. Unless defined otherwise, all technical and scientific terms used herein have the same meanings as commonly understood by one of ordinary skill in the art. Although any methods, materials, and devices similar or equivalent to those described herein can be used in the practice or testing of embodiments, the preferred methods, materials, and devices are now described. All publications mentioned herein are incorporated by reference. Nothing herein is to be construed as an admission that the embodiments described herein are not entitled to antedate such disclosure by virtue of prior invention.
For the purpose of this disclosure, the term “open”, when referring to a valve or valve system, may be defined as a state of the valve or valve system in which a structure associated with a first side of the valve is placed in fluid communication with a structure associated with a second side of the valve.
For the purpose of this disclosure, the term “closed”, when referring to a valve or valve system, may be defined as a state of the valve or valve system in which a structure associated with a first side of the valve is not placed in fluid communication with a structure associated with a second side of the valve.
For the purpose of this disclosure, the term “inflatable compression sleeve”, “compression sleeve” or “appliance” may all refer to a device comprising at least one inflatable cell, being designed to provide an amount of pressure to a tissue. Non-limiting examples of such inflatable compression sleeve may comprise one or more of a chest sleeve, a foot sleeve, an ankle sleeve, a calf sleeve, a lower leg sleeve, a thigh sleeve, an upper leg sleeve, a lower arm sleeve, an upper arm sleeve, a wrist sleeve, a hand sleeve, a chest sleeve, a single shoulder sleeve, a back sleeve, an abdomen sleeve, a buttocks sleeve, a genital sleeve, and combinations thereof.
In one embodiment, a method of auto-calibrating a pneumatic compression therapy device may comprise providing a compression therapy device including an inflatable compression sleeve comprising an inflatable cell, a fill manifold configurable to be in fluid communication with the inflatable cell, a fluid source having a source output configured to introduce a fluid into the inflatable cell via the fill manifold, a cell valve disposed between the inflatable cell and the fill manifold, a pressure sensor, and a controller configured to receive pressure sensor data from the pressure sensor, and to control one or more actions of the cell valve and the fluid source. The controller may further comprise at least one processor device and at least one non-transitory memory storage device. The method may further comprise receiving, by the cell, a first portion of fluid from the fluid source and receiving, by the controller, dynamic pressure sensor data related to a dynamic pressure within the cell, receiving, by the controller, static pressure sensor data related to a static pressure within the cell, calculating, by the controller, a pressure difference between the dynamic pressure sensor data and the static pressure sensor data, and calibrating, by the controller, a dynamic pressure sensor target value based, at least in part, on one or more of a static pressure sensor target value, the dynamic pressure sensor data, the static pressure sensor data, and the pressure difference.



BRIEF DESCRIPTION OF THE DRAWINGS
Aspects, features, benefits and advantages of the embodiments described herein will be apparent with regard to the following description, appended claims, and accompanying drawings where:
FIGS. 1a, b illustrate embodiments of a pneumatic compression device in accordance with the present disclosure.
FIGS. 2a-d illustrate various embodiments of cells used in a pneumatic compression device in accordance with the present disclosure.
FIG. 3 is a block diagram of an embodiment of hardware that may be used to contain or implement program instructions in accordance with the present disclosure.
FIGS. 4-9 illustrate a variety of embodiments of therapeutic protocols in accordance with the present disclosure.
FIG. 10 is a flowchart of an embodiment of a method for auto-calibration of a pneumatic compression device in accordance with the present disclosures.
FIGS. 11a-c depict various embodiments of systems to which a method of auto-calibration may apply in accordance with the present disclosure.



DETAILED DESCRIPTION
FIG. 1a,b depict embodiments of a pneumatic compression device. As shown in FIG. 1a, the pneumatic compression device may include one or more compression pumps 105, a fill valve 120, a vacuum source 110, an exhaust valve 130, a transducer 115, a controller 145 and a plurality of cell valves, such as 125a-N. The compression pump 105 may be used as a source of a pressurized fluid, including, without limitation, air, nitrogen, or water. The fill valve 120 may be in fluid connection with the compression pump 105 through a pressure pump output to receive the pressurized fluid. During an inflation period, the fill valve 120 may open to connect the output of the compression pump 105 to a common node or manifold 140. During a deflation period, exhaust valve 130 may open to connect the common manifold 140 to, for example, a vacuum source 110 to depressurize the cells. Alternatively, exhaust valve 130 may be connected to atmosphere 135. It may be understood that the vacuum source and/or atmosphere may serve as a sink of the pressurizing fluid. One or more inputs to the vacuum or to the atmosphere may be provided. Typically, fill valve 120 and exhaust valve 130 may not be open at the same time. However, some modes of use of the compression device may benefit from the fill valve and exhaust valve being open together. Although FIG. 1a illustrates a single exhaust valve 130 capable of connecting to either a vacuum source 110 or the atmosphere 135, it may be appreciated that one exhaust valve may be used to connect the manifold 140 to the vacuum source 110, while a second exhaust valve may be used to connect the manifold 140 to atmosphere 135. Fill valve 120 and exhaust valve 130 may be manually operated, or may be automatically operated by controller 145. Additional fill and/or exhaust valves may be associated with the manifold 140. Each of the cell valves 125a-N may be connected to the common manifold 140 on a first side and a corresponding cell on a second side. Additionally, one or more sensors, such as pressure sensors or flow rate sensors, may be on the cell side of the valves. Each cell valve 125a-N may be used to selectively connect (in an open configuration) or disconnect (in a closed configuration) the corresponding cell to the common manifold 140. Cell valves 125a-N may also be manually operated or automatically operated by controller 145.
The transducer 115 may be connected to and used to monitor the pressure of the common manifold 140. The controller 145 may receive information regarding the pressure detected by the transducer 115 or by any other sensor associated with the cell valves. Based on at least the received pressure information, the controller 145 may determine whether to open or close the fill valve 120, the exhaust valve 130, and/or one or more of the cell valves 125a-N.
In an embodiment, illustrated in FIG. 1a, the transducer 115 may have a transfer function associated with it which is used to determine the input pressure monitored at the common manifold 140. For example, the transfer function for an MPX5050 transducer manufactured by Motorola may be VO=VS*(0.018*P+0.04)+Offset Error, where VO is the output voltage, VS is the supply voltage (which may be, for example, approximately 5 Volts), P is the input pressure as measured in kPa, and Offset Error is a static voltage value that is dependent on the process, voltage, and temperature of the transducer. Solving for the pressure and combining the Offset Error and 0.04VS term results in the following equation:




  
    
      
        
          P
          ⁡
          
            (
            kPa
            )
          
        
        =
        
          
            55.6
            *
            
              (
              
                
                  V
                  O
                
                -
                
                  V
                  offset
                
              
              )
            
          
          
            V
            S
          
        
      
    
    
      
        (
        1
        )
      
    
  




Equation (1) may also be represented in terms of mm Hg by converting 1 kPa to 7.5 mm Hg. The resulting equation is the following:





  
    
      
        
          P
          ⁡
          
            (
            
              mm
              ⁢
              
                
              
              ⁢
              Hg
            
            )
          
        
        =
        
          
            417
            *
            
              (
              
                
                  V
                  O
                
                -
                
                  V
                  offset
                
              
              )
            
          
          
            V
            S
          
        
      
    
    
      
        (
        2
        )
      
    
  




The transducer 115 may then be calibrated to determine the pressure based on the output voltage. Initially, Voffset may be determined by closing all of the cell valves 125a-N and venting the common manifold 140 to the atmosphere 135 via the exhaust valve 130. A value determined by an analog-to-digital (A/D) converter that may either be in communication with or integral to the transducer 115 may be read when the transducer is under atmospheric pressure. The value output by the A/D converter may be an offset value (OFFSET). For a 12-bit A/D converter, OFFSET may be between 0 and 4095.
A scale value (SCALE) may also be determined that corresponds to a scaled source voltage. For example, a precision resistor divide-by-two circuit may be used to divide VS by 2. The A/D converter may output SCALE based on the VS/2 input value. For a 12-bit A/D converter, SCALE may be a value between 0 and 4095.
Substituting OFFSET and SCALE into Equation (2) results in the following equation:




  
    
      
        
          P
          ⁡
          
            (
            
              mm
              ⁢
              
                
              
              ⁢
              Hg
            
            )
          
        
        =
        
          
            208.5
            *
            
              (
              
                TRANSDUCER_OUTPUT
                -
                OFFSET
              
              )
            
          
          SCALE
        
      
    
    
      
        (
        3
        )
      
    
  




As such, the offset error and the scale error of the transducer 115 and any errors in the transducer supply voltage may be accounted for by measuring the OFFSET and SCALE values once (for example, at power up).

Alternative transducers potentially having different transfer functions may also be used within the scope of the present disclosure as will be apparent to one of ordinary skill in the art. In addition, one of ordinary skill in the art will recognize that alternate methods of calibrating a transducer may be performed based on the teachings of the present disclosure.
An additional embodiment is illustrated in FIG. 1b. In this embodiment, a fill manifold 141 may be associated with the fill valve 120 and compression pump 105. A separate exhaust manifold 142 may be associated with the vacuum source 110 and exhaust valve 130. Cell valves 125a-N may be associated with both the fill manifold 141 and exhaust manifold 142. It is understood that cell valves 125a-N in this embodiment may have a 3-way function: open to fill, open to exhaust, and closed. In an alternative embodiment, each cell may have a first valve to connect to the fill manifold 141 and a second valve to connect to the exhaust manifold 142. In the dual manifold embodiment in FIG. 1b, transducer 115, associated with fill manifold 141, may be calibrated with respect to atmosphere in a manner as disclosed above by means of a separate shunt valve (not shown) associated either directly with transducer 115 or with the fill manifold 141. It may be understood that during the calibration process, fill valve 120 and cell valves 125a-N may be closed. Exhaust manifold 142 may also be in communication with its own transducer 115′ to monitor the pressure within the exhaust manifold. Transducer 115′ may be calibrated with respect to atmosphere in a manner similar to that disclosed above with regards to transducer 115 in FIG. 1a. Transducers 115 and 115′ may provide sensor data as well to controller 145.
In addition, each valve 125a-N may be in fluid connection with a flow sensor 150a-N in-line with the connection to its respective cell. Each flow sensor 150a-N may be associated with a valve 125a-N or with an inflatable cell. Flow sensors 150a-N may provide sensor data as well to controller 145. For example, a flow sensor 150a-N may be used to monitor that its respective valve 125a-N is completely open. If a valve is blocked or otherwise impeded, the fluid flow through it may not match an expected flow profile as determined by controller 145. A flow sensor could provide the controller with data to indicate a fault with the associated valve. The controller may then be programmed to notify a user of the valve flow fault condition. Additionally, the flow sensors may be used to accurately determine the fill/exhaust time for a cell. Based on the data from the flow sensor, the fill/exhaust rate for a cell may be adjusted by controller 145 to control the amount of time required for a fill or exhaust step. A clinician developing a particular therapy protocol may then be able to program a fill or exhaust time as part of the protocol. Such time-based programming may be easier for a clinician to use instead of flow rates and volumes. In addition, the volume of a cell and the fill rate from the flow sensor may allow the controller 145 to detect the presence or absence of a limb in a sleeve or boot incorporating the pressure cells, and may allow the controller the ability to calculate the volume or size of the limb. In one embodiment, a measurement of limb or foot size may be used by the controller for compliance monitoring. In another embodiment, such data may also be used as input to an algorithm for making the compression device more adaptive for different limb sizes
Additionally, a pressure sensor 155a-N may be associated with each cell to measure the fluid pressure within the cell during its operation. Alternatively, each pressure sensor 155a-N may be associated with a respective cell valve 125a-N. The pressure sensors 155a-N may also provide data to controller 145 so that the controller may be able to control the operation of the compression device. A pressure sensor 155a-N associated with its respective cell, may provide direct indication of a pressurization or depressurization profile of the cell. Controller 145 may compare an individual cell pressure against a pre-programmed cell pressure profile. If a cell is unable to sustain an expected pressure, a leak condition may be determined. The controller 145 may then be programmed to notify a user of the leak condition.
Although FIG. 1a does not explicitly illustrate the use of either flow or pressure sensors between the valves 125a-N and their respective cells, it may be appreciated that either flow sensors, pressure sensors, or both types of sensors may be included in alternative embodiments. Similarly, although FIG. 1b illustrates the use of such sensors, it should be understood that other embodiments may lack either one or both types of sensors.
Additional features may be associated with the cells, including, without limitation, volume sensors, inflation sensors, and additional valves. FIGS. 2a-d illustrate a number of embodiments of the inflation cells that may be used with the pneumatic compression device. In one embodiment, illustrated in FIG. 2a, an inflatable cell 210a may be in fluid connection with its cell valve 225a. Cell valve 225a may be in fluid communication with the manifold 140 as in FIG. 1a, or both fill manifold 141 and exhaust manifold 142 as in FIG. 1b. 
In another embodiment, illustrated in FIG. 2b, cell 210b may have a cell valve 225b also in fluid communication with the manifold 140 as in FIG. 1a, or manifolds 141 and 142 as in FIG. 1b. In addition, cell 210b may have a shunt valve 215 which may be vented to the atmosphere. For example, valve 215 may be used as an emergency release valve in the event that a cell is unable to be exhausted by valve 125 and/or exhaust valve 130. Valve 215 may be manually operated or automatically operated under control of controller 145.
As illustrated in FIG. 2c, a cell 210c may have a cell valve 225c and may also have a strain gage 220 associated with the cell material. Strain gage 220 may be glued or otherwise affixed to the cell, or fabricated as part of the cell, and may be associated with either the inner or outer surface of the cell. The strain gage 220 may be used to measure the deformation of the cell material as it is inflated or deflated, and thereby provide a measure of the volume of fluid within the cell. Although a single strain gage 220 is illustrated, it may be appreciated that multiple strain gages may be associated with each cell to provide accurate data regarding the change in volume or shape of the cell during a therapeutic cycle.
In another embodiment, illustrated in FIG. 2d, cell 210d may be in fluid communication with valve 225d, permitting the cell to have fluid access to the fill and/or exhaust manifold. Cell 210d may be fitted with a plethysmograph sensor 230 that may also be used to detect changes in cell shape or volume during a therapeutic cycle. Multiple plethysmograph sensors may be associated with each cell for improved data collection.
Strain gage 220 and plethysmograph sensor 230 may be in data communication with controller 145, thereby providing a point of control feedback to the controller. Although strain gage 220 and plethysmograph sensor 230 are illustrated in FIG. 2, it may be understood that they represent non-limiting examples of sensor systems capable of determining the change in cell shape and/or volume.
The pneumatic compression device may be may be operated to provide a variety of therapeutic protocols. A therapeutic protocol may be defined as a specific sequence of operations to inflate (fill) and deflate (exhaust) one or more cells while they are in contact with a patient. Therapeutic protocols may include, in a non-limiting example, a list of an ordered sequence of cells to be activated, an inflation or deflation pressure threshold value for each cell, an amount of time during cell inflation or deflation, and a phase or lag time between sequential cell activation. In one non-limiting example, the therapeutic protocol may result in the inflation of a plurality of cells substantially simultaneously. In an alternative non-limiting embodiment, the therapeutic protocol may result in the inflation of a plurality of cells in an ordered sequence. It may be understood that an ordered sequence of cells is a sequence of cell inflation over time. In one non-limiting example, the sequentially inflated cells may be physically contiguous in the compression sleeve. In another non-limiting example, the sequentially inflated cells may not be physically contiguous, but may be located in physically separated parts of the compression sleeve. In an additional non-limiting example, the therapeutic protocol may result in stopping the inflation of a plurality of cells substantially simultaneously. In an additional non-limiting example, the therapeutic protocol may result in stopping the inflation of a plurality of cells in an ordered sequence. In some non-limiting examples of a therapeutic protocol, each of a plurality of cells may retain fluid at about the same cell pressure. In some non-limiting examples of a therapeutic protocol, each of a plurality of cells may retain fluid at different pressures. A further non-limiting example of the therapeutic protocol may include deflating a plurality of cells substantially simultaneously. A further non-limiting example of the therapeutic protocol may include deflating a plurality of cells in an ordered sequence. It may be understood that an ordered sequence of cells is a sequence of cell deflation over time. In one non-limiting example, the sequentially deflated cells may be physically contiguous in the compression sleeve. In another non-limiting example, the sequentially deflated cells may not be physically contiguous, but may be located in physically separated parts of the compression sleeve. In yet another non-limiting example of a therapeutic protocol, one of the cells may be inflated and a second cell may be deflated during at least some period of time. As one non-limiting example, one or more cells may be inflated simultaneously as one or more cells are deflated. In another non-limiting example, a first one or more cells may begin inflation and a second one or more cells may begin deflation after the first one or more cells have started inflating. In an alternative non-limiting example, a first one or more cells may begin deflation and a second one or more cells may begin inflation after the first one or more cells have started deflating.
Prior to the start of a therapeutic protocol, an initialization sequence may occur. In one example of an initialization sequence, fill valve 120 may be closed, thereby isolating the compression pump 105 from a manifold (either 140 or 141), and exhaust valve 130 may be opened to atmosphere 135. The cell valves 125a-N may then be opened thereby placing each cell in fluid communication with either the common manifold 140 or exhaust manifold 142 thereby allowing all the cells to be vented to atmosphere. Alternatively, exhaust valve 130 may be opened to vacuum source 110 to permit rapid evacuation of the cells. The controller 145 may determine whether a minimum pressure threshold has been reached based on information received from the transducer 115 (for a common manifold configuration) or from transducer 115′ (for a dual manifold configuration). The controller 145 may also receive sensor data from the cell specific pressure sensors 155a-N. In one embodiment, when the minimum pressure threshold is reached, the controller 145 may send operation commands to exhaust valve 130 to close. In another embodiment, the controller 145 may also provide operation commands to the cell valves 125a-N to close. In yet another embodiment, the controller may initiate a therapeutic protocol. It may be appreciated that the initialization sequence may occur while the cells are in contact with the patient, before the cells are affixed onto the patient, or after a protocol has been completed.
A protocol may incorporate one or more cell fill phases. As a non-limiting example of such a fill phase, the following operating sequence may occur. One or more cell valves 125a-N may be opened along with the fill valve 120 thereby allowing the one or more cells to be in fluid communication with the compression pump 105. In an embodiment incorporating a common manifold 140, one or more of the cell valves 125a-N may open to the common manifold. In an embodiment having independent fill 141 and exhaust 142 manifolds, one or more of the cell valves 125a-N may be configured to open the cells to communicate with the fill manifold 141 only. In an embodiment, a cell valve, such as 125a, connected to a cell affixed to a distal portion of the patient, may be opened or remain open to the fill 141 or common 140 manifold for inflation while cell valves associated with more proximal cells are closed to that manifold. The cell (e.g. cell A) connected to the open cell valve (e.g. 125a) may inflate as a result of being connected to the pressurized fluid from the compression pump 105. The cell pressure may be monitored by the controller 145 via the transducer 115, a pressure sensor 155a associated specifically with that cell, or by both.
In an embodiment, the amount of pressure sensed by the transducer 115 may differ from the cell pressure at a particular cell. For example, pressure losses may occur between the transducer 115 and a cell. Accordingly, the controller 145 may access a lookup table to determine the threshold at which the pressure sensed by the transducer 115 is appropriate to close the cell valve 125a-N corresponding to the cell.
In another embodiment of a fill phase, an opened cell valve, such as 125a, may be modulated to control the fill rate of the corresponding cell. The opened cell valve may be modulated based on time and/or pressure. For example, a cell valve that is being modulated on a time basis may be opened for a first period of time and closed for a second period of time as the cell is inflating. Alternately, a cell valve that is being modulated on a pressure basis may be opened while the cell pressure increases and closed for a period of time during the inflation cycle. The pressure increase may be determined by measuring an initial cell pressure before opening the cell valve and the cell pressure as the cell valve is open. When the difference between the initial cell pressure and the inflating cell pressure is substantially equal to a specific value, the cell valve may be closed. The duty cycle at which the cell valve is modulated may be any value and may be specifically programmed by a user or clinician. The controller 145 may determine when to open and close the cell valve. For pressure-based modulation, any one or more of transducer 115 or cell specific pressure sensors 155 may provide pressure data to the controller 145 to assist in determining when to open and/or close the cell valve during modulation.
Modulation may be performed to ensure that the cell pressure does not increase too quickly for a given protocol. For example, a lymphedema patient may be treated with a protocol requiring slowly inflating and deflating cells. Alternatively, an arterial patient may require a protocol capable of rapid inflation and deflation cycles. Moreover, cells may be of varying size. For example, cells in a device designed for a child may be smaller than cells in a device designed for an adult. However, the compression pump 105 may have a relatively fixed flow rate. As such, modulation may be used to ensure that cell inflation is performed at a proper rate.
In an alternate embodiment, a cell valve, such as 125a, may include a variable aperture, which may be used to restrict the rate at which the pressure increases in the corresponding cell. A flow sensor such as 150a may monitor the fluid flow rate into the cell. The data from the flow sensor may be provided to controller 145 so that the controller may be able to adjust the aperture in the cell valve. In another embodiment, a cell valve such as 125a may incorporate a one-way valve. For example, if valve 125a is opened to allow cell A to be filled by common manifold 140 or fill manifold 141, and then valve 125b is opened to allow cell B to be pressurized, a one-way valve incorporated in valve 125a will prevent transient depressurization of cell A when valve 125b is opened to initially evacuated cell B. In another alternate embodiment, a compression pump 105 that operates with a variable flow rate may be used. Additional methods of modulating pressure may also be performed and will be apparent to one of ordinary skill in the art based on this disclosure.
When the cell reaches an appropriate pressure threshold value incorporated as a part of a therapeutic protocol, the controller 145 may close the cell valve 125a corresponding to the cell.
A protocol may also incorporate one or more cell exhaust phases. As a non-limiting example of such an exhaust phase, the following operating sequence may occur. One or more cell valves 125a-N may be opened along with the exhaust valve 130 thereby allowing the one or more cells to be in fluid communication with either the vacuum source 110, or the atmosphere 135. In an embodiment incorporating a common manifold 140, one or more of the cell valves 125a-N may open to the common manifold. In an embodiment having independent fill 141 and exhaust 142 manifolds, the one or more cell valves 125a-N may be configured to open the cells to communicate with the exhaust manifold 142 only. In an embodiment, a cell valve, such as 125a, connected to a cell affixed to a distal portion of the patient, may be opened or remain open to the exhaust 142 or common 140 manifold for deflation while cell valves associated with more proximal cells are closed to that manifold. The cell (e.g. cell A) connected to the open cell valve (e.g. 125a) may deflate as a result of being connected to the vacuum source 110 or atmosphere 135. The cell pressure may be monitored by the controller 145 via transducer 115 for a common manifold configurations or transducer 115′ for independent manifold configurations, a pressure sensor 155a associated specifically with that cell, or by both.
In an embodiment, the amount of pressure sensed by the transducer 115 or transducer 115′ may differ from the cell pressure at a particular cell. For example, pressure losses may occur between the transducer 115 (or 115′) and a cell. Accordingly, the controller 145 may access a lookup table to determine the threshold at which the pressure sensed by the transducer 115 (or 115′) is appropriate to close the cell valve 125a-N corresponding to the cell.
In another embodiment of an exhaust phase, an opened cell valve, such as 125a, may be modulated to control the exhaust rate of the corresponding cell. The opened cell valve may be modulated based on time and/or pressure. For example, a cell valve that is being modulated on a time basis may be opened for a first period of time and closed for a second period of time as the cell is deflating. Alternately, a cell valve that is being modulated on a pressure basis may be opened while the cell pressure decreases and closed for a period of time during the exhaust cycle. The pressure decrease may be determined by measuring an initial cell pressure before opening the cell valve and the deflated cell pressure as the cell valve is open. When the difference between the initial cell pressure and the cell pressure is substantially equal to a specific value, the cell valve may be closed. The duty cycle at which the cell valve is modulated may be any value and may be specifically programmed by a user or clinician. The controller 145 may determine when to open and close the cell valve. For pressure-based modulation, any one or more of transducers 115, 115′, or cell specific pressure sensors 155 may provide pressure data to the controller 145 to assist in determining when to open and/or close the cell valve during modulation.
Modulation during inflation may be performed to ensure that the cell pressure does not decrease too quickly, which could cause a reverse gradient. While a typical pressure gradient may result in distal cells having a greater pressure than proximal cells, a reverse gradient may result in proximal cells having a greater pressure than distal cells. Reverse gradients are frequently considered undesirable, although some therapeutic protocols may make use of them. Moreover, cells may be of varying size. For example, cells in a device designed for a child may be smaller than cells in a device designed for an adult. However, the vacuum source 110 may have a relatively fixed flow rate, and venting to atmosphere 135 may occur due to unregulated, passive exhaust. As such, modulation may be used to ensure that cell deflation is performed at a proper rate.
In an alternate embodiment, a cell valve, such as 125a, may include a variable aperture, which may be used to restrict the rate at which the pressure decreases in the corresponding cell. A flow sensor such as 150a may monitor the fluid flow rate into the cell. The data from the flow sensor may be provided to controller 145 so that the controller may be able to adjust the aperture in the cell valve. In another embodiment, a cell valve such as 125a may incorporate a one-way valve. For example, if valve 125a is opened to allow cell A to be evacuated by exhaust manifold 142, and then valve 125b is opened to allow cell B to be evacuated, a one-way valve incorporated in valve 125a will prevent transient re-pressurization of cell A when valve 125b is opened to previously pressurized cell B. In another alternate embodiment, a vacuum source 110 that operates with a variable flow rate may be used. Additional methods of modulating pressure may also be performed and will be apparent to one of ordinary skill in the art based on this disclosure.
When the cell reaches an appropriate pressure threshold incorporated as a part of a therapeutic protocol, the controller 145 may close the cell valve 125a corresponding to the cell.
It may be appreciated that a therapeutic protocol may be composed of any variety of sequences of cell inflation and deflation steps. Cells may be inflated and deflated in a specific order, and multiple cells may be inflated or deflated either in synchrony or in a staggered fashion. The cells may be held at a particular inflation or deflation pressure for a specific amount of time. In addition, a specific protocol may be repeated with some lag time between repeats. Alternatively, a first protocol may be followed by a second and different protocol.
In one embodiment of a protocol, a plurality of cell valves 125a-N may be opened simultaneously to inflate the plurality of respective cells simultaneously. As the pressure in each cell surpasses a corresponding threshold, the controller 145 may close the cell valve 125a-N for the cell. The pressure thresholds for all the cells may be identical or they may differ. For example, the pressure threshold for a cell at a distal position on a patient may be higher than a cell more proximally located. As a result, a pressure gradient may be developed by the cells from a greater pressure at the distal point, to a lesser pressure at the proximal point. The cells may then be deflated simultaneously until they all reach an ambient pressure. Alternatively, only selected cells may be deflated.
In an another embodiment of a protocol, the cell valves 125a-N may not be opened simultaneously when the cells are deflated, but rather may be opened in a staggered fashion. In an embodiment based on the common manifold configuration, fill valve 120 may be closed, and exhaust valve 130 may be opened to either the vacuum source 110 or to atmosphere 135. A first cell valve, such as 125a, may be opened to release the pressure in the corresponding cell. After a short period of time elapses, a second cell valve, such as 125b, may be opened to release the pressure in the corresponding cell. Such a delay time between the deflation of successive cells, may be about 1 second long or longer. In an alternative non-limiting example, the controller 145 may cause a cell valve, such as 125a or 125b, to release the pressure in the corresponding cell in response to the controller receiving data from a corresponding cell sensor, such as a pressure sensor 155a or 155b. The controller 145 may cause the pressure in a cell to be released then the sensor data has achieved a therapeutic protocol defined threshold value, such as a maximum pressure. The process may be repeated until each cell valve 125a-N has been opened.
In an embodiment of a protocol using modulation, a plurality of cell valves 125a-N may be modulated simultaneously. At any given time, one or more cell valves may be opened and/or closed according to a modulation schedule. For example, for a time-based modulation scheme having a 50% duty cycle, half of the cell valves 125a-N may be open and half of the cell valves may be closed at any time.
FIG. 3 is a block diagram of an embodiment of hardware that may be used to contain or implement program instructions for controller 145. Some or all of the below-described hardware may be incorporated in the controller 145. Referring to FIG. 3, a bus 328 may serve as the main information highway interconnecting the other illustrated components of the hardware. CPU 302 or other computing device is the central processing unit of the system, performing calculations and logic operations required to execute a program. Read only memory (ROM) 318 is one embodiment of a static memory device and random access memory (RAM) 320 is one embodiment of a dynamic memory device.
A controller 304 may interface the system bus 328 with one or more optional disk drives 308. These disk drives may include, for example, external or internal DVD drives, CD ROM drives, or hard drives. Such drives may also be used as non-transitory computer-readable storage devices.
Program instructions may be stored in the ROM 318 and/or the RAM 320. Optionally, program instructions may be stored on a computer readable medium such as a compact disk or a digital disk or other recording medium, or received by means of a communications signal or a carrier wave. Such program instructions may include a library of pre-loaded therapeutic protocols. Non-limiting examples of such program instructions may cause the controller to receive an input related to one or more therapeutic protocols from an input device, place at least two of the plurality of valves into the first state for a period of time based at least in part on the one or more therapeutic protocols, receive cell sensor data from at least one cell sensor, and transmit, to the output device, an output related to the data from at least one cell sensor. Additional instructions may cause the computing device to place at least two of the plurality of valves in one of the first state and the third state for a period of time based at least in part on data received from at least one cell sensor in operable communication with each of the at least two valves. Additional instructions may cause the computing device to place at least two of the plurality of valves in the first state substantially simultaneously or in an ordered sequence. Further instructions may cause the computing device to place the at least two of the plurality of valves in the third state, either substantially simultaneously or in an ordered sequence. Various instructions may be directed towards receiving sensor data, for example from pressure or flow sensors associated with the valves, and comparing them against appropriate threshold values as included in the therapeutic protocol. Similar instructions may be directed towards placing any of the valves into any of the possible cell states based on the sensor data values and threshold values according the therapeutic protocol.
An optional display interface 322 may permit information from the bus 328 to be displayed on the display 324 in audio, graphic or alphanumeric format. Communication with external devices may occur using various communication ports 326. For example, communication with the fill valve 120, exhaust valve 130, and/or the cell valves 125a-N may occur via one or more communication ports 326. Controller 145 may also provide command data over communication ports 326 to valves 120, 130, and 125a-N to direct their respective operations.
In addition to the components disclosed above, the hardware may also include an interface 312 which allows for receipt of data from input devices such as a keyboard 314 or other input device 316 such as a mouse, remote control, pointing device, and/or joystick. Such input devices may allow a user to choose a pre-programmed therapeutic protocol from a library of such protocols maintained by the controller, enter parameters into a preprogrammed protocol, or enter a new therapeutic protocol into the controller. In addition, transducers 115 and 115′, pressure sensors 155a-N, flow sensors 150a-N, as well as sensors communicating data related to the change in shape or volume of the cells, such as a strain gage 220 and/or a plethysmograph 230, may communicate sensor input 315 through interface 312 to bus 328.
In an embodiment, the controller 145 may store and/or determine settings specific to each cell. For example, the controller 145 may determine one or more pressure thresholds for each cell. Moreover, the controller 145 may prevent the pneumatic compression device from being used improperly by enforcing requirements upon the system. For example, the controller 145 may be programmed so that distal cells in a therapeutic protocol are required to have higher pressure thresholds than proximal cells. The controller may override instructions received from a user via the user interface that do not conform to such pressure threshold requirements. In an embodiment, the pressure thresholds of one or more cells may be adjusted to meet the pressure threshold constraints.
In a further embodiment, controller 145 may provide a compression device user with an interface to permit the user to program the control to provide a variety of therapeutic protocols for patients. The interface may be displayed on the control display, such as a flat panel display. Input devices such as a mouse, keypad, or stylus may be used by the user to provide data to define a particular therapeutic protocol. The controller may record the protocols on a memory or disk device for future use. In one embodiment of the controller, a user may be presented with a list of previously stored therapeutic protocols from which to choose for a particular patient. In another embodiment, a user may define a therapeutic protocol for a patient on an as-needed basis. In another embodiment, a user may choose a stored protocol and modify it. It may be appreciated that such programming may be accomplished through any of a variety of methods. In one non-limiting example, a therapist or other health care professional may enter commands and/or parameters via a keyboard. In another non-limiting example, the therapist or other health care professional may use a mouse or touch screen to select one or more pre-programmed therapeutic protocols or parameters from a menu. In yet another non-limiting example, the therapist or other health care professional may program a protocol with help of a graphical interface presenting therapeutic protocol “primitives.” The user may define a therapeutic protocol by selecting a group of graphical primitives representing cells, valves, sensors, and the like, and link them together to form a complete protocol. As one non-limiting example, a final graphical presentation of a therapeutic protocol may be presented on an output device as a flow-chart listing steps, cell inflation order, time between cell inflations/deflations, cell pressure hold parameters, and/or fluid flow rate or pressure thresholds.
In addition to storing protocols, the controller 145 may also record sensor readings obtained during a particular therapy session. Sensor readings may include, without limitation, cell pressures, cell volumes, cell inflation data, and/or air or vacuum air flow values. The controller may also record patient related data such as blood pressure or blood oxygen saturation levels measured during a therapeutic session, as well as a date and time for the session. The controller may also record therapy notes entered by the user.
Although not illustrated in FIG. 3, controller 145 may also include a number of communications interfaces to either a network or a wireless device such as a cell phone, an iPad, a local area network device, and/or a wide area network device. Such communication interfaces may permit the controller to be monitored remotely by a clinician to obtain performance data or patient compliance data. Such communication interfaces may also permit a remote clinician to program the controller. As one non-limiting example, a physician or technologist may program a new therapeutic protocol in the controller. Alternatively, the care provider may transmit parameter data for a preprogrammed therapeutic protocol, or select a pre-programmed therapeutic protocol in the controller. In one embodiment, a cell phone may have an application that may bring up a user-friendly programming interface to permit ease of reprogramming. Alternatively, a remote computer may display a web-enabled display for programming, data assessment, and/or analysis.
The controller may further comprise storage devices that may be fixed (such as a hard drive) or removable, such as a removable disc, a removable card, and a removable memory chip.
A number of possible examples of therapeutic protocols are illustrated schematically in FIGS. 4-9.
An embodiment of a sequential gradient protocol is illustrated in FIG. 4, in which the cells A-E may be arranged distally to proximally on a limb, such as a leg. Initially, all cells A-E may be deflated, FIG. 4a. Subsequently, each cell in an ordered sequence may be inflated to a set pressure in an inflation cycle. Thus, cell A may be inflated to a first pressure such as to 60 mmHg, as in FIG. 4b, cell B may be inflated to a second pressure (e.g. 50 mmHg) in FIG. 4c, cell C may be subsequently inflated to a lower pressure, such as to 40 mmHg, (FIG. 4d) followed by cell D (to 30 mmHg, FIG. 4e) and cell E (to 20 mmHg, FIG. 4f). It may be understood that a successive cell may begin inflation immediately after its preceding cell has been inflated, or there may be a phase delay after a preceding cell has been inflated before the successive cell begins to inflate. In the inflation sequence, the phase delays for each cell may be the same, or different cells may have different phase delays associated with them. The therapeutic protocol may include such phase delay information as part of its parameters. After the entire set of cells has been inflated, they may be simultaneously deflated as illustrated in FIG. 4g. The protocol may be repeated as necessary with some rest period between inflation cycles. The cell pressures may be essentially repeated from one cycle to another. Alternatively, a cycle may cause the cells to inflate to a different pressure gradient, such as 70, 60, 50, 40, and 30 mmHg for cells A-E, respectively. It may be appreciated that the final inflation pressure of each cell may differ from all the remaining cells, or all cells may reach essentially the same pressure.
Another embodiment of a sequential inflation cycle is illustrated in FIG. 5. FIG. 5a may represent the inflation state of a group of cells after a gradient inflation protocol, as illustrated in FIG. 4f. Thereafter, the pressure in all the cells may be reduced by some amount; the resulting cell pressure in each cell may be less than at the start of the protocol, but all the cells may retain some pressure, as in FIG. 5b. Thereafter, each cell in succession may be re-pressurized (FIGS. 5c-5f) until all the cells are re-pressurized to their initial state at the beginning of the protocol, FIG. 5g. Cells may be deflated simultaneously or in an ordered sequence. In the case of sequential deflation, it may be understood that a successive cell may begin deflation immediately after its preceding cell has been deflated, or there may be a phase delay after a preceding cell has been deflated before the successive cell begins to deflate. In the deflation sequence, the phase delays for each cell may be the same, or different cells may have different phase delays associated with them. The therapeutic protocol may include such phase delay information as part of its parameters.
FIG. 6 illustrates another embodiment of a rapid toggle protocol. Initially, all the cells may be deflated in as FIG. 6a. Thereafter, cell A may begin inflating to some pressure, FIG. 6b. Cell A may continue to inflate, but cell B may begin to inflate after cell A reaches a threshold pressure (FIG. 6c). As illustrated in FIG. 6d, cell A may continue pressurizing to some final value. Meanwhile, as cell B pressurizes past a threshold value, cell C may then begin to inflate. The sequence may continue (FIGS. 6e-6g), in which a cell begins to inflate when a preceding cell inflates to a particular pressure threshold. It is understood that the thresholds for all the cells may be essentially the same. Alternatively, one or more cells may have different thresholds. In one embodiment, the thresholds may be programmed by a therapist operating the compression therapy device. In another embodiment, a user or patient receiving the compression therapy may program the thresholds. In addition, although FIG. 6 illustrates that the final pressures attained by all the cells are effectively identical, it may be appreciated that the final pressures attained by the cells may form a pressure gradient as illustrated in FIG. 4f. 
FIG. 7 illustrates yet another therapeutic protocol. In this protocol, an even number of cells may be employed. When the protocol begins, all the cells may be in a deflated state (FIG. 7a). Thereafter, a pair of cells, such as cells A and D may inflate simultaneously (FIG. 7b) until they reach their final pressures. The next cells, B and E, may then be inflated (FIG. 7c) until they reach their final pressures. Thereafter, the final cells, D and F may be inflated (FIG. 7d). It may be appreciated that cells B and E may begin to inflate before cells A and D finish inflating, and similarly cells C and F may begin their inflation cycle before cells B and E attain their final pressures. After the protocol is completed (FIG. 7d) all the cells may deflate simultaneously, or in some other order as required.
In another example of a therapeutic protocol, FIG. 8 illustrates what may be termed a “milking” protocol. FIGS. 8a-8e illustrate a gradient inflation protocol similar to that illustrated in FIGS. 4b-4f. Instead of deflating all cells as in FIG. 4g, the protocol may allow cells A, B, and C to retain their pressures, while only cells D and E partially deflate to lower pressures (FIG. 8f). Thereafter, in sequence, cell D (FIG. 8g) and E (FIG. 8h) may re-inflate to their previous pressures (FIG. 8h). The protocol may then repeat the steps illustrated in FIGS. 8f-h. 
In yet another example of a therapeutic protocol, the cells may inflate in a “wave” motion (FIG. 9). In one simple protocol, the cells may be partially inflated to some pressure (FIG. 9a). Although all cells are represented as having about the same pressure, it may be appreciated that the cells may be initially inflated into a gradient as illustrated in FIG. 8e. Thereafter, one cell at a time may be increased in pressure, Cell A (distal) through cell E (proximal) according to the sequence in FIGS. 9b-9f. Although the protocol illustrated in FIG. 9 illustrates a single cell inflating at a time, it is understood that a more effective therapy may include inflating a more proximal cell while its neighboring more distal cell is inflated, and then deflating the distal neighbor after the proximal cell is fully inflated. As an example, after cell A is fully inflated (FIG. 9b), cell B may be inflated. Thereafter, after cell B has been inflated, cell A may be deflated back to its prior pressure resulting in the state illustrated in FIG. 9c. 
It may be understood that the protocols illustrated in FIGS. 4-9 represent a few examples of possible inflation/deflation protocols. Other protocols may include more or fewer cells, and a variety of sequences of inflation and deflation.
More complex therapeutic protocols may include feedback from the individual cells to the controller 145 before, during, and/or after inflation or deflation. In one non-limiting example, the controller 145 may monitor the pressure of a cell after it has stopped inflating or deflating to assure the cell pressure is maintained while the cell is in a hold state (neither inflating nor deflating). Thus, the pressure measured by a pressure sensor 155a associated with a first cell may change due to effects on the tissue brought about by the inflation of a neighboring cell. The controller 145 may respond to the change in pressure in the first cell by activating its associated valve 125a to adjust the first cell pressure to a desired value.
In another protocol, the controller 145 may retain or have access to logs associated with the patient's medical history over time. Such historical data may be used by the controller 145 or a health care professional to modify a protocol to account for a change in the patient's status. As one non-limiting example, the controller 145 may alter a patient's usual therapeutic protocol if the long term patient status—as recorded in the patient logs—indicates an improvement over time. Alternatively, if the patient does not improve, the controller 145 may alter the usual patient's protocol in an attempt to improve its effectiveness. A health care provider may also be presented with such long term status information along with a recommendation for a protocol change by the controller 145. The health care provider may then accept the recommendation by the controller 145, or may make additional modifications.
In one non-limiting embodiment, the pneumatic compression device may be portable. In an embodiment, the pneumatic compression device may include a user interface that enables the user to interact with the controller 145. For example, the user interface may include a display and one or more input devices, such as a keypad, a keyboard, a mouse, a trackball, a light source and light sensor, a touch screen interface and/or the like. The one or more input devices may be used to provide information to the controller 145, which may use the information to determine how to control the fill valve 120, exhaust valve 130, and/or the cell valves 125a-N.
As disclosed above, a therapeutic protocol may specify a sequence of inflation times and pressures for a number of inflatable cells comprising an appliance used with a compression therapy device. The pressure desired in each cell during a protocol may be determined by a health care provider in order to optimize fluid flow through the patient's tissues. It may be appreciated that a compression therapy device may be so designed as to meet, in a repeatable fashion, the set target pressures for each cell during a therapeutic protocol.
Cell pressures may be monitored in a number of ways. In one non-limiting embodiment, cell pressure may be calculated by a fluid flow rate, a time for fluid flow, and the volume of the cell. In a second non-limiting embodiment, cell pressure may be inferred by a pressure sensor associated with a fill manifold while a cell is in fluid communication with the fill manifold. Such a method may be based on pressure equalization between the fill manifold and the cell while the cell is being filled by the fluid. In a third non-limiting embodiment, a pressure sensor may measure directly a pressure associated with a cell.
Cell pressures may be monitored during a therapeutic protocol while the cells are inflated or deflated. The relationship between the pressure of a cell during inflation (a dynamic pressure measurement) and the final pressure required by a therapeutic protocol after the cell has been pressurized to a stable pressure (a static pressure measurement) may be determined by a calibration method. In one non-limiting embodiment, the calibration method may include pre-calibrating the appliance and each of the independently inflatable cells therein at a fabrication or supply location prior to providing the appliance to the patient. A second non-limiting embodiment may include an auto-calibration function built into the pneumatic compression device for use with any appliance provided for the compression therapy.
FIG. 10 presents a flow chart of one non-limiting embodiment of a method to auto-calibrate a compression therapy device. A compression therapy device may be provided 1010 for auto-calibration. Such a device may comprise an appliance or inflatable compression sleeve comprising at least one inflatable cell. The device may further comprise a fluid source having a source output and configured to introduce a fluid into the inflatable cell, a fill manifold configurable to be in fluid communication with the fluid source and the inflatable cell, a cell valve disposed between the inflatable cell and the fill manifold, a pressure sensor, and a controller. The controller may be configured to receive pressure sensor data from the pressure sensor and to control one or more actions of the cell valve. The controller may further comprise at least one processor device, at least one non-transitory and at least one memory storage device.
The inflatable cell may receive 1020 some portion of the inflation fluid from the fluid source. The pressure sensor may determine a pressure associated with a dynamic pressure of the cell while the cell is filling. The controller may receive 1030 the dynamic pressure sensor data provided by the pressure sensor at least once during the cell filling cycle. After the cell has received the portion of inflation fluid, and the inflation cycle has ceased, the pressure sensor may determine a pressure associated with a static pressure of the cell and the controller may receive 1040 the static pressure sensor data provided by the pressure sensor. The controller may calculate 1050 a difference between the dynamic pressure sensor data and the static pressure data. The controller may calibrate 1060 a dynamic pressure sensor target value based, at least in part, on one or more of a static pressure sensor target value, the dynamic pressure sensor data, the static pressure sensor data, and the pressure difference. The static pressure sensor target value may represent a desired inflatable cell pressure as defined by a therapeutic protocol. The dynamic pressure sensor target value may be used by the controller to determine when a dynamically inflated cell may have achieved a pressure close to the desired static pressure target.
The dynamic pressure sensor target value may be stored in at least one non-transitory memory storage device of the controller. Additionally, the controller may provide the dynamic pressure sensor target value to a device in communication with the controller. Non-limiting examples of such devices may include a remote computer terminal, a smart phone, a tablet computer, a server, or other computing device. It may be understood that the calibration method, as disclosed above, may be used to determine a dynamic pressure sensor target value associated with more than one static pressure target values for the cell. Thus, a first dynamic pressure sensor target value for a cell may be determined for a static pressure of about 5.3 kPa, and a second dynamic pressure sensor target value for the cell may be determine for a static pressure of about 8 kPa. Each of these dynamic pressure sensor target values may be stored in non-transitory memory or transmitted to devices in communication with the controller. In one non-limiting example, the controller may store a static pressure target value and its related dynamic pressure target value in a table. The values in the table may be used during non-calibration (for example, therapeutic) uses of the therapeutic device to determine a dynamic pressure corresponding to a target therapeutic protocol pressure for a cell.
The controller may also provide a warning indicator that is activated when a difference value exceeds a threshold value. The warning indicator may be useful to monitor the function of the fluid source, or the state of the valve and/or cell. Over time, the performance of the fluid source may degrade, and provide less fluid than when the source was new. Additionally, the warning indicator may be used to indicate a malfunctioning or plugged valve or manifold. The warning indicator may further indicate a degradation of the cell construction, such as the appearance of leaks in the cell, or the cell material becoming stretched due to over-use. The controller may retain calibration data—including static pressure values, dynamic pressure values, pressure differences, and calculated dynamic pressure sensor target values—over time in a calibration log. The controller may review the data in such a calibration log at each use or additional calibration. If the pressure difference value exceeds a threshold, the controller may notify a user that the value of the calculated dynamic pressure sensor target value may be in question. The user, upon receiving the warning indicator, may then choose to change or service the fluid source, replace valves, or replace the appliance. The warning indicator may include any type of indicator, including, but not limited to, an optical indicator, an audible indicator, a text indicator displayed on a readable output device (such as a computer monitor, laptop display, or text message to a smart phone) in data communication with the controller, and a graphical indicator on a viewable output device in data communication with the controller.
Refinements of the basic auto-calibration method disclosed above may also be considered. For example, the auto-calibration method may begin as disclosed above. A fluid source may deliver a first portion of fluid to a cell, the controller may receive a first dynamic pressure measurement, the source may stop delivering the fluid to the cell, and the controller may receive a first static pressure measurement. The controller may determine a first difference value and calculate a first dynamic target pressure value corresponding to a static target pressure value. The controller may cause the fluid source to deliver a second portion of fluid to the cell, the controller may receive a second dynamic pressure measurement, the source may stop delivering the fluid to the cell, and the controller may receive a second static pressure measurement. The controller may determine a second difference value and calculate a second dynamic pressure target value corresponding to the static target pressure value.
It may be appreciated that the compression device may run any number of series of such calibration steps, with a cell partially inflated at each series. In one non-limiting embodiment, the controller may store in non-transitory memory each of the dynamic pressure target values calculated for a specific static pressure target value. Additionally, the controller may calculate and store in non-transitory memory a final dynamic pressure sensor target value based at least in part, on one or more of any of the static pressure values, dynamic pressure values, differences, dynamic pressure target values, and static pressure target value obtained during one or more calibration steps. In one non-limiting example, the final dynamic pressure sensor target value may be calculated as an average of the multiple calculated dynamic pressure target values. In another non-limiting example, the final dynamic pressure sensor target value may be calculated as a weighted average of the multiple calculated dynamic pressure target values.
Although the non-limiting method for calibration disclosed above is described in terms of a single inflatable cell, similar methods may be used to calibrate dynamic pressure sensor target values for each of a plurality of inflatable cells that may comprise the inflatable compression article or sleeve. The multiple cells may be independently inflatable, and may be inflated sequentially, concurrently, or one or more cells may be inflated starting at a time after one or more additional cells have begun to inflate. Each cell of the plurality of cells may be configurable to be in fluid communication with the fill manifold, and a separate cell valve may be associated with each of the plurality of cells. The cell valves may be disposed between their respective cells and the fill manifold, and the actions of each valve may be independently controlled by the controller.
It may be understood that each independently inflatable cell may be independently calibrated. One cell may be calibrated while one or more additional cells may be inflated, deflated, or maintained at a constant pressure. For example, the fluid source may introduce a portion of fluid into a first cell, and the fluid source may introduce a second portion of fluid into a second cell. Alternatively, a fluid source may introduce a second portion of fluid into a second cell while a first cell no longer receives a first portion of fluid for inflation. In still another embodiment, a fluid source may introduce a second portion of fluid into a second cell while a pressure sensor measures a dynamic sensor pressure value or a static pressure value of a first cell, or transmits such data to the controller.
Although a single measurement of the dynamic pressure and static pressure are disclosed above, it may be understood that multiple consecutive measurements may be made to obtain greater statistical accuracy. For example, successively measured static pressure values may be averaged together and successively measured dynamic pressure values may be averaged together. Averages, measures of variability of the pressure measurements, and additional statistical metrics may be calculated for the dynamic pressure value and the static pressure value.
FIGS. 11A-11C depict some non-limiting examples of compression therapy systems to which the auto-calibration method may apply. It should be noted that elements having the same number in each of FIGS. 11A-11C have the same function although the elements may have different structures depending on the configuration of the system depicted.
FIG. 11A depicts one embodiment of a system for providing compression therapy to a patient. The system includes a fluid source 1105, which may be any type of compression or pumping device. The fluid source 1105 may deliver the fluid into a fill manifold 1141 through a source outlet, and the source outlet may be isolated from the fill manifold by means of a fill valve 1120. The fill manifold 1141 may deliver the fluid to one or more independently inflatable cells 1160a and 1160b. Each cell 1160a, 1160b may be isolated from the manifold by means of a cell valve 1125a and 1125b, in which one cell valve is associated with one cell (for example, cell valve 1125a may be associated with cell 1160a, and cell valve 1125b may be associated with cell 1160b). When the fluid source 1105 delivers fluid into the fill manifold 1141, pressure within the fill manifold may be measured by a pressure sensor 1165. In one non-limiting example, the fill manifold 1141 may also be configured to deliver fluid to a low pressure source such as to the atmosphere or a source of vacuum. The fill manifold 1141 may be isolated from the low pressure source by means of an exhaust valve 1170. In the configuration depicted in FIG. 11A, cells 1160a,b may be inflated when fill valve 1120 is configured to permit the fluid source 1105 to source fluid into the fill manifold 1141 while the exhaust valve 1170 is closed and the one or more cell valves 1125a,b are open. Fluid in cells 1160a,b may be removed by closing fill valve 1120 and opening exhaust valve 1170 while cell valve 1125a,b are open. Controller 1145 may be configured to control the fill valve 1120, exhaust valve 1170, cell valves 1160a,b, and the fluid source 1105.
Cell 1160a may be calibrated in the configuration depicted in FIG. 11A by the following non-limiting method. A patient may don a compression appliance comprising one or more individually inflatable cells 1160a,b over a body part to receive the compression therapy. Controller 1145 may cause the fluid source 1105 to provide fluid into the fill manifold 1141 by enabling the fluid source over a control line 1106, opening the fill valve 1120, and closing exhaust valve 1170. Cell 1160a may be placed in fluid connection with the fill manifold 1141 by the controller 1145 opening cell valve 1125a. While cell 1160a is inflated, controller 1145 may receive dynamic pressure data from pressure sensor 1165. The dynamic pressure data may represent the dynamic pressure within the fill manifold 1141, and therefore, by extension, the dynamic pressure of the cell 1160a in fluid communication therewith. The controller 1145 may cause the source of the fluid 1105 to cease emitting the fluid into the fill manifold 1141 by disabling the source via a control signal over the control line 1106. The controller 1145 may receive a static pressure value from the pressure sensor 1165. The static pressure data may represent the static pressure within the fill manifold 1141, and therefore, by extension, the static pressure of the cell 1160a in fluid communication therewith. The controller may then calculate a difference between the dynamic pressure and the static pressure, thereby calibrating a dynamic target pressure value that may be related to a desired static pressure value. Additionally, as disclosed above, the controller 1145 may cause the fluid source 1105 to emit additional fluid into the fill manifold 1141 and receive successive measurements of the dynamic and static pressures of the cell 1160a, thereby providing redundancy in the calibration of the dynamic target fill pressure.
In another non-limiting example, it may be desirable to isolate the fluid source 1105 from the fill manifold 1141 while static pressure measurements are made. The isolation may be useful if it is determined that the fluid source 1105 leaks when the fluid source is disabled (by means of a command issued over control line 1106 from controller 1145). Under such conditions, the fluid source 1105 may be disabled, and the fill valve 1120 may be placed in a state to isolate the fluid source from the fill manifold 1141 while the controller 1145 receives the static pressure measurement from the pressure sensor 1165.
It may be appreciated that the method for calibrating a dynamic sensor target pressure for one cell (such as 1160a) may be extended to any number of cells (such as 1160b) that are incorporated into the compression therapy appliance.
FIG. 11B depicts another non-limiting example of a compression therapy system that may use the calibration method disclosed above. The system depicted in FIG. 11B differs from that depicted in FIG. 11A in that fill valve 1120 is a three-way valve capable of placing the output of the fluid source 1105 in fluid communication with the fill manifold 1141, isolating the fluid source output, and placing the output of the fluid source in fluid communication with a fluid receiver 1180. The states of the fill valve 1120—source-to-manifold, source isolation, and source-to-receiver—may be controlled by the controller 1145. The fluid receiver 1180 may comprise any device or environment capable of receiving the fluid emitted by the fluid source 1105. Non-limiting examples of the fluid receiver 1180 may include the atmosphere and a source of a vacuum. For a system having a configuration depicted by FIG. 11B, the fluid source 1105 may remain active while the controller 1145 receives the static pressure measurement from the pressure sensor 1165. For example, the fill valve 1120 may be placed in a state to direct the fluid flow into the fluid receiver 1180, thereby isolating the fill manifold 1141 from the fluid source 1105 during the static pressure measurement.
FIG. 11C depicts yet another embodiment of a compression therapy system that may be calibrated according to the method disclosed above. In the system depicted in FIG. 11C, there is no pressure sensor associated with the fill manifold 1141. Instead, each cell 1160a and 1160b has a pressure sensor (1155a and 1155b, respectively) configured to measure a pressure within the cell. The controller 1145 may be configured to receive dynamic pressure data and static pressure data from pressure sensors 1155a and 1155b. The output of the fluid source 1105 may be placed in fluid communication with the fill manifold 1141 via fill valve 1120 under control of controller 1145. The fluid may enter the fill manifold 1141 and be admitted into a cell (for example 1160a) by the action of an associated cell valve (for example 1125a) also under control of the controller 1145. While cell valve 1125a is open, the controller 1145 may receive dynamic pressure sensor data from pressure sensor 1155a associated with the cell 1160a. The receipt, by the cell 1160a, of the fluid may be halted by the controller 1145 configuring cell valve 1125a to close. The controller 1145 may receive static pressure sensor data from pressure sensor 1155a while cell valve 1125a is in the closed configuration. The controller 1145 may place the cell valve 1125a into an open configuration, thereby permitting fluid to enter the cell 1160a from the fill manifold 1141.
The present disclosure is not to be limited in terms of the particular embodiments described in this application, which are intended as illustrations of various aspects. Many modifications and variations can be made without departing from its spirit and scope, as will be apparent to those skilled in the art. Functionally equivalent methods and apparatuses within the scope of the disclosure, in addition to those enumerated herein, will be apparent to those skilled in the art from the foregoing descriptions. Such modifications and variations are intended to fall within the scope of the appended claims. The present disclosure is to be limited only by the terms of the appended claims, along with the full scope of equivalents to which such claims are entitled. It is to be understood that this disclosure is not limited to particular methods, reagents, compounds, compositions or biological systems, which can, of course, vary. It is also to be understood that the terminology used herein is for the purpose of describing particular embodiments only, and is not intended to be limiting.
With respect to the use of substantially any plural and/or singular terms herein, those having skill in the art can translate from the plural to the singular and/or from the singular to the plural as is appropriate to the context and/or application. The various singular/plural permutations may be expressly set forth herein for sake of clarity.
It will be understood by those within the art that, in general, terms used herein, and especially in the appended claims (e.g., bodies of the appended claims) are generally intended as “open” terms (e.g., the term “including” should be interpreted as “including but not limited to,” the term “having” should be interpreted as “having at least,” the term “includes” should be interpreted as “includes but is not limited to,” etc.). It will be further understood by those within the art that if a specific number of an introduced claim recitation is intended, such an intent will be explicitly recited in the claim, and in the absence of such recitation no such intent is present. For example, as an aid to understanding, the following appended claims may contain usage of the introductory phrases “at least one” and “one or more” to introduce claim recitations. However, the use of such phrases should not be construed to imply that the introduction of a claim recitation by the indefinite articles “a” or “an” limits any particular claim containing such introduced claim recitation to embodiments containing only one such recitation, even when the same claim includes the introductory phrases “one or more” or “at least one” and indefinite articles such as “a” or “an” (e.g., “a” and/or “an” should be interpreted to mean “at least one” or “one or more”); the same holds true for the use of definite articles used to introduce claim recitations. In addition, even if a specific number of an introduced claim recitation is explicitly recited, those skilled in the art will recognize that such recitation should be interpreted to mean at least the recited number (e.g., the bare recitation of “two recitations,” without other modifiers, means at least two recitations, or two or more recitations). Furthermore, in those instances where a convention analogous to “at least one of A, B, and C, etc.” is used, in general such a construction is intended in the sense one having skill in the art would understand the convention (e.g., “a system having at least one of A, B, and C” would include but not be limited to systems that have A alone, B alone, C alone, A and B together, A and C together, B and C together, and/or A, B, and C together, etc.). In those instances where a convention analogous to “at least one of A, B, or C, etc.” is used, in general such a construction is intended in the sense one having skill in the art would understand the convention (e.g., “a system having at least one of A, B, or C” would include but not be limited to systems that have A alone, B alone, C alone, A and B together, A and C together, B and C together, and/or A, B, and C together, etc.). It will be further understood by those within the art that virtually any disjunctive word and/or phrase presenting two or more alternative terms, whether in the description, claims, or drawings, should be understood to contemplate the possibilities of including one of the terms, either of the terms, or both terms. For example, the phrase “A or B” will be understood to include the possibilities of “A” or “B” or “A and B.”
As will also be understood by one skilled in the art all language such as “up to,” “at least,” and the like include the number recited and refer to ranges which can be subsequently broken down into sub-ranges as discussed above. Finally, as will be understood by one skilled in the art, a range includes each individual member. Thus, for example, a group having 1-3 cells refers to groups having 1, 2, or 3 cells. Similarly, a group having 1-5 cells refers to groups having 1, 2, 3, 4, or 5 cells, and so forth.
Various of the above-disclosed and other features and functions, or alternatives thereof, may be combined into many other different systems or applications. Various presently unforeseen or unanticipated alternatives, modifications, variations, or improvements therein may be subsequently made by those skilled in the art, each of which is also intended to be encompassed by the disclosed embodiments.

## Claims

1. A method of auto-calibrating a pneumatic compression therapy device, the method comprising:
providing a compression therapy device comprising:
an inflatable compression sleeve comprising an inflatable cell,
a fill manifold configurable to be in fluid communication with the inflatable cell,
a fluid source having a source output configured to introduce a fluid into the inflatable cell via the fill manifold,
a cell valve disposed between the inflatable cell and the fill manifold,
a pressure sensor, and
a controller configured to receive pressure sensor data from the pressure sensor, and to control one or more actions of the cell valve and the fluid source, the controller comprising at least one processor device and at least one non-transitory memory storage device;

receiving, by the cell, a first portion of fluid from the fluid source and receiving, by the controller, dynamic pressure sensor data related to a dynamic pressure within the cell;
receiving, by the controller, static pressure sensor data related to a static pressure within the cell;
calculating, by the controller, a pressure difference between the dynamic pressure sensor data and the static pressure sensor data; and
calibrating, by the controller, a dynamic pressure sensor target value based, at least in part, on one or more of a static pressure sensor target value, the dynamic pressure sensor data, the static pressure sensor data, and the pressure difference.

2. The method of claim 1, wherein the pressure sensor is configured to measure a pressure within the fill manifold.

3. The method of claim 1, wherein the pressure sensor is configured to measure a pressure within the cell.

4. The method of claim 1, wherein receiving, by the cell, a first portion of fluid from the fluid source comprises:
enabling, by the controller, the fluid source to emit the fluid into the fill manifold; and
configuring, by the controller, the valve to place the cell in fluid communication with the fill manifold.

5. The method of claim 1, wherein receiving, by the controller, static pressure sensor data related to a static pressure within the cell comprises:
causing, by the controller, the fluid source to cease emitting a fluid into the fill manifold; and
receiving, by the controller, static pressure sensor data related to a static pressure within the cell.

6. The method of claim 1, wherein receiving, by the controller, static pressure sensor data related to a static pressure within the cell comprises:
configuring, by the controller, the valve to fluidly isolate the cell from the fill manifold; and
receiving, by the controller, static pressure sensor data related to a static pressure within the cell.

7. The method of claim 1, wherein receiving, by the controller, static pressure sensor data related to a static pressure within the cell comprises:
isolating the fill manifold from the output of the fluid source;
placing, by the controller, the output of the fluid source in fluid communication with a receiver of fluid; and
receiving, by the controller, static pressure sensor data related to a static pressure within the cell.

8. The method of claim 7, wherein the receiver of fluid is the atmosphere.

9. The method of claim 7, wherein the receiver of fluid is a source of a vacuum.

10. The method of claim 1, further comprising storing, in the at least one non-transitory memory storage device, the dynamic pressure sensor target value.

11. The method of claim 1, further comprising:
receiving, by the cell, at least a second portion of fluid from the fluid source and receiving, by the controller, at least second dynamic pressure sensor data related to a second dynamic pressure within the cell;
receiving, by the controller, at least second static pressure sensor data;
calculating, by the controller, at least a second pressure difference between the at least second dynamic pressure sensor data and the at least second static pressure sensor data; and
calibrating, by the controller, at least a second dynamic pressure sensor target value based, at least in part, on one or more of the static pressure sensor target value, the at least second dynamic pressure sensor data, the at least second static pressure sensor data, and the at least second pressure difference.

12. The method of claim 11, further comprising storing, in the at least one non-transitory memory storage device, the at least second dynamic pressure sensor target value.

13. The method of claim 12, further comprising:
calculating a final dynamic pressure sensor target value based, at least in part, on one or more of the static pressure sensor target value, the dynamic pressure sensor data, the static pressure sensor data, the pressure difference, the at least second dynamic pressure sensor data, the at least second static pressure sensor data, and the at least second pressure difference; and
storing, in the at least one non-transitory memory storage device, the final dynamic pressure sensor target value.

14. The method of claim 1, wherein:
the inflatable compression sleeve comprises at least a second independently inflatable cell in fluid communication with the fluid source;
the compression therapy device further comprises at least a second cell valve disposed between the at least second inflatable cell and the fill manifold; and
the controller is configured to control one or more actions of the at least second cell valve.

15. The method of claim 14, further comprising at least a second pressure sensor, wherein the controller is configured to receive pressure sensor data from the at least second pressure sensor.

16. The method of claim 14, wherein receiving, by the cell, a portion of fluid from the fluid source comprises:
receiving, by the cell, a first portion of fluid from the fluid source; and
receiving, by the at least second cell, a second portion of fluid from the fluid source.

17. The method of claim 14, wherein receiving, by the controller, dynamic pressure sensor data related to a dynamic pressure within the cell comprises:
receiving, by the controller, dynamic pressure sensor data related to a dynamic pressure within the cell; and
receiving, by the at least second cell, a second portion of fluid from the fluid source.

18. The method of claim 14, wherein receiving, by the controller, static pressure sensor data related to a static pressure within the cell comprises:
receiving, by the controller, static pressure sensor data related to a static pressure within the cell; and
receiving, by the at least second cell, a second portion of fluid from the fluid source.

19. The method of claim 1, further comprising providing, by the controller, an indicator if a value of the difference exceeds a difference threshold.

20. The method of claim 19, wherein the indicator comprises one or more of an optical indicator, an audible indicator, a text indicator displayed on a readable output device in data communication with the controller, and a graphical indicator on a viewable output device in data communication with the controller.