Patent Grant
10670005
Certain embodiments described herein relate generally to the field of fluid transfer. More particularly, some embodiments described herein relate to fluid transfer having a relatively small amount or no amount of impurities introduced to the fluid being transferred and/or relatively little or no damage to the fluid being transferred.
Understanding that drawings depict only typical embodiments of the invention and are not therefore to be considered to be limiting of its scope, the invention will be described and explained with additional specificity and detail through the use of the accompanying drawings. The drawings are listed below.
Elements numbered in the drawings include:
This disclosure relates to a pump apparatus and related methods and systems. Various views of an illustrative embodiment of a pump are provided in
It is noted that similar or duplicate features are referred to with a unique alphanumeric designation. Certain features common to various embodiments may be designated with a primed numeral in some figures. In either case, duplicate elements will not be described in further detail to the extent their performance is similar to the embodiments previously described. For example, the chamber diaphragms illustrated in
Certain diaphragm pumps can have application as a single use disposable medical blood pump. For example, a pump can be used to move blood through an extracorporeal circuit. An advantage of pumping blood with certain pumps as described herein is that, in various embodiments, a relatively small amount, a minimal amount, a negligible amount, or even no amount of synthetic pump material particles is released into the flow of blood that is caused by rubbing, sliding, or straining of materials typically used in other types of pump mechanisms to energize fluid flow. Synthetic particulates generated by certain pumps that move fluids to and from a patient have the potential to create adverse health effects including embolisms or microembolisms in the vascular system. Further, the toxicity of materials introduced or generated by such pumps can be delivered to the patient and can be left residing in the vascular system of the patient.
Certain embodiments of a pneumatically actuated diaphragm pump can be advantageous because of the inherent control that may be achieved for delivering fluids within physiologically acceptable pressure ranges. For example, if a blockage occurs in the process fluid lines connected to an embodiment of a pump, some embodiments of the pump may only generate pressure in the process fluid at a level that is at or near those of the motive fluid pressures that are driving the pump. In the case of pumping blood, such a pump can reduce or eliminate excessive pressures or high vacuums in the fluid lines that can potentially damage blood or cause air embolisms by out-gassing the blood under high suction levels.
Some embodiments of pumping systems that may be used in single-use disposable medical applications can advantageously be comprised of a removable and/or separable disposable pumping component and a reusable pump control system. The disposable pumping component can be packaged and pre-sterilized for use in a medical application related to an individual patient. In some embodiments, the disposable pumping component can be coupled in operative association with the reusable pump control system for a single patient during a medical application, and then removed and disposed.
In some embodiments, the reusable pump control system can be isolated from the flow of biological fluids and may selectively control and operate a plurality of disposable pumping components—one or more for each of a multiple number of patients or applications, in some instances—without being sterilized between uses. The removable/disposable pumping component may include pump chambers, inlet and outlet valves, inlet and outlet lines, and other components which are in contact with the blood or biological fluid. In some embodiments, the removable/disposable pumping component comprises a double diaphragm pump. As discussed below, in some embodiments, the double diaphragm pump can be configured and designed with a plurality of pump chambers, flow paths, valves, etc. that are specifically designed for a particular application. For example, some embodiments of double diaphragm pumps can be configured for use in such medical applications as cardiopulmonary bypass, surgical perfusion support, heart assist, and hemodialysis, as further described below.
Various embodiments of double diaphragm pumps also enable fluids to be transferred in a wide variety of other fields. For example, such pumps can be used in the transfer of high purity process fluids. Some embodiments of double diaphragm pumps can be advantageous in transferring high purity process fluids, as the pump avoids, minimizes, or otherwise reduces the introduction or generation of contaminants or particulate matter that can be transferred downstream by reducing or eliminating rubbing and sliding components within the pump. Downstream transfer of contaminants or particulate matter may effect the desired outcome of using the high purity process fluid. Also for shear sensitive fluids, some pumps can be operated to gently move fluid from a source to a destination.
Some of the components which comprise the valves and the pump chambers are shown in
Other means of sealing the valves and chambers can also be used, including adhesives, heat bonding, and welding. In certain embodiments, the diaphragms 140a, b and 150a, b and pump body 110 can be fabricated with similar materials that will bond together when heated. In some embodiments, fluorinated ethylene propylene (FEP) materials can be used for both of the diaphragms 140a, b, 150a, b and the pump body 110, and heat can be used to bond the diaphragms to the body. Other heat sealable materials that can be used for both of the diaphragms 140a, b, 150a, b and the pump body 110 include polyvinylchloride (PVC), polyurethane (PU), and polypropylene (PP). In some embodiments, an adhesive, such as Scotch Weld Acrylic DP-8005 adhesive manufactured by 3M—Industrial Business, Industrial Adhesives and Tapes Division, St. Paul, Minn., is used to attach the chamber plate 160 assembly posts 169a-d and air bosses 162a, b (see, e.g.,
In certain embodiments, the preformed actuation regions of chamber diaphragm 140a include first pump chamber region 141a and second pump chamber region 141b. The preformed actuation regions of valve diaphragm 150a include first inlet valve region 151i, first outlet valve region 151o, second inlet valve region 152i, and second outlet valve region 152o. Each media 140a, b and 150a, b can also have holes 142a-f (see
With reference to
The flow paths of the process fluid in some embodiments of the double diaphragm pump 100 are described below with reference to
In certain embodiments, different regions of the chamber diaphragms 140a and 140b and valve diaphragms 150a and 150b can be moved by applying pressure of the motive fluid which is greater than the pressure of the process fluid at the process fluid destination, receiver, or return 239 (see
The amount of pressure or vacuum applied can vary significantly depending on the intended use of the pump 100. For example, in some embodiments, the double diaphragm pump 100 delivers a fluid at a pressure in a range of between about 0 mmHg (millimeters of mercury) and about 1500 mmHg, between about 50 mmHg and about 500 mmHg, between about 50 mmHg and about 700 mmHg, or between about 80 mmHg and about 500 mmHg. Similarly, in some embodiments, the double diaphragm pump 100 may receive fluid from a source or generate suction in a range of between about −500 mmHg and about 0 mmHg, between about −250 mmHg and about 0 mmHg, between about −120 mmHg and about 0 mmHg, or at an amount that is less than the fluid pressure at the process fluid source 238.
In some embodiments of the double diaphragm pump 100 that are configured to be used as a blood pump, blood is received into the pump and delivered from the pump in a range between about −250 mmHg and about 500 mmHg. While blood pressure in a patient vasculature system is typically in a range of 0 mmHg to 200 mmHg, depending on the location of blood in the system and condition of the patient, the blood pump 100 may operate at higher pressures and with vacuum assisted suction to overcome pressure losses in the extracorporeal circuit. These pressure losses can occur as blood flows through cannulae, connection lines, blood treatment devices, filters, reservoirs, and connectors. The blood pump may be operated to cause the blood to be drawn from and return to the patient vascular system at safe levels. These safe levels of blood pressure at the fluid source 238 may be above 0 mmHg and the blood pressure at the fluid return 239 may be below 150 mmHg. The blood may also be drawn into the pump without a vacuum source supplied to the pump (e.g., by application of about 0 mmHg relative pressure via a vacuum source or vent 230). Gravity feed into the pump may also be used to assist in filling the pump chambers. For example, in some embodiments, the process fluid source 238 is at an elevated pressure and at an elevated location from the pump and the resultant blood pressure at the pump causes the pump valves and chambers to vent the motive fluid and actuate the diaphragms when the pressure source 220 is removed (e.g., about 20 mmHg relative to atmosphere and located 24 inches higher in elevation). A motive fluid at a pressure higher than the elevated pressure of the blood entering the pump and also higher than the pressure at the fluid return 239 can be used to operate the pump and expel the process fluid from the pump 100 to deliver blood through an external circuit to the process fluid return 239 at acceptable physiological pressures (e.g., in some cases at about an average pressure of 80 mmHg).
In certain embodiments, actuation cavities 161a, b are defined by cavity surfaces 165a, b that extend to outer perimeters 168a, b, respectively. The cavity surfaces 165a, b can include recesses 166a, b, respectively. An edge of each recess 166a, b is shown with dashed lines in the embodiment illustrated in
Chamber passages or channels 133i and 133o provide fluid communication respectively between first inlet valve seat 111i and first pump chamber cavity 113a and between first outlet valve seat 111o and first pump chamber cavity 113a. Similarly fluid communication between second inlet valve seat 112i and second pump chamber cavity 113b and between second outlet valve seat 112o and second pump chamber cavity 113b is achieved, respectively, via chamber channels 134i and 134o. This configuration permits first inlet valve seat 111i and second inlet valve seat 112i to be in fluid communication with inlet channel 138i and to alternatively receive process fluid. Similarly, first outlet valve seat 111o and second outlet valve seat 112o are in fluid communication with outlet channel 138o and alternatively deliver process fluid.
With continued reference to
Similarly, the valve seats 111i, 111o, 112i, 112o can define a smooth transition from a face of the pump body 110 to a more recessed portion of the pump body 110. For example, the valve seat 111i can smoothly slope inward from the perimeter 118i, which can be at a substantially planar first face of the pump body 110, toward a more recessed portion of the valve seat 111i that is closer to an opposite face of the pump body 110.
In certain embodiments, smooth, tangent, or rounded transitions such as just described can limit the mechanical strain by limiting the minimum radius of bending curvature of the diaphragm actuation region between the constrained perimeter of the diaphragm and a slope inflection point in the diaphragm as the diaphragm actuation region transitions between end-of-stoke positions. Reduced mechanical strain can result in a longer lifespan of the chamber diaphragms 140a, b and valve diaphragms 150a, b, in certain embodiments. In some embodiments, the diaphragms are constrained to flex at the smooth or rounded transitions (e.g., to flex over the rounded lips 116a, b). In some embodiments, the amount of strain induced in a flexing diaphragm is inversely related to the radius of curvature in these regions; as a result, longer mechanical life of the diaphragms can be achieved with relatively gradually sloping transition regions. In other embodiments, relatively sharp transitions in these regions can cause the diaphragm to flex across a plastic-like hinge. A diaphragm actuation region could incur high cyclic strain in certain of such embodiments, and might rapidly fail due to cyclic fatigue.
The valve diaphragms 150a, 150b can have additional support as the diaphragms rest on seat rims 135i, 135o, 136i, and 136o in a closed valve position, which can be at a position near a preformed dome height of the valve diaphragm valve regions 151i, 151o, 152i, 152o. If the diaphragm material is too stretchable or if the diaphragm valve regions 151i, 151o, 152i, 152o are formed with excessive dome heights, high strain plastic-like hinges can form on the edges of the seat rims, and may cause high cyclic strain and short cyclic fatigue life. In some embodiments, the diaphragm valves desirably actuate from an open to a closed position at a differential pressure less than that provided by the pressure source 220 and at a differential pressure level less (e.g., less negative) than that provided by the vacuum source 230 (see
In some embodiments, chamber diaphragms 140a, b and valve diaphragms 150a, b have actuation regions, which are pre-shaped or formed prior to assembly of the pump 100, as further discussed below. The actuation regions can protrude from a plane defined by a relatively flat portion of a diaphragm 140a, b, in some embodiments. In further embodiments, the actuation regions naturally protrude and/or are naturally rounded in a convex manner when in a first state or resting state, and can be transitioned to a concave orientation when in a second state or displaced state. The second state can be stable or metastable, in some embodiments, and the actuation regions can define a variety of other shapes in the first and/or the second states. In some embodiments, the actuation regions can be readily transitioned between the first and second states, and the regions can deform, flex, or otherwise change shape by application of a relatively small amount of pressure, as compared with a substantially flat diaphragm without actuation regions which is stretched to conform to the same shape of the first or second state of an actuation region.
In some embodiments, the diaphragm regions are preformed in such a manner that the cord length of the valve regions and the chamber regions remains substantially constant while cycling. In other embodiments, the diaphragm regions stretch by a relatively small amount. One method to quantify diaphragm stretch is the change in cord length as the diaphragm flexes from end-of-stroke positions, where the cord length is the length of a cord if positioned on the surface of the diaphragm such that the cord extends from one point on the perimeter of the formed region and continues through the center point of the region to a second point on the perimeter of the formed region, with the first and second points being opposite from each other relative to the center point. For example, in various embodiments, the cord length can change by less than about 10%, less than about 5%, or less than about 3% during each pump cycle. The cord length can be sufficient to enable the diaphragm regions 150a, b and 151i, 151o, 152i, 152o to flex and pump the fluid in the pump chamber and to flex and controllably seal the fluid flow through the pump valves at the same or substantially the same pressures. By preforming the regions of the diaphragm media in some embodiments, the valve regions can be seated without application of additional pressure, as compared with the pressure used to move the region of the diaphragm within the pump chamber. By controlling the cord length of a diaphragm in certain embodiments, the mechanical cycle life of the diaphragm can be increased by minimizing material strain when flexing from one end-of-stroke condition to the other end-of-stroke condition, and the diaphragm can be capable of reaching the end-of-stroke condition without (or substantially without) the material of the diaphragm stretching. In certain embodiments, since pressure is applied for movement or is applied for movement and at most a nominal amount for stretching the preformed actuation regions, the amount of pressure needed to actuate the diaphragm region is low and the lifespan of the diaphragm media is extended due to the gentler cycling. In some embodiments, since material strain is reduced using thin film materials in the construction of the flexing chamber diaphragms 140a, b and valve diaphragms 150a, b, the material strain caused by in-plane stretching can be controlled by the support of the pump chamber and valve cavities at end-of-stroke conditions, and long mechanical life of the diaphragms can be achieved.
In certain embodiments, higher ratios of the maximum distance between opposing sides of a perimeter or perimeter width (e.g., the diameter of a circumference) of a diaphragm region 141a, b, 151i, 151o, 152i, 152o to a dome height of the region can promote long mechanical cyclic life of the diaphragms 140a, b, 150a, b without material fatigue failure. In some embodiments, the dome height of a region is defined as the maximum distance from a plane defined by a maximum perimeter of the region (e.g., a maximum circumference of the region) to any portion of the diaphragm material that comprises the region along a line normal to the plane. The term “dome height” is a broad term and is not limited to situations in which an actuation region 141a, b, 151i, 151o, 152i, 152o shaped substantially as a rounded dome. For example, a region having a substantially pyramidal configuration could also define a dome height.
In some embodiments, the diaphragm media is reshaped when traveling between end-of-stroke positions and the reshaping can cause the material to strain. With relatively low ratios between the perimeter width and the dome height of a region, the diaphragm material in some embodiments creates relatively sharp folds in order for the dome to move from one end-of-stroke condition to another which can cause relatively high material strain and a relatively short mechanical life for the diaphragm. With relatively high ratios between the perimeter width and the dome height of a region, the size of some embodiments of the double diaphragm pump 100 can be relatively large, which can increase material costs and other costs for manufacturing the pump 100.
In various embodiments, the ratio of the perimeter width to the dome height of the actuation regions 141a, b of the chamber diaphragms 140a, b is between 4:1 and about 30:1, between about 5:1 and about 20:1, or between about 6:1 and about 10:1. In some embodiments, the ratio is about 8:1. In certain of such embodiments, the actuation regions 141a, b have diameters of about 2.7 inches and dome heights of about 0.36 inches. For such embodiments, the actuation regions 141a, b can have a stroke volume of about 25 cubic centimeters (cc) when the dome moves from one end-of-stroke position to the other.
In various embodiments, the ratio of the diameter to the preformed dome height of the actuation cavities 171i, 171o, 172i, 172o of the valve diaphragms 150a, 150b is between about 4:1 and about 30:1, between about 5:1 and about 20:1, or between about 6:1 and about 10:1. In some embodiments, the ratio is about 8:1. In certain of such embodiments, the actuation cavities 171i, 171o, 172i, 172o have diameters of about 1.12 inches and dome heights of around 0.14 inches. For such embodiments, the actuation cavities 171i, 171o, 172i, 172o can have a valve actuation stroke volume of about 1.5 cubic centimeters (cc) when the dome moves from one end-of-stroke position to the other.
In certain embodiments, to actuate the chamber diaphragms 140a, b and valve diaphragms 150a, b from one end-of-stroke position to another, a certain pressure differential level between the fluid on one side of a diaphragm and the actuation chamber pressure on the other side of the diaphragm is provided to overcome the structural stiffness of the diaphragms. If the structural stiffness of the diaphragms is too high, the pressure used to actuate the regions 141a, b, 151i, 151o, 152i, 152o may exceed the desired operating pressure of the pump. However, some embodiments also benefit from the structural stiffness of the diaphragms not being too low. For example, in some embodiments, the diaphragms desirably have enough structural rigidity to not plastically deform under the operating pressures and also to bridge over regions of the diaphragms that are not supported at their end-of-stoke positions.
In various embodiments, the differential pressure used to actuate the chamber diaphragms 140a, 140b and valve diaphragms 150a, 150b is in a range of between about 5 mmHg and about 200 mmHg, between about 20 mmHg and about 100 mmHg, or between about 30 mmHg and about 60 mmHg. In some embodiments, a relatively small initial pressure differential is sufficient to actuate preformed regions 141a, b, from a first end-of-stroke position to a second end-of-stroke position. In some embodiments, a relatively small initial pressure differential is sufficient to actuate preformed regions 151i, 151o, 152i, 152o from an open valve position to a closed valve position.
Once a valve is in the closed position, the valve can remain in the closed position so long as the fluid pressure that acts on one side of the associated region to maintain the valve in the closed position exceeds the fluid pressure on the opposite side of the region by an amount greater than the amount of pressure required to actuate the valve. For example, in some embodiments, the region 151o can be actuated from the closed valve position illustrated in
Some embodiments can include diaphragms 140a, b, 150a, b that comprise elastomeric material in a flat sheet configuration. Certain of such embodiments, however, can exhibit performance characteristics that are not present or are much less pronounced in some embodiments that include diaphragms 140a, b, 150a, b having actuation regions 141a, b, 151i, 151o, 152i, 152o. For example, in some embodiments having a flat sheet configuration, operation of the pump can cause repeated in-plane stretching of diaphragm material as displacement volumes are created, which can cause a diaphragm to fail as a result of low cycle, high strain material fatigue. In some embodiments, the pressure and suction levels needed to stretch the material by an amount sufficient to actuate the valves can exceed the available pressure level in the pressure source 220 and/or the available vacuum level in the vacuum source 230 (see
Further, variation in fluid pressures can be created in the pumping chambers 103a, b during a pumping stroke. In certain embodiments that include a sheet-like diaphragm without preformed actuation regions 141a, b, 151i, 151o, 152i, 152o, the diaphragm stretches to fill and discharge fluid and uses a dynamically changing portion of the pressure supplied to the pump chamber 103a, b in the stretching process. The pressure within the pump chamber as the chamber fills with fluid is related to the difference between the pressure supplied by a pressure source and the changing amount of pressure used to actuate and stretch the flat sheet diaphragm in its travel through a stroke. When the pump chamber discharges from a filled state, energy stored in the stretched diaphragm releases and increases the pressure supplied to the pump actuation chamber, which may result in pressure spikes in the outlet line 180o. In some embodiments, such pressure spikes can be undesirable. Similarly, when the pump chamber is filled from a discharged state, the energy stored in the stretched diaphragm releases and increases the suction supplied to the pump chamber 103a, b, which may result in suction spikes in the inlet line 180i. In some embodiments, such suction spikes can be undesirable. Some embodiments that include actuation regions 141a, b 151i, 151o, 152i, 152o thus can provide inlet line 180i and/or outlet line 180o pressures that have fewer spikes or fluctuations as a result of the actuation regions 141a, b, 151i, 151o, 152i, 152o transitioning between first and second states.
In certain embodiments, each of the diaphragms 140a, 140b, 150a, 150b is formed from a film having a substantially uniform thickness. The thickness of a diaphragm may be selected based on a variety of factors, such as the material or materials of which the diaphragm is composed, the size of the valve or chamber in which the diaphragm moves, etc. A diaphragm can be configured to separate a motive fluid from the process fluid during all stages of a stroke cycle and can be supported intermittently by surface features of the pump cavities (such as, for example, the seat rims 135i, 135o, 136i, 136o of the inlet and outlet valves 101i, 101o, 102i, 102o and/or the recesses 114a, b, 166a, b of the pump chambers 103a, b) when at an end of a stroke cycle. Accordingly, in some embodiments, the diaphragm media thickness is sufficiently thick to provide a substantially impermeable barrier between the process fluid and the motive fluid and to provide sufficient stiffness to resist substantial deformation when pressed against the surface features of the pump cavities. In some embodiments, the diaphragm thickness is also sufficiently flexible or pliable to transition between open and closed valve positions or between filled and discharged chamber positions with application of relatively small pressure differentials. In some embodiments, a thin diaphragm can have a lower level of mechanical strain when cycled between open and closed valve positions or between filled and discharged chamber positions than can a thicker diaphragm of otherwise like construction. The lower cyclic strain of a thin diaphragm can increase the lifespan of the diaphragm before mechanical failure of the material. In various embodiments, the diaphragm media has a thickness in a range between about 0.001 inches and about 0.060 inches, between about 0.002 inches and about 0.040 inches, between about 0.005 inches and about 0.020 inches, or between about 0.005 and about 0.010 inches.
In certain embodiments, higher ratios of minimum radius of bending curvature of the profile of the flexing portion of a preformed diaphragm to the diaphragm thickness may increase diaphragm cyclic life as the diaphragm transitions from one end-of-stroke position to another. In various embodiments, this ratio is in a range between about 5:1 and about 100:1, between about 10:1 and about 50:1, or between about 20:1 and about 30:1. In one embodiment, the diaphragm has a minimum radius of bending curvature of 0.25 inches and a diaphragm thickness of about 0.010 inches with a resulting ratio of 25:1.
A heater 330 (such as, for example, an infrared heater) is positioned to heat the regions of the diaphragm that are to be pre-shaped. In some embodiments, the diaphragm is substantially planar upon initial positioning between the first plate 310 and the second plate 310. The diaphragm film material can sag to a substantially non-planar configuration as it is heated and is exposed to a pressure differential, and the diaphragm material can conform to the surfaces 314a, b (see
In some embodiments, the chamber diaphragms 140a, b are made of FEP film material with a thickness of about 0.007 inches and assembled in a forming fixture 300 that is at a temperature of about 20° C. to about 40° C. In certain of such embodiments, a vacuum of about −10 psi is applied to passage 318 and an infrared heater 330 with a heater surface 331 operating at a temperature of 315° C. is positioned substantially parallel to and about 1.5 inches away from the surface of the flat diaphragm for about 1 minute. The heater is then removed. In certain embodiments, without being limited by theory, a diaphragm 140 formed via thermoforming techniques retains its shape as it is repeatedly cycled in the pump because internal stresses in the diaphragm material are relieved during the heat forming process.
While
In some embodiments, suction in first outlet valve chamber 101o causes first inlet valve region 151i of valve diaphragms 150a, 150b to move (e.g., flex) away from first inlet valve seat rim 135i, thereby permitting fluid communication between inlet channel 138i and first pump chamber 103a via chamber channel 131i. Suction provided via passage 163a (see
In some embodiments, the inlet valves 101i, 102i actively control ingress of process fluid into the first and second pump chambers 103a, b, and the outlet valves 101o, 102i actively control egress of process fluid from the first and second pump chambers 103a, b, respectively. As used herein, the term “actively control” means that the valves 101i, 101o, 102i, 102o can be actuated without dependency on the direction of the flow of process fluid through the pump 100. For example, the actuation medium that controls the transitioning and positioning of the valves 101i, 101o, 102i, 102o can do so independent of the reversal of flow of process fluid through the valve.
In some embodiments a preformed diaphragm region (e.g., 141b, 152i, 152o) defines its natural preformed shape when in an end-of-stroke position. For example, the preformed region 152o shown in
In some embodiments, it can be desirable for a preformed diaphragm region to be in its natural preformed shape when at an end-of-stroke position, as this can reduce strain on the diaphragm region in certain arrangements. In other embodiments, the diaphragm region can pass through its preformed shape before reaching an end-of-stroke position, which may, in some instances, cause the region to stretch in order to reach the end-of-stroke position. In still other embodiments, the diaphragm region may be prevented from achieving its natural preformed shape when operating within a pump chamber or valve chamber.
In some embodiments, it can be advantageous to switch from an expel stroke to a draw stroke before a diaphragm reaches an end-of-stroke condition, such as the position shown in
The bypass channels 139i, 139o can have flow areas that are much smaller than those defined by the valve portals 131i, 131o and chamber channels 133i, 133o. A volume of air can flow through an opening at a faster rate than a like volume of liquid. Accordingly, in the event of a significant volume of air being introduced into inlet channel 138i along with process fluid, the double diaphragm pump 100 will cause liquid to flow less efficiently through the pump, and air will fill the pump chambers 103a, 103b through the bypass channels 139i, 139o and then return back through the bypass channels and may prevent continually expelling air into the outlet channel 138o and then into the outlet line 180o.
For example, in some embodiments, a mixture of process fluid and air may enter the first chamber 103a from the inlet channel 138i during a fluid draw stroke. As the diaphragms 140a, b move toward the pump body 110′ to decrease the volume of the chamber 103a during an expel stroke, air within the chamber 103a may preferentially exit the chamber 103a via the bypass channel 139i and return to inlet channel 138i. This air, and possibly additional air received via the inlet channel 138i, may gather or collect in the chamber 103a and may cycle back and forth through the bypass channels 139i, 139o over the course of repeated intake and expel strokes. Eventually, sufficient air may gather in the chamber 103a to cause the pump 100′ to operate less efficiently or to stall. For example, as an increasing volume of air passes through the bypass channel 139o to gather in a chamber 103a, the amount of blood that can be drawn into the chamber 103a and subsequently expelled from the chamber 103a can decrease due to the presence of the air.
With reference again to
In some embodiments, the double diaphragm pump 100 is constructed with the inlet and outlet valve chambers 101i, 101o, 102i, 102o and the pump chambers 103a, b located on the same side of the pump body 110. The pump chambers 103a, b can also be located on opposite sides of the pump body 110 while the inlet and outlet valves 101i, 102i, 101o, 102o can be located on the opposite side of the pump body 110 from their associated pump chamber 103a, b. The pump body 110 can be constructed with more than two pump cavities 103a, b, more than two inlet valves 101i, 102i, and more than two outlet valves 112i, 112o to cooperatively work in pumping a single fluid. Also, multiple double diaphragm pumps 100 can be constructed on a single pump body 110. The diaphragms 140a, b, 150a, b can also have more valve regions 151i, 151o, 152i, 152o and pump chamber regions 141a, 141b than those shown in the depicted embodiments.
Components of the double diaphragm pump 100, or portions thereof, that are exposed to a process fluid (such as, for example, blood) can be constructed of any suitable material that is compatible with the process fluid. For example, in some embodiments, the pump 100 comprises any suitable blood-compatible material, whether currently known in the art or yet to be devised. Examples of such candidate materials can include plastic materials, such as polycarbonate (PC), polyvinyl chloride (PVC), polypropylene (PP), polyethylene (PE), polytetrafluoroethylene (PTFE), polyperfluoroalkoxyethylene (PFA), fluorinated ethylene propylene (FEP), and polyurethane (PU). In some embodiments, metal materials can be used, such as stainless steel 316L and/or titanium. In some embodiments, the body 110 is constructed of PC. The body 110 can be substantially rigid and relatively inflexible, in some arrangements.
In certain embodiments, the chamber diaphragms 140a, 140b and valve diaphragms 150a, 150b may be formed from a polymer or an elastomer. In some embodiments, polymers that have high endurance to cyclic flexing may be used, such as, for example, a fluorpolymer, such as polytetrafluoroethylene (PTFE), polyperfluoroalkoxyethylene (PFA), or fluorinated ethylene propylene (FEP). Other non-elastomer film materials may be used, such as PE, PVC, PP. In some embodiments, an elastomeric material such as silicone or polyurethane can be used for the diaphragms 140a, b, 150a, b. In certain of such embodiments, it is preferable that supporting structures be configured so as to prevent plastic hinges (e.g., relatively sharp bends in material where the diaphragm is forced by pressure into contact with features in the actuation cavities) that may cause cyclic failure.
In some embodiments, components of the pump 100 that do not contact a process fluid can be constructed of any of a variety of materials without consideration of possible incompatibilities among the materials and the process fluid. For example, in some embodiments, materials used for the chamber plate 160 and valve plate 170 can be any suitable plastic or metal material. In many embodiments, the chamber plate 160 and the valve plate 170 are substantially rigid and can be relatively inflexible.
The inlet line 180i and outlet line 180o can be made from any suitable material, and can be compatible with the process fluid. In some embodiments, the lines 180i, 180o comprise a blood compatible PVC material containing softening plasticizers, such as Tygon® S-95-E tubing available from Saint Gobain Performance Plastics, Akron, Ohio.
In certain embodiments, the pump 1100 can be in fluid communication with an inlet line 1180i and an outlet line 1180o. The pump 1100 can comprise a pump body 1110, which can define an inlet channel 1138i in fluid communication with the inlet line 1180i and an outlet channel 1138o in fluid communication with the outlet line 1180o. The pump 1100 can further comprise a chamber plate 1160, which can cooperate with the pump body 1110 to at least partially define a first pump chamber 1103a, a first inlet valve 1101i, and a first outlet valve 1101o. In some embodiments, one or more diaphragms 1140 are included between the pump body 1110 and the chamber plate 1160. The one or more diaphragms 1140 can include one or more diaphragm actuations regions 1141a, 1151i, 1151o configured to move within the first pump chamber 1103a, the first inlet valve 1101i, and the first outlet valve 1101o, respectively.
In some embodiments, the pump body 1110, the chamber plate 1160, and the one or more diaphragms 1140 further define a second pump chamber, a second inlet valve, and a second outlet valve (not shown) such as the illustrated first pump chamber 1103a, first inlet valve 1101i, and first outlet valve 1101o, respectively. The inlet channel 1138i can extend between the first inlet valve 1101i and the second inlet valve, and the outlet channel 1138o can extend between the first outlet valve 1101o and the second outlet valve.
In some embodiments, the first inlet valve 1101i includes a seat rim 1135i and the second inlet valve 1101o includes a seat rim 1135o. The pump body 1110 can define a chamber channel 1133i that provides fluid communication between the seat rim 1135i of the first inlet valve 1101i and the first pump chamber 1103a and can define another chamber channel 1133o that provides fluid communication between the pump chamber 1103a and the seat rim 1135o of the first outlet valve 1101o. In some embodiments, the diaphragm actuation region 1151i is configured to selectively permit fluid communication between the inlet channel 1138i and the chamber channel 1133i. Similarly, the diaphragm actuation region 1151o can be configured to selectively permit fluid communication between the chamber channel 1133o and the outlet channel 1138o.
In some embodiments, the chamber plate 1160 defines a motive fluid passage 1173i in fluid communication with the first inlet valve 1101i, a motive fluid passage 1173o in fluid communication with the first outlet valve 1101o, and a motive fluid passage 1163a a in fluid communication with the first pump chamber 1103a. The motive fluid passages 1173i, 1173o, and 1163a can be at least partially defined by motive fluid transfer bosses 1176a, 1176b, and 1162a, respectively. In some embodiments, the bosses 1176a, 1176b, and 1162a are configured to be connected with a motive fluid control device. In some embodiments, motive fluid is provided to the valves 1101i, 1101o and the pump chamber 1103a to actuate the diaphragm actuation regions 1151i, 1151o, and 1141a, respectively. In some embodiments, such as that illustrated in
With reference to
As further discussed below, in some embodiments, the control system 451 can control the manner in which the pumps 100, 100a operate. The control system 451 can operate a set of pumps 100, 100a in a variety of different modes, depending on the type of procedure involved. In some embodiments, the control system 451 is reconfigurable, such that the manner in which the control system 451 controls the pumps 100, 100a can be altered. The control system 451 can comprise a fluid logic system configured to direct motive fluids from different sources (e.g., motive fluids at different pressure levels) to different portions of each pump 100, 100a, and in further embodiments, can alternate which motive fluids sources are directed to the portions of the pumps 100, 100a.
In certain embodiments, the control system 451 comprises a processor 452, which can comprise any suitable logic processor or controller, and may comprise, for example, an on-board computer. In some embodiments, the processor 452 is configured to run executable computer code, and can include volatile and/or non-volatile memory. In further embodiments, the processor 452 can be configured to communicate with other devices, and may be part of a network.
In some embodiments, the control system 451 includes a user control interface 453. The interface 453 can be of any suitable variety, and can be configured to communicate information to and/or from the processor 452. For example, the interface 453 can include one or more display screens, touch screens, keyboards, mouse controllers, switches, indicators, and/or speakers. In some embodiments, instructions can be provided to the processor 452 via the interface 453. For example, in some embodiments, the processor 452 is capable of operating in a variety of different modes and the interface 453 can be used to select among the available modes. The interface 453 may also be used to program the processor 452 to operate in a new or different mode.
As further discussed below, in some embodiments, the control system 451 comprises one or more pneumatic regulators and/or vacuum generators, which can control the pressure level of a pressure source 220 and/or a vacuum source 230 (see
With continued reference to
In certain embodiments, each pump mounting area 405a, b of the manifold mounting assembly 400 comprises a manifold cover 402a, b. The manifold cover 402b can extend over and substantially shield a series of air transfer bosses 407 (see also
In certain embodiments, each air transfer boss 407 can receive a sealing element, such as an o-ring 431a-e, to facilitate or enable creation of a fluid-tight seal between the air transfer bosses 407 and the air bosses 162a, b, 176a-d of the pump 100a. Once the o-rings 431a-e are in place, the manifold cover 402b can be placed over the air transfer bosses 407 and secured to the manifold mounting assembly 400 via any suitable fastener, such as one or more screws 434a-d. In some embodiments, each o-ring 431a-e is retained between and is in fluid-tight contact with a ridge of an air transfer boss 407 and an underside of the manifold cover 402b.
In some embodiments, the manifold mounting assembly 400 comprises latches 403a, b that interact with the mounting hook 175 (see
In some embodiments, the latch 403a comprises a catch 406 (see
In certain embodiments, a screw 432b and a washer 433b are used in conjunction with a manifold plate 410 to constrain the motion and positioning of latch 403b. For example, in the embodiment illustrated in
With reference to
With reference to
In some embodiments, when the pump 100 is connected to the control system 451, the air transfer bosses 162a, b, 176a-d of the pump 100 are in fluid communication with the air transfer bosses 411-416 of the manifold mounting assembly 400. For example, in some embodiments, the air transfer bosses 412, 413, and 414 are connected with air transfer bosses 176c, 162b, and 176b of the double diaphragm pump 100 to provide for actuation of the second inlet valve 102i, second pump chamber 103b, and first outlet valve 101o. Similarly, the air transfer bosses 411, 415, and 416, are connected with air transfer bosses 176d, 162a, 176a of the air diaphragm pump 100 to provide for actuation of the first inlet valve 101i, first pump chamber 103a, and second outlet valve 102o.
In some embodiments, the air passages 417, 418 include restrictions 421, 422, respectively. For example, the air passages 417, 418 can include transfer passages to redirect the flow of motive fluid toward the air transfer bosses 411-416 (see
In some embodiments, such as the embodiment illustrated in
In some embodiments, the valve controller 212 is configured to effect transition of a motive fluid valve 210 among a variety of operational states. In some embodiments, the valve controller 212 comprises an electrical actuator (or controller) or a pneumatic actuator (or controller), which can transition the valve 210 among the operational states.
In some embodiments, the valve 210 is configured to operate in two or more positions and may include a resting state, a first state, and a second state. In the illustrated embodiment, the resting, disconnected, closed, or shutoff state of the valve 210 corresponds with the middle rectangular section, the first operational state corresponds with the top rectangular section, and the second operational state corresponds with the bottom rectangular section. In some embodiments, the resting state of the valve 210 substantially prevents fluid communication between the pump 100 and the pressure source 220 and vacuum source 230. The valve 210 can be positioned in this state, for example, during installation and removal of the pump 100 or during a pump “off” condition or pump “shut down” condition.
In some embodiments, the valve 210 provides fluid communication between a pressure source 220 and the supply port A and between a vacuum source 230 and the supply port B when in the first state, and provides fluid communication between the pressure source 220 and the supply port B and between the vacuum source 230 and the supply port A when in the second state. As indicated by the double-headed arrow, in some embodiments, the valve 210 passes through the resting state when transitioning between the first and the second operational states. Other arrangements of the valve 210 are also possible. For example, the first and second operational states of the valve 210 can be positioned adjacent to each other such that the valve 210 does not pass through the resting state in transitioning between the first and second operational states. In other embodiments, multiple motive fluid valves 210 can be used.
The pressure source 220 can comprise any suitable source of motive fluid such as, for example, an air compressor, a pressurized canister, connection to a pressurized air line, etc. Similarly, the vacuum source 230 can comprise any suitable source of motive fluid (or, in some instances, a relative lack thereof), such as, for example, a connection to a rarefied air line or a vacuum generator or an air compressor configured to evacuate or partially evacuate a chamber. In some embodiments, the vacuum source 230 comprises a vent to atmosphere, and the pressure source 220 is pressurized to a level that exceeds that of atmospheric pressure. In some embodiments, the pressure source 220 and/or the vacuum source 230 can comprise one or more pneumatic regulators to help achieve a relatively constant pressure level. As an example, in some embodiments, the pressure source 220 can comprise a first motive fluid, such as compressed air at a first pressure level (e.g., about 300 mmHg (millimeters of mercury)), and the vacuum source 230 can comprise a second motive fluid, such as rarefied air at a second pressure level (e.g., about −200 mmHg vacuum pressure).
In certain embodiments, the pump 100 is in fluid communication with a process fluid source 238, which can comprise any fluid for which pumping is desired. For example, in some medical applications, the process fluid source 238 comprises blood circulating in the vasculature of a patient. Other fluids at a variety of pressures and/or at a variety of viscosity levels are also possible. The pump 100 can be in fluid communication with the process fluid source 238 via the inlet line 180i. The pump 100 can further be in fluid communication with a process fluid destination, discharge, receiver, or return 239 via the outlet line 180o. In some embodiments, the process fluid source 238 and the process fluid return 239 are at about the same pressure. In other embodiments, the process fluid source 238 is at a lower pressure than the process fluid return 239. Other arrangements and configurations are also possible.
In some embodiments, the control valve 210 is alternated between operational states to cyclically apply pressure and vacuum to supply ports A and B prior to the chamber diaphragms 140a, b reaching the end-of-stroke or pump chamber surfaces 114a, 114b and/or the chamber cavity surfaces 165a, b. In certain of such embodiments, the pressure and flow of the process liquid at the process fluid receiver 230 can be maintained at a substantially constant level.
In certain embodiments, as the pump 100 causes fluid to flow from the process fluid source 238 to the process fluid return 239, the flow can be restricted by the capacities of fluid carrying components that may be located between the process fluid source 238 and the inlet line 180i and/or between the outlet line 180o and the process fluid receiver 239. In some embodiments, the pressure levels of the pressure source 220 and/or the vacuum source 230 and/or the operational speed or cycling rate of the valve 210 can be adjusted to achieve a desired flow rate of the process fluid.
In certain embodiments, the pressure levels of the sources 220, 230 and/or the cycling rate (or rates) of the valve 210 can be selectively changed to cause the double diaphragm pump 100 to operate in one or more different desired operating modes. For example, in a first illustrative mode, the valve 210 can switch the first supply port A from being in fluid communication with the pressure source 220 to being in fluid communication with the vacuum source 230 and can substantially simultaneously switch the second supply port B from being in fluid communication with the vacuum source 230 to being in fluid communication with the pressure source 220. The change in supply sources 220, 230 can cause the chamber diaphragms 140a, b to switch stroke direction prior to one of the pump chambers 103a, b being completely filled and prior to the other pump chamber 103a, b being completely emptied. With the pump chambers 103a, b operating opposite from each other (e.g., one chamber 103a draws process fluid from the fluid source 238 while the other chamber 103b expels process fluid to the fluid return 239), the pump 100 can draw process fluid and expel process fluid at a substantially constant rate.
In another mode, the pump 100 can be controlled to provide a substantially constant draw pattern or fill rate and a pulsatile discharge pattern by adjusting the cyclic speed of the control valve 210, the vacuum level of the vacuum source 230, and/or the pressure level of the pressure source 220. For example, in some embodiments, one of the chamber diaphragm regions 141a, b can switch stroke direction prior to completely filling one of the chambers 103a, b with process fluid when the valve 210 transitions from an open state to a closed state, and can completely discharge the contents of the chamber 103a, b and contact one of the chamber cavity surfaces 114a, b for a period of time before the valve 210 transitions from the closed state back to the open state. Likewise, the other chamber diaphragm region 141a, b can reach the end-of-stroke condition when it completely discharges the contents of the other chamber 103a, b and can be in contact with the other chamber cavity surface 114a, b for a period of time prior to the valve 210 transitioning from a closed state to an open state, and can fail to reach the fill end-of-stroke condition of the chamber 103a, b with process fluid prior to the valve 210 transitioning from the open state back to the closed state.
Similarly, in yet another mode, the pump can operate in a pulsatile fill pattern and substantially constant discharge pattern. In certain of such embodiments, one of the chamber diaphragm regions 141a, b can permit one of the chambers 103a, b to completely fill with process fluid and can contact one of the cavity surfaces 165a, b for a period of time before the valve 210 transitions from a substantially full state to a partially emptied state, and can fail to completely discharge the contents of the chamber 103a, b before the valve 210 transitions from the partially emptied state back to the substantially full state. Likewise, the other chamber diaphragm region 141a, b can fail to completely discharge the contents of the other chamber 103a, b before the valve 210 transitions from a partially emptied state to a substantially full state, and can permit the other chamber 103a, b to completely fill with process fluid and can contact the other cavity surface 165a, b for a period of time before the valve 210 transitions from the substantially full state back to the partially emptied state.
Other embodiments of supplying motive fluid to the double diaphragm pump 100 are also possible. For example, in some embodiments, multiple air control valves 210 may be employed. In further embodiments, a common motive fluid supply to one or more of the valves 101i, 101o, 102i, 102o and/or a common motive fluid supply provided to the pump chambers 103a, 103b can instead be replaced with a separate supply of motive fluid to each valve 101, 102 and chamber 103. For example, certain embodiments of the two air transfer passages 417, 418 could be replaced with six separate passages (one for each air transfer boss 411-416).
In some embodiments, the valves 101i, 101o, 102i, 102o and chambers 103a, b can be sequenced electronically to provide operating modes such as those described above. In further embodiments, operating a pump in a flow forward mode and then in a flow reverse mode by changing the sequencing of actuating the valves 101i, 101o, 102i, 102o and chambers 103a, b can also be achieved. In some embodiments, individual control of the pump valves 101i, 101o, 102i, 102o and pump chambers 103a, b can also allow other pump operating modes that can create constant (or substantially constant) and pulsatile flow from the process fluid source 238 to the process fluid receiver 239 (or vice versa). In some embodiments, time delays between allowing fluid communication between motive fluid sources (e.g., sources 220, 230) and one or more of the chambers 103a, b and valves 101i, 101o, 102i, 102o using individual controls can be advantageous. For example, in some embodiments, it can be desirable to actuate one or more of the valves 101i, 101o, 102i, 102o prior to actuating the chambers 103a, b
In certain embodiments, one or more of the diaphragm blood pumps 100b-f may have separately selectable and controllable pressure levels. For example, in some embodiments, each blood pump 100b-f is connected to a separate pressure source 220 and/or a separate vacuum source 230. In further embodiments, one or more of the pumps 100b-f can include a valve 210 that cycles at a different rate. In some embodiments, one or more of the pumps 100b-f share a common pressure source 220 and/or vacuum source 230. In certain of such embodiments, pneumatic regulators can be placed in line from the main pressure source 220 and vacuum source 230 to create unique pressure and/or suction levels for each pump 100b-f.
In some embodiments, one or more of the diaphragm blood pumps 100b-f may have separate motive fluid control valves 210, and one or more controllers 212 associated with each control valve 210 may operate the pumps 100b-f at different rates, which may be dependant upon the function the pump serves within the cardiopulmonary by-pass system 700. In some embodiments, a single processor 452 controls the one or more valve controllers 212 and the cycle rates or cycle patterns of the one or more valves 210. In other embodiments, multiple processors may provide the pumps 100b-f with different pumping rates and/or modes.
In certain embodiments, the reservoir 706 is supplied with blood flow from the patient P from the venous return catheter 704 via the venous tubing segment 705 and from the interconnections with the diaphragm blood pumps 100c 100d, and may be interconnected with other components of the system 700. Blood can be pumped from the reservoir 706 using a double diaphragm blood pump 100b, through the blood oxygenator 701, and back to the patient P via arterial tubing segment 702 and arterial cannula 703.
In some embodiments, the double diaphragm pump 100b may be operated in a manner that provides pulsatile blood flow to the patient P through the arterial cannula 703. A time delay between the cyclically controlled discharge of the pump chambers 103a, b, such as described above, can cause the pump 100b to create a more physiological “heart-like” flow through the circuit. Many of the components in the system 700 can act to dampen the effect of pulsation created by the pump 100b before the blood is returned to the patient P. In some embodiments, the pump 100b can be controlled to offset these effects. For example, in some embodiments, a processor 452 includes programmed instructions and/or implements one or more algorithms to counteract pulsation dampening provided by the system 700. In some embodiments, the processor 452 can utilize information regarding the amount of dampening provided by the system to dynamically alter operation of the pump 100b and thereby provide a desired pulsatile pumping pattern. For example, in some embodiments, the system 700 includes one or more flow meters or pressure sensors (not shown) that provide information to the processor 452 regarding the pressure and/or the flow rate of blood within the tubing segment 702.
In certain embodiments, the pump 100b operates in a mode that creates a substantially constant flow into the venous return catheter 704 from the patient P and a pulsatile outlet flow out of the arterial cannula 703 and to the patient P. Dampening of the pump-created pulsations in the various reservoirs, tubing segments, and other devices in the circuit may occur. The dampening effects can be offset by controlling the vacuum source 220, pressure source 230, and pump cycle rate to cause the pump 100b to expel fluid at a faster rate than blood is drawn, which can create an end-of-stroke discharge condition during each pump stroke. In other embodiments, the pump 100b can exhibit substantially equivalent discharge and fill times, which can create a substantially constant flow into the venous return catheter 704 from the patient and a substantially constant flow out of the arterial cannula 703 and into the patient P. Pump-created process fluid pressure pulsations can be dampened by the various reservoirs, tubing segments, and other devices in the circuit causing a substantially uniform flow into and out of the extracorporeal circuit.
In certain embodiments, when the diaphragm blood pump 100b is used to effect blood flow both away from patient P, such as via the venous return catheter 704 and into the patient, such as via arterial cannula 703, flow rates through the pump can be in a range of, for example, between about 1.0 and about 7.0 liters per minute, between about 1.0 and about 5.0 liters per minute, between about 1.0 and about 3.0 liters per minute, no more than about 7.0 liters per minute, no more than about 6.0 liters per minute, no more than about 5.0 liters per minute, no more than about 4.0 liters per minute, no more than about 3.0 liters per minute, no less than about 1.0 liters per minute, no less than about 2.0 liters per minute, or no less than about 3.0 liters per minute, depending on the medical procedure involved.
With continued reference to
Blood can also be recovered through the vent catheter 712, which may be placed inside a cavity of the heart or other cavity of a patient to withdraw blood and control the pressure or suction level inside the cavity. In such applications, it can be desirable to operate the pump 100d with near uniform suction by cyclically switching the filling and discharge of the pump chambers 103a, b before the diaphragms reach an end-of-stroke fill position. The recovered blood may be sequestered in a separate reservoir (not shown) and may be selectively returned to the reservoir 706. The recovered blood may also be processed through a system (not shown) configured to clean the blood before it is returned to the reservoir 706. In some embodiments, flow rates through the diaphragm blood pumps 100c, 100d used to effect blood flow from patient P via the suction device 713 and the vent catheter 712 to the reservoir 706 can be in the range of between about 0 and about 1.0 liters/minute, depending on the medical procedure being performed.
As shown in
In some embodiments, one or more flowmeters (not shown) can be included in the outlet fluid lines of one or more of the pumps 100e, f and can sense the flow rate of fluid discharged from the pumps 100e, f. The one or more flowmeters can provide feedback information regarding the flow rate to one or more processors 452 that control the pumps 100e, f. In some embodiments, the pressure level in the pressure source 220 and/or the vacuum source 230 can be adjusted in response to the feedback information to cause the flow rate from the pumps 100e, f to increase or decrease to obtain a desired level of mixing and a desired delivery rate of mixed fluid to the patient P. In some embodiments, the cycle rate at which diaphragm actuation regions of a given pump 100e, f are actuated can be adjusted to provide increased or decreased fluid flow from that pump 100e, f. In certain embodiments, appropriately mixed and/or heated or cooled cardioplegia fluid can be delivered via a tubing segment and cardioplegia cannula 709 to the patient P.
In certain embodiments, the pumps 100b-f can provide desirable pressure levels for the system 700. In some embodiments, the pumps 100b-f may be safer than pumps conventionally used in some of the applications described above, such as roller pumps. For example, if a vascular access connection to the patient P is somehow degraded or a blockage occurs in the system 700 (e.g., via a kink in a portion of tubing), certain embodiments of the pumps 100b-f have limited capability to generate high pressure and/or high suction levels that may damage the blood in the system 700 and/or that might otherwise be hazardous to the patient P. For example, in some embodiments, the pressure sources 220, 230 can be at pressure levels that limit the amount of pressure and/or suction provided to extracorporeal blood within the system 700. In various embodiments, the pressure of extracorporeal blood within the system is within a of between about −250 mmHg and about 500 mmHg, between about −200 mmHg and about 400 mmHg, or between about −100 mmHg and about 300 mmHg. In some embodiments the pressure of extracorporeal blood within the system 700 is no less than about −250 mmHg, no less than about −200 mmHg, no less than about −150 mmHg, no less than about −100 mmHg, no greater than about 500 mmHg, no greater than about 400 mmHg, no greater than about 300 mmHg, or no greater than about 200 mmHg.
Further, some embodiments of the pumps 100b-f do not significantly raise the temperature of blood within the system 700 if a vascular access connection to the patient P is somehow degraded or a blockage occurs in the system 700. In various embodiments, the pumps 100b-f change (e.g., raise) the temperature of extracorporeal blood within the system 700 by no more than about 3° C., no more than about 4° C., no more than about 5° C., or no more than about 6° C.
In some embodiments, the heart-assist system 750 comprises additional components and devices that are known in the art (not shown). For example, in various embodiments, the heart-assist system 750 comprises one or more reservoirs, air bubble traps, filters, and/or other devices.
In various embodiments, the system 750 can provide flow rates to or from the patient P in the range of about 1.0 liters/minute to about 8.0 liters/minute, depending on the amount of heart support needed. In certain embodiments, the pump 100g comprises pump chambers 103a, 103b that each have a volume of between about 15 cubic centimeters and about 50 cubic centimeters, between about 20 cubic centimeters and about 30 cubic centimeters, no more than about 25 cubic centimeters, or about 25 cubic centimeters. In some embodiments, the pump 100g is operated at a rate between about 10 and about 200 cycles per minute, between about 90 and about 130 cycles per minute, between about 100 and about 120 cycles per minute, no more than about 200 cycles per minute, no more than about 150 cycles per minute, no more than about 120 cycles per minute, no less than about 10 cycles per minute, no less than about 50 cycles per minute, no less than about 100 cycles per minute, or about 120 cycles per minute. In various embodiments, the pump 100g can deliver blood to the patient P at a rate between about 2 liters per minute and about 8 liters per minute, between about 3 liters per minute and about 7 liters per minute, or between about 4 liters per minute and about 6 liters per minute. In certain embodiments, the volume of the pump chambers 103a, 103b of a pump 100g and the number of cycles per minute at which the pump 100g operates can be adjusted to provide a desired flow rate. In further embodiments, relatively lower cycles per minute can lengthen the life expectancy of the pump 100g and/or can aid in providing pulsatile blood flow to a patient that mimics a heartbeat.
In some embodiments, uptake from the process fluid source 238 and discharge to the process fluid receiver 239 occurs via needles punctured into an artery to vein fistula or graft shunt, or alternatively, from a catheter positioned in a large central vein. In certain embodiments, for the portion of the circuit 800 between the patient P and the pump 100h, blood pressure can be measured and monitored by means of a pressure sensor, such as a piezo-resistive pressure transducer 804a that can be connected to the drip chamber 803, whereby a hydrophobic membrane filter (not shown) serves to prevent contamination of the blood. Similarly, venous reflux pressure in the portion of the circuit 800 between dialyzer 810 and the patient P can be measured by means of a pressure transducer 804b. Pressure sensors can be used at other portions of the circuit 800. For example, in some embodiments, pressure sensors can be used to monitor the pressure levels of blood entering and exiting the pump 100h. Pressure sensors can also be used to determine the pressure levels of motive fluid provided to the pump 100h.
In certain embodiments, the blood pump 100h effects the flow of blood in the extracorporeal circuit 800. In some embodiments, a heparin pump 808 provides for continuous feed of a desired heparin dose to prevent blood coagulation. The dialyzing liquid system 820 causes dialyzing liquid to flow through the dialyzer 810 and acts as a receiver of excess fluid and toxins removed from the blood that flows through the dialyzer. In some embodiments, the components of the extracorporeal blood circuit 800 are connected with each other via suitable safety devices known in the art or yet to be devised.
In some embodiments, an air detector 825 is included between the dialyzer 810 and the patient P. The air detector 825 can be configured to prevent infusion of blood foam or air, which may have entered the extracorporeal circuit 800, into the patient P. In some embodiments, the air detector 825 recognizes whether air bubbles or microfoam are present in the drip chamber 812 or elsewhere in the circuit 800. The air detector 825 can be in communication with a processor 452 (see, e.g.,
In other embodiments, the pump 100h may similarly be deactivated in response to other information regarding the circuit 800. For example, the sensors 804a, b may detect an undesirable increase or decrease of the arterial or venous pressure above or below a threshold level. The information can be used to deactivate the pump 100h. Similarly, the pump 100h may be deactivated as a result of a blood leak. In some embodiments, the pump 100h may be operatively associated with a control system 451, which may include an interface 453. In some embodiments, the interface 453 can display or otherwise signal information received from sensors within the circuit 800.
In some embodiments, information regarding the pressure of blood in the circuit 800, such as information provided by one or more of the pressure transducers 804a, b, is used to adjust the pressure level of motive fluid delivered to the pump 100h. For example, in some embodiments, the pressure transducers 804a, b, are configured to communicate with a processor 452 (see, e.g.,
In certain embodiments, the pump 100h can provide desirable pressure levels for the extracorporeal circuit 800. In some embodiments, the pump 100h may be safer than conventional dialysis pumps, such as roller pumps. For example, if the vascular access connection to the patient is somehow degraded or a blockage occurs in the extracorporeal circuit 800 (e.g., via a kink in a portion of tubing), certain embodiments of the pump 100h have limited capability to generate high pressure and/or high suction levels that may damage the blood in the circuit 800 and/or that might otherwise be hazardous to the patient P. Further, some embodiments of the pump 100h does not significantly raise the temperature of blood within the circuit under such conditions of connection degradation or blockage.
In some embodiments, the diaphragm blood pump 100f generates two overlapping substantially square wave inflow pressure profiles and outflow pressure profiles during the pumping cycle which can result in a substantially constant blood inflow pressure and/or a substantially constant blood outflow pressure. The inflow and outflow pressures can be set near or within safety limits to provide maximum process fluid flow without triggering pressure limit alarms. The pressure profile generated by conventional roller pumps used in hemodialysis procedures is somewhat sinusoidal and may only operate at the maximum pressure level for a short duration of the pumping cycle. Accordingly, in some embodiments, as compared with such conventional pumps, the pump 100h can achieve higher blood flows at the same peak pressure limits. Higher flow rates can reduce the duration of a given hemodialysis procedure. In some embodiments, the inflow rate and/or the outflow rate of the pump 100h can be controlled or balanced (e.g., via the processor 452) to be substantially continuous with little pulsation of pressures or flow, as compared to some roller pumps that cannot simultaneously control the inflow pressure, outflow pressure, and flowrate. In other embodiments, the pump 100h can be configured to operate in a manner similar to conventional roller pumps, if desired.
Non-limiting examples will now be discussed with reference to
Various operational parameters of the pump 100b of the present example or of other embodiments of the pump 100b can be altered such that the inflow pressure for the extracorporeal circuit and the outflow pressure for the extracorporeal circuit are more uniform than that shown. For example, in some embodiments, the valley of the “Pump Out” line at the time coordinate of 0.2 seconds is relatively more shallow (e.g., has a minimum value of between about 200 and about 300 mmHg) and/or may be relatively more constricted (i.e., span over a shorter time period). Similarly, in some embodiments, the peak of the “Pump In” line at the time coordinate of 0.2 seconds is smaller (e.g., has a maximum valve of between about 0 and about 100 mmHg) and/or may be relatively more constricted.
In some embodiments, the inflow to the pump 100b and outflow from the pump 100b are approximately uniform. As used herein, the term “approximately uniform” when used to describe a flow rate is a broad term and signifies that over a single pump cycle, the maximum flow rate deviates from the average flow rate by no more than about 25% of the average flow rate during the pump cycle.
As discussed above, in some embodiments, flow and pressure pulsations created by a pump 100b can be dampened by the various reservoirs, tubing segments, and other devices in a circuit, and can result in more uniform flow rates and pressures. In certain embodiments, the uptake flow rate at a blood source 238 (e.g., a patient) and/or a delivery flow rate at a blood delivery destination 239 (e.g., a patient) can be essentially constant during a pump cycle. As used herein, the term “essentially constant” when used to describe a flow rate is a broad term and signifies that over a single pump cycle, the maximum flow rate deviates from an average flow rate by no more than about 10% of the average flow rate during the pump cycle. The pump 100b used to create the chart of
Various operational parameters of the pump 100g of the present example or of other embodiments of the pump can be altered such that the inflow to the extracorporeal circuit is more uniform than that shown. For example, in some embodiments, the peak of the “Pump In” line at the time coordinate of about 0.45 seconds is smaller (e.g., has a maximum valve of between about 20 and about 80 mmHg) and/or may be relatively more constricted. Similarly, the pulsatile characteristics of the outflow from the extracorporeal circuit may be modified, as briefly discussed below.
The pump 100g used to create the chart of
The chart illustrates the pump 100h as having operated at 3 seconds per stroke (i.e., 6 seconds per cycle or 10 cycles per minute). The pressure level in the pressure source 220 was established below about 390 mmHg, which caused the dialyzer out pressure to remain below about 250 mmHg, and the level of suction in the suction source was established above about 250 mmHg. The pump 100h used to create the chart of
The pump 100h is illustrated as having operated at 3 seconds per stroke (i.e., 6 seconds per cycle or 10 cycles per minute). Shorter, more pronounced pulse widths can be generated by extending the cycle time or increasing the pressure level in the pressure source 220. The pressure level in the pressure source 220 was established below about 360 mmHg, which caused the dialyzer out pressure to remain below about 250 mmHg, and the level of suction in the suction source was established above about −160 mmHg. The pump 100h used to create the chart of
Various features and structures discussed herein, and equivalents thereof, can provide specific functionalities. By way of illustration, in some embodiments, the first and second pump chambers 103a, b are examples of first and second means for selectively drawing process fluid from a process fluid source (e.g., the fluid source 238) and selectively expelling process fluid to a process fluid delivery destination (e.g., the process fluid delivery destination 239); the first and second inlet valves 101i, 102i are examples of first and second means for selectively permitting process fluid to flow to the first and second means for selectively drawing process fluid from a process fluid source and selectively expelling process fluid to a process fluid delivery destination, respectively; and the first and second outlet valves 101o, 102o are examples of first and second means for selectively permitting process fluid to flow from the first and second means for selectively drawing process fluid from a process fluid source and selectively expelling process fluid to a process fluid delivery destination, respectively.
As used in this specification, including the claims, the term “and/or” is a conjunction that is either inclusive or exclusive. Accordingly, the term “and/or” either signifies the presence of two or more things in a group or signifies that one selection may be made from a group of alternatives.
Without further elaboration, it is believed that one skilled in the art can use the preceding description to utilize the claimed inventions to their fullest extent. The examples and embodiments disclosed herein are to be construed as merely illustrative and not a limitation of the scope of the present disclosure in any way. It will be apparent to those having skill in the art that changes may be made to the details of the above-described embodiments without departing from the underlying principles discussed. In other words, various modifications and improvements of the embodiments specifically disclosed in the description above are within the scope of the appended claims. For example, any suitable combination of features of the various embodiments described is contemplated. Note that elements recited in means-plus-function format are intended to be construed in accordance with 35 U.S.C. § 112 ¶6. The scope of the invention is therefore defined by the following claims.
This application is a continuation of U.S. patent application Ser. No. 13/472,099, filed May 15, 2012, titled DIAPHRAGM PUMPS AND PUMING SYSTEMS, which is a continuation of U.S. patent application Ser. No. 11/945,177, filed Nov. 26, 2007, titled DIAPHRAGM PUMP AND RELATED METHODS, which is a continuation-in-part of U.S. application Ser. No. 11/484,061, filed Jul. 11, 2006, titled DOUBLE DIAPHRAGM PUMP AND RELATED METHODS, which claims priority to U.S. Application No. 60/699,262, filed Jul. 13, 2005, titled DOUBLE DIAPHRAGM PUMP AND RELATED METHODS; each of the foregoing applications is hereby incorporated by reference herein and made a part of this application.
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| 20150098846 A1 | Apr 2015 | US |
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| Parent | 11484061 | Jul 2006 | US |
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