METHOD AND APPARATUS FOR ENHANCED TRANSPORT CROSS-REFERENCE TO RELATED APPLICATIONS [0001] This application claims benefit of U.S. Provisional Application No.63/347,440 filed May 31, 2022, the disclosure of which is hereby expressly incorporated herein by reference in its entirety. ACKNOWLEDGEMENT OF GOVERNMENT SUPPORT [0002] This invention was made with government support under Grant No.1 R43 HL160318-01 awarded by the National Institutes of Health. The government has certain rights in the invention. FIELD [0003] The present application is directed to the use of acoustic energy such as ultrasound to enhance transport of matter, such as gases or waste products, across membranes. BACKGROUND [0004] Use of membranes to mediate transport of matter between media are used in a range of applications, especially medical applications. For example, the extra-corporeal membrane oxygenation (ECMO) device mediates transport of oxygen across a membrane and into blood to assist the cardiovascular system of a patient. However, such devices often rely on membranes with large surface areas increasing the need for anticoagulants to avoid fouling and adverse effects on the patient. [0005] Thus, there remains a need for further improvements in systems for enhancing transport across membranes. SUMMARY [0006] Disclosed herein is a system and method for enhancing transport of matter between two media. The system includes a membrane separating the two media wherein the first media contacts at least one surface area of the membrane. Further included is a transducer configured to direct acoustic energy into the first medium proximate the at least one surface area of the membrane. In this manner, the system accelerates transport of the matter from the first to the second media. The system is useful in dialysis and extracorporeal membrane oxygenation for example. The system also can have industrial applications, such as in the oil and gas industry. [0007] A method of another embodiment enhances transport of a matter from a first medium across a membrane to a second medium. The method includes supplying power to at least one transducer to generate acoustic energy. Also, directing the acoustic energy into the first medium proximate at least one surface area of the membrane. The method also includes accelerating transport of the matter from the first medium through the membrane into the second medium using the acoustic energy. [0008] Another embodiment includes dialysis specific applications. For example, the system enhances transport of waste products between blood and dialysate. The system can include a dialysis membrane and at least one transducer. The dialysis membrane is porous and separates the blood from the dialysate. The blood contacts at least one surface area of the membrane. The dialysate contacts an opposite surface area of the membrane. The at least one transducer is configured to direct acoustic energy into one of the blood or dialysate proximate the at least one surface area and the opposite surface area of the membrane. This accelerates transport of the waste products from the blood to the dialysate. Waste products can include excretable solutes such as urea, inorganic phosphate or any other small molecule with molecular weight < 1KDa. DESCRIPTION OF DRAWINGS [0009] FIG. 1 is a schematic of a system for enhancing transport across a membrane of one embodiment of the present invention; [0010] FIG.2 is a schematic another embodiment of a system for enhancing transport with a focused energy field; [0011] FIG.3 is a schematic of another embodiment of a system for enhancing transport with a side-mounted transducer; [0012] FIG.4 is a schematic of another embodiment of a system for enhancing transport with an angled transducer; [0013] FIG.5 is a schematic of another embodiment of a system for enhancing transport with a top-mounted transducer directed at a second medium; [0014] FIG.6 is a schematic of another embodiment of a system for enhancing transport with a medium having an osmotic pressure similar to blood; [0015] FIG.7 is a schematic of another embodiment of a system for enhancing transport with a top-mounted transducer directed at a second medium having an osmotic pressure similar to blood; [0016] FIG.8 is a schematic of another embodiment of a system for enhancing transport with an acoustically active membrane; [0017] FIG.9 is a schematic of another embodiment of a system for enhancing transport with an acoustically active membrane and a second medium with an osmotic pressure similar to blood; [0018] FIG.10 is a schematic of another embodiment of a system for enhancing transport with bubbles on a porous membrane; [0019] FIG.11 is a schematic of another embodiment of a system for enhancing transport with bubbles within a porous membrane; [0020] FIG.12 is a schematic of another embodiment of a system for enhancing transport with a bubble generator; [0021] FIGS. 13-16 are graphs showing an increase in matter transport across a membrane using ultrasound of other embodiments of the present invention; [0022] FIG. 13 shows the effect of ultrasound on polypropylene membrane mediated oxygenation of perfluorodecalin; [0023] FIG. 14 shows the effect of ultrasound on polypropylene membrane mediated oxygenation of whole blood at 37ºC; [0024] FIG. 15 shows the improvement of KMnO4 diffusion rate when a 24v ultrasound transducer is placed in the KMnO4 solution side and the beam was focused on the membrane; [0025] FIG. 16 shows the improvement of KMnO4 diffusion rate when a 24v ultrasound transducer is placed in the dialysate side and the beam was focused on the membrane; [0026] FIG.17 is a front elevation view of a diffusion device of one embodiment of the present invention; [0027] FIG.18 is a side elevation view of the diffusion device of FIG.17; [0028] FIG.19 is a top plan view of the diffusion device of FIG.18; [0029] FIG.20 is a bottom plan view of the diffusion device of FIG.19; [0030] FIG. 21 is a cross-sectional view of the diffusion device of FIG. 17 showing a fluid flow path therethrough; [0031] FIG.22 is a cross-sectional plan view of the diffusion device of FIG.17 showing a gas path therethrough including through a hollow fiber membrane; [0032] FIG. 23 is a partial sectional perspective view of the diffusion device of FIG. 17 showing a membrane module; [0033] FIG.24 is an electron microscopy photo of a hollow fiber used in the membrane module of FIG.23; [0034] FIG.25 shows an example computing environment in which example embodiments of the control of membrane transport systems and aspects thereof may be implemented; [0035] FIG.26 is a schematic diagram of computer hardware that may be utilized to implement control of membrane transport processing in accordance with the disclosure according to certain embodiments; and [0036] FIG. 27 shows a graph depicting enhanced diffusion of CO ₂ across a hollow fiber membrane as a function of increasing the power of an ultrasound-emitting transducer. DETAILED DESCRIPTION [0037] The following description of certain examples of the inventive concepts should not be used to limit the scope of the claims. Other examples, features, aspects, embodiments, and advantages will become apparent to those skilled in the art from the following description. As will be realized, the device and/or methods are capable of other different and obvious aspects, all without departing from the spirit of the inventive concepts. Accordingly, the drawings and descriptions should be regarded as illustrative in nature and not restrictive. [0038] For purposes of this description, certain aspects, advantages, and novel features of the embodiments of this disclosure are described herein. The described methods, systems, and apparatus should not be construed as limiting in any way. Instead, the present disclosure is directed toward all novel and nonobvious features and aspects of the various disclosed embodiments, alone and in various combinations and sub-combinations with one another. The disclosed methods, systems, and apparatus are not limited to any specific aspect, feature, or combination thereof, nor do the disclosed methods, systems, and apparatus require that any one or more specific advantages be present or problems be solved. [0039] Features, integers, characteristics, compounds, chemical moieties, or groups described in conjunction with a particular aspect, embodiment or example of the invention are to be understood to be applicable to any other aspect, embodiment or example described herein unless incompatible therewith. All of the features disclosed in this specification (including any accompanying claims, abstract, and drawings), and/or all of the steps of any method or process so disclosed, may be combined in any combination, except combinations where at least some of such features and/or steps are mutually exclusive. The invention is not restricted to the details of any of the disclosed embodiments. The invention extends to any novel one, or any novel combination, of the features disclosed in this specification (including any accompanying claims, abstract, and drawings), or to any novel one, or any novel combination, of the steps of any method or process so disclosed. [0040] It should be appreciated that any patent, publication, or other disclosure material, in whole or in part, that is said to be incorporated by reference herein is incorporated herein only to the extent that the incorporated material does not conflict with existing definitions, statements, or other disclosure material set forth in this disclosure. As such, and to the extent necessary, the disclosure as explicitly set forth herein supersedes any conflicting material incorporated herein by reference. Any material, or portion thereof, that is said to be incorporated by reference herein, but which conflicts with existing definitions, statements, or other disclosure material set forth herein will only be incorporated to the extent that no conflict arises between that incorporated material and the existing disclosure material. [0041] As used in the specification and the appended claims, the singular forms "a," "an" and "the" include plural referents unless the context clearly dictates otherwise. Ranges may be expressed herein as from "about" one particular value, and/or to "about" another particular value. When such a range is expressed, another aspect includes from the one particular value and/or to the other particular value. Similarly, when values are expressed as approximations, by use of the antecedent "about," it will be understood that the particular value forms another aspect. It will be further understood that the endpoints of each of the ranges are significant both in relation to the other endpoint, and independently of the other endpoint. [0042] Although the operations of exemplary embodiments of the disclosed method may be described in a particular, sequential order for convenient presentation, it should be understood that disclosed embodiments can encompass an order of operations other than the particular, sequential order disclosed. For example, operations described sequentially may in some cases be rearranged or performed concurrently. Further, descriptions and disclosures provided in association with one particular embodiment are not limited to that embodiment, and may be applied to any embodiment disclosed. [0043] Further, the terms “coupled” and “associated” generally means electrically, electromagnetically, and/or physically (e.g., mechanically or chemically) coupled or linked and does not exclude the presence of intermediate elements between the coupled or associated items. [0044] "Optional" or "optionally" means that the subsequently described event or circumstance may or may not occur, and that the description includes instances where said event or circumstance occurs and instances where it does not. [0045] The term “transducer” refers to a device that converts energy of one type to energy of another type. In the present disclosure, the term transducer will generally refer to a device that converts electrical energy to ultrasound energy. In portions of the present disclosure, we will use the terms “acoustic source,” “ultrasound source,” and “ultrasound emitter” to be generally synonymous with the term transducer. Ultrasound transducers may include piezoelectric ceramics (including lead-ziconate-titanate), piezoelectric polymers (including PVDF), MEMS transducers, CMUTs, PMUTs, PolyMUTs, and other technologies. The term ultrasound refers to acoustic energy with frequencies above approximately 20 kHz. Unless specifically noted, the term “fluid” will refer to blood, dialysate, or other fluids of practical interest, including non-biological fluids such as petroleum. [0046] One embodiment of the present invention applies ultrasound energy to enhance diffusion of gas through a semi-permeable membrane. In one embodiment, a membrane separates a gas-filled chamber from a fluid-filled chamber. Ultrasound energy is applied to the fluid-filled chamber and is directed towards the membrane. [0047] Without being wed to theory, the inventors have determined that ultrasound energy enhances diffusion through a number of mechanisms. First, whenever an ultrasound wave propagates through a medium with finite attenuation (practically all media) then the loss of ultrasound energy leads to a momentum transfer from the propagating ultrasound wave to the medium. This momentum transfer results in a local force being applied to the propagation medium. This force is localized within the propagating ultrasound field with a direction coincident with the direction of the propagating ultrasound field. This force field, known as acoustic radiation force, may cause displacements of solid media and may induce flow within fluid media. Such radiation force induced flow is known as acoustic streaming. Acoustic streaming may act to increase the transport of gases by causing flow near the membrane separating the gas and fluid. This flow may shrink the boundary layer near the membrane and therefore steepen the concentration gradient of the dissolved gas within the fluid. Because this concentration gradient drives diffusion, diffusion may increase. [0048] The inventors have also determined that at high ultrasound intensities, non-linear propagation may cause the development of harmonic frequencies in the propagated ultrasound wave field. Likely, higher frequencies are more rapidly attenuated, so the acoustic streaming may grow more rapidly with increasing ultrasound amplitude. The improvements in transport may thus grow faster than linearly with increasing acoustic amplitude. [0049] The improvements in transport are greater with focused ultrasound fields than with a broad, uniform ultrasound field. One reason may be that the acoustic radiation force field is localized within the ultrasound field. A uniform wave field yields a uniform force within the fluid. This bulk force does not allow for recirculation and therefore does not yield significant velocities. Higher flow velocities may disrupt the boundary layer more and may therefore yield more significant improvements in transport. [0050] In one embodiment of the present invention, the ultrasound wavefield is generated by an unfocused transducer with dimensions selected so that the near-field / far-field transition of the wave field is located near the membrane. In this scenario the transducer “auto-focuses” so that the acoustic intensity and therefore radiation force field is localized in or before the membrane. This may yield higher flow velocities near the membrane. In other embodiments, it is considered to place the near-field / far-field transition at a distance before the membrane so that the flow field may be greater at the membrane surface. [0051] In another embodiment of the present invention, it is advantageous to use physically focused transducers (ultrasound emitters) to localize the acoustic field and therefore the acoustic radiation force. This may allow for placement of the ultrasound focus at a distance that would not be compatible with an auto-focused system. This may be particularly valuable when it is desired to place the focus at a range near to the transducer. Such a configuration can allow for a shallower fluid layer and therefore a smaller apparatus. [0052] In embodiments with a focused system, it may be desired to present a flat surface to the fluid, rather than a convex surface. In these embodiments, it may be desired to encapsulate the transducer to yield a desired surface geometry. One of skill in the art, studying this disclosure of the invention, will realize that unless the encapsulant has the same speed of sound as the working fluid, it may be necessary to account for speed of sound differences to ensure proper focusing of the acoustic field. [0053] In another embodiment, it may be advantageous to use a phased array focusing system, rather than a physically focused transducer. This approach may allow a flat transducer to be focused at an arbitrary depth. A phased array system has the further advantage of being able to employ apodization to increase the depth of field of the focal field. A phased array system also allows the acoustic field (acoustic beam) to be steered. Such steering may be advantageous. In one instance the steering may be applied to direct the acoustic beam against the direction of flow of the fluid. In one such approach the applied fluid flow would be parallel to the membrane and the ultrasound beam would be directed at 45° relative to the membrane, but with a component pushing against the fluid flow direction. This approach may cause mixing of the fluid. In another instance the beam may be steered at 45° relative to the direction of flow, but along the direction of flow to accelerate the fluid. This may create a higher flow velocity and may act to collapse the boundary condition. [0054] The embodiments of the present invention may be further supplemented by the use of an array of transducers designed to create an array of acoustic beams. Such a configuration may create multiple acoustic streaming paths. This would increase diffusion at multiple locations on the membrane simultaneously. One simple approach to create multiple beams would be to create a checkerboard of transducers with white squares being active transducers and black squares being inactive regions. Alternative geometries such as hexagonal grids, triangular grids, or other geometries would also work well. [0055] Diffusion is a rate limited process. Ultrasound can be turned on and off very quickly. It may be advantageous to alternate ultrasound between two or more transducers. In one embodiment, the checkerboard pattern described above could alternate between a period of transmission on the white squares and a second period of transmission from the black squares. [0056] In each of the above embodiments, it could be advantageous to coat the transducer or transducer encapsulant with material to reduce the likelihood of clot formation. [0057] Blood (and other fluids) can be damaged by excessive temperatures. For this reason, it may be advantageous to apply active cooling to the back of the transducer. Alternatively, or in addition, the transducer can be placed within a thermally conductive fixture. As another alternative or option, the fluid itself can be cooled. The encapsulant described above can be selected to provide thermal insulation. One possible material for encapsulation is polymethylpentene (trade name TPX). This material provides an excellent acoustic match to blood (and other working fluids) and has a low thermal conductivity. [0058] In addition to bulk streaming, resulting from acoustic radiation force within fluid, microstreaming is also a possibility. Microstreaming is the result of expansion and contraction of bubbles within a fluid. Since liquids are almost entirely incompressible, but gases are highly compressible, the application of ultrasound to a bubble may cause that bubble to expand and contract dramatically. Since the fluid may mostly retain its volume, the fluid will rush into and out of the volume around the bubble. This effect is called microstreaming which may advantageously improve oxygen transport. [0059] The embodiments of the present invention may incorporate bubbles on the membrane in order to provide a locus for microstreaming. Microstreaming can effectively mix fluids at the membrane surface and therefore disrupt the boundary layer and enhance transport. Similar effects can be achieved by embedding bubbles within the membrane. Bubbles can also be injected within the fluid in order to enable microstreaming and associated mixing throughout the bulk of the fluid. The bubbles will also be displaced strongly by the acoustic wave field and may therefore increase streaming and associated mixing. [0060] Absorption of the propagating ultrasound causes local heating of the fluid and the membrane if it impinges upon it. Differential heating will induce convection, which can drive an increase in transport. [0061] In the present disclosure, the term hollow fiber membrane (HFM) refers to a hollow tube with porous walls. The HFM wall, for example, can separate the blood chamber from the fluid or gas chamber. (An HFM can be used to separate other media, including non-biological media such as petroleum and water for example.) In the embodiments of the present disclosure where HFM allows diffusion of gases into the blood, the HFM is permeable to gases. In the current embodiment of the present disclosure where HFM allows diffusion of water-soluble molecules from the blood, the HFM is permeable to water. [0062] In one embodiment where HFM is used for diffusing gases into the blood, the inner diameter of the HFM ranges between 100 μ-200μ, 200μ-300μ, 300μ-400μ, 400μ-500μ, 500μ- 700μ and wall thickness ranges from 10-30μ, 30-60μ, 60-90μ, 90μ-120μ and about 100μ and the size of the pores in the wall ranges from 1nm, 1nm to 3nm, 3nm to 5nm, 5nm to 10nm, 10nm to 100nm, 100nm to 500nm, 500nm to 1 micrometer. [0063] In the embodiment where HFM is used for diffusing gases into the blood, the gas is passed through the hollow lumen and blood is passed over the HFM outer surface. [0064] In one embodiment where HFM is derived from poly methyl pentene (PMP) by a melt extrusion process, the PMP HFM has an outer layer which partially covers the pores present in the wall and resists fluid from the blood to infiltrate into the hollow lumen. [0065] In another embodiment, HFM is derived from polypropylene. [0066] In another embodiment, expanded polytetrafluoroethylene (ePTFE) is used as HFM. In this embodiment ePTFE HFM is produced by expanding PTFE tubes by forcefully pulling it from both ends. [0067] In the embodiment where ePTFE is used as HFM, the density of ePTFE varies from 0.3-0.5 g/cc, 0.5-0.7 g/cc, 0.7-0.9 g/cc, 0.9-1.2 g/cc, 1.2-1.5g/cc, 1.5-1.8 g/cc, 1.8-2.0 g/cc. [0068] In another embodiment of the current disclosure, the HFM comprises polyvinylidene fluoride (PVDF) which has piezoelectric property. [0069] In another embodiment of the current disclosure, the HFM comprises a porous ceramic which has piezoelectric property. The porous ceramic HFM can be produced by casting a composite film of ceramic particle dispersion and a polymer binder which undergoes thermal degradation during the subsequent sintering step. [0070] In another embodiment of the current disclosure, the HFM is made out of PVDF and ceramic composite which has piezoelectric property. [0071] In an embodiment of the present disclosure where HFM is used for the diffusion of gases into the blood, the blood contacting surface is coated with an antithrombogenic coating which includes, but is not limited to phosphatidyl choline, heparin, or bovine serum albumin. [0072] In an embodiment of the present disclosure where the HFM is used for diffusing excretable solutes from the blood into a secondary fluid, the inner diameter of the HFM varies between 100 μ-200μ, 200μ-300μ, 300μ-400μ, wall thickness varies between 10-20μ, 20-30μ, 30-40μ, 40-50μ, 50-70μ and pore size varies between 1-3 nm, 3-5nm, 5-10nm, 10-20nm, 20- 50 nm. [0073] In an embodiment of the present disclosure where the HFM is used for diffusing excretable solutes from the blood into a secondary fluid, the blood is passed through the hollow fiber and the secondary fluid of identical osmotic pressure of blood is passed over the HFM. Excretable solutes diffused and convected through the HFM are removed by the secondary fluid. [0074] In an embodiment of the present disclosure where the HFM is used for diffusing excretable solutes from the blood into a secondary fluid, the HFM can comprise polysulfone or polyether sulfone or polyvinyl pyrrolidone or sulfonated polyacrylonitrile or polymethylmethacrylate. [0075] In an embodiment of the present disclosure where the HFM is used for diffusing excretable solutes from the blood into a secondary fluid, the pore size of HFM wall allows small molecules and macromolecules (<11 KDa) to diffuse through the membrane while limiting albumin leakage. [0076] In an embodiment where ultrasound is focused on the HFM, the deposition of any protein membrane on the HFM wall is inhibited by the ultrasound. [0077] In an embodiment where ultrasound is focused on the HFM, the diffusion rate of solutes is increased by the local heating created by the ultrasound on the HFM surface. [0078] In an embodiment where HFM is used for diffusing excretable solutes from the blood into a secondary fluid, the biocompatibility of the membrane can be improved or supplemented by incorporating oligomeric surface-active additives into the bulk polymer during the HFM manufacturing process. [0079] In an embodiment where HFM is used for diffusing excretable solutes from the blood into a secondary fluid, the surface charge (zeta potential) of the HFM is partially neutralized by incorporating zwitterionic surface active additives into the bulk polymer during the HFM manufacturing process. [0080] Figures 1-12 show various embodiments of transducers and membranes to enhance transport across the membranes and to test the same for various practical applications. Figure 1, for example, shows a dual compartment setup with a porous membrane 110 dividing a blood compartment 120 from a gas compartment 130. An ultrasound source 140, such as an ultrasound transmitter, is positioned adjacent to the blood compartment 120. The ultrasound transmitter 140 is oriented to emit a signal generally perpendicular (generally orthogonal) to the surface of the porous membrane 110. [0081] Figure 2 illustrates, in another embodiment, a focused ultrasound energy field 250 emitted by a perpendicularly oriented ultrasound source 240. Other components of the system of Figure 2 are similarly configured as Figure 1, including a porous membrane 210 and a blood compartment 220 and a gas compartment 230 separated by the porous membrane. [0082] Figure 3 illustrates, in another embodiment, a porous membrane 310 separating a blood compartment 320 from a gas compartment 330. An ultrasound source 340 is positioned adjacent to the blood compartment 320 and is oriented to emit an ultrasound energy field 350 that parallels the blood-facing surface of the porous membrane 310. [0083] Figure 4 illustrates, in another embodiment, a porous membrane 410 separating a blood compartment 420 from a gas compartment 430. An ultrasound source 440 is positioned adjacent the blood compartment 420 and is oriented to emit an ultrasound energy field 450 at an angle to the surface of the porous membrane. [0084] Figure 5 illustrates another embodiment wherein a porous membrane 510 again separates a blood compartment 520 from a gas compartment 530, but an acoustic source 540 is positioned adjacent to the gas compartment. The acoustic source 540 is oriented generally perpendicular or orthogonal to the surface of the porous membrane 510. [0085] Figure 6 illustrates another embodiment wherein a porous membrane 610 separates a blood compartment 620 from a liquid compartment 630. The liquid in the liquid compartment has an osmotic pressure similar to that of blood. Like Figure 2, an ultrasound source 640 is oriented and emits an ultrasound energy field 650 perpendicular to the surface of the porous membrane 610. [0086] Figure 7 illustrates another embodiment wherein a porous membrane 710 separates a blood compartment 720 from a liquid compartment 730. An ultrasound source 740 is positioned adjacent to the liquid compartment 730. The ultrasound source is positioned and oriented (configured) to emit an ultrasound energy field 750 perpendicular, through a liquid with an osmotic pressure similar to blood, to the porous membrane 710. [0087] Figure 8 shows an embodiment wherein a porous membrane 810 separates a blood compartment 820 from gas compartment 830. In this embodiment, the porous membrane 810 is itself acoustically active. [0088] Figure 9 shows an embodiment wherein an acoustically active porous membrane 910 separates a blood compartment 920 from a liquid compartment 930. The liquid has an osmotic pressure similar to blood. [0089] Figure 10 shows an embodiment wherein a porous membrane 1010 separates a blood compartment 1020 from a gas compartment 1030. An ultrasound source 1040 is positioned adjacent to the blood compartment opposite the porous membrane 1010. Also, a plurality of bubbles 1060 are positioned over the blood-side surface of the porous membrane 1010 in the pathway of an ultrasound energy field. [0090] Figure 11 shows an embodiment wherein a porous membrane 1110 separates a blood compartment 1120 from a gas compartment 1130. An ultrasound source 1140 is positioned opposite the porous membrane 1110. A plurality of bubbles 1160 are positioned within the porous membrane 1110. [0091] Figure 12 shows an embodiment wherein a porous membrane 1201 separating a blood compartment 1220 from a liquid compartment 1230. An ultrasound source 1240 is positioned adjacent to the liquid compartment 1230 and opposite the porous membrane 1201. The liquid in the liquid compartment 1230 has an osmotic pressure similar to blood. (Liquid compartments disclosed herein may have other liquids and do not necessarily require a matching of osmotic pressure with blood.) A bubble injector 1270 is positioned in fluid communication with the liquid compartment and is configured to inject a plurality of bubbles 1260 within the liquid. [0092] Exemplary testing results are provided herein for the purposes of illustration and not limitation. [0093] Test 1: Perfluorodecalin oxygenation through a membrane as shown in Figure 13. [0094] In a closed loop, 60 mL perfluorodecalin (PFD) was circulated at 150 ml/min through the transducer compartment of the dual compartment setup shown in Figure 1. The other compartment was placed under an oxygen atmosphere maintaining 3 cm hydrostatic pressure. Both compartments were separated by a semipermeable polypropylene membrane (100 nm pore size). Rate of PFD oxygenation was measured real time by recording the dissolved oxygen concentration using PreSens OXY-4 SMA oximeter probe working on an oxidative photobleaching mechanism. The rate of oxygenation was compared between two separate experiments run in the presence and absence of ultrasound. Figure 13 shows the effect of ultrasound on polypropylene membrane mediated oxygenation of perfluorodecalin. The rate of oxygenation increased by 6.3-fold under the influence of 24V ultrasound focused on polypropylene membrane. [0095] Test 2: Whole blood oxygenation through a membrane as shown in Figure 14. [0096] In a closed loop, 60 mL whole blood was circulated at 150 ml/min through the transducer compartment of a dual compartment setup shown in Figure 1. The other compartment was placed under an oxygen atmosphere maintaining 3 cm hydrostatic pressure. Both compartments were separated by a semipermeable polypropylene membrane (100 nm pore size). The rate of whole blood oxygenation was measured in real time by recording the blood oxygen saturation using Fresenius CRIT LINE III pulse oximeter probe. The rate of oxygenation was compared between two separate experiments run in the presence and absence of ultrasound. Figure 14 shows the effect of ultrasound on polypropylene membrane mediated oxygenation of whole blood at 37 C. The rate of oxygenation increased by 4.6-fold under the influence of 24V ultrasound focused on polypropylene membrane. [0097] Test 3: Whole blood removal of small molecules through a membrane as shown in Figures 15 and 16. [0098] In a closed loop, 20 mL KMnO4 solution in phosphate buffer saline (PBS) was placed in the transducer compartment of a dual compartment setup shown in Figure 1. 200 mL PBS buffer as dialysate was circulated through the other compartment at 150 ml/min flow rate. Both compartments are separated by a semipermeable polysulfone membrane (30 nm pore size). The rate of KMnO4 diffusion was measured by collecting 300 uL dialysate solution at every time point. The rate of KMnO4 diffusion was compared between two separate experiments run in the presence and absence of ultrasound. This experiment was repeated with the transducer placed both in the KMnO4 side and the dialysate side. [0099] Figure 15 shows improvement of KMnO4 diffusion rate by 14-fold when a 24v ultrasound transducer is placed in the KMnO4 solution side and the beam was focused on the membrane. The KMnO4 concentration in flowing dialysate was measured at different time points by UV-vis absorption spectroscopy at 562 nm wavelength. Figure 16 shows improvement of KMnO4 diffusion rate by 5.5-fold when a 24v ultrasound transducer is placed in the dialysate side and the beam was focused on the membrane. The KMnO4 concentration in flowing dialysate was measured at different time points by UV-vis absorption spectroscopy at 562 nm wavelength. It should be noted that for some systems any amount of improvement can yield practical results that justify the use of sonic energy to improve transport. For example, just a few fractions of improvement in certain industrial processes or in human systems can have large production and health consequences. Improvements of 20% or more or even just fractions of a percent or 1% or more can have a surprising impact in some more staid industries. In the water purification industry a mere 20% to 50% improvement would have wide-ranging impacts on the availability of purified water. [00100] Figure 17 illustrates a diffusion device 1700 of another embodiment of the present invention including a housing 1710, a membrane module 1730, and a transducer module 1750. The gas diffusion device 1700, amongst other things, defines an internal fluid pathway 1770 (as shown in Figure 21) and a gas pathway 1731 (as shown in Figure 22) and promotes exchange of gas from the gas pathway through a membrane (such as an HFM) into the fluid pathway. Advantageously, the gas diffusion device 1700 uses sonic energy (such as ultrasound) to facilitate transport of gases into fluids in various systems, such as an ECMO device, at improved rates. The device 1700 could also facilitate gas to gas, or fluid to fluid, or fluid to gas transport. [00101] As shown in Figures 17 and 18, the housing 1710 includes a collection of wall structures supporting a fluid inlet 1712, a fluid outlet 1714, and a plurality of bubble vents 1717a, 1717b. Generally, the wall structures can be any assembly of members that can support the various features of the diffusion device 1700 (including, for example, the membrane module 1730 and the transducer module 1750) and can define the fluid pathway 1770. The housing 1710, for example, includes an outlet plate 1720, an inlet plate 1722, a first annulus 1724 and a second annulus 1726. When assembled, the first and second annuluses 1724, 1726 sandwich the membrane module 1730 therebetween. Similarly, when assembled, the outlet plate 1720 and the inlet plate 1722 bracket the “sandwich” of the annuluses 1724, 1726 and membrane module 1730. [00102] The inlet plate 1722, as shown by the cross-section of Figure 21, includes a stack of three subplates layered onto each other to define a portion of the fluid pathway 1770 and a central opening 1728 (shown, for example, in Figure 23). The inlet plate 1722 – and its subplates – have a bi-lobal shape as shown in Figure 20 with a circular lobe and an elliptical lobe. The plates are held together by a pair of fasteners that transfix the three plates through the elliptical lobe. Also, four fasteners extend through the circular lobe, further securing the three subplates of the inlet plate 1722. [00103] An outer one of the subplates defines a portion of the central opening 1728 configured to accept a transducer 1752 of the transducer module 1750. The remaining two subplates can define the remainder of the central opening 1728 in the inlet plate 1722. For example, the central opening 1728 may have a circular shape defined through all three subplates and sized to receive a circular shaped transducer 1752 as well as to provide a pathway for sonic energy (emitted from the transducer 1752) through the fluid pathway 1770 and toward the membrane module 1730. The middle one of the subplates defines a slot or channel 1760 that extends from the central opening 1728 in the circular lobe to an inlet opening 1762 in the elliptical lobe. The inlet opening 1762 is also formed partially by the inner (relative to the entire assembly 1700) one of the subplates to receive an end of the fluid inlet 1712. [00104] The outlet plate 1720 is on the opposite side of the housing 1710 from the inlet plate 1722 and is also comprised of three subplates in a stacked arrangement. The outlet plate 1720, as shown by the cross-section of Figure 21, defines a portion of the fluid pathway 1770 including a portion of the central opening 1728. The outlet plate 1720 – and its subplates – have a bi-lobal shape as shown in Figure 19 with a circular lobe and an elliptical lobe. The plates are held together by a pair of fasteners that transfix the three plates through the elliptical lobe. Also, four fasteners extend through the circular lobe, further securing the three subplates of the outlet plate 1720. [00105] An outer one of the subplates of the outlet plate 1720 defines an outlet opening 1764 sized and shaped to receive the fluid outlet 1714. The remaining two subplates (middle and inner) can define the central opening 1728 part of the fluid pathway 1770 in the outlet plate 1720. For example, the central opening 1728 may have a circular shape defined to receive and pass the fluid (such as blood) exiting the membrane module 1730. The middle one of the subplates defines a slot or channel 1766 that extends from the central opening 1728 in the circular lobe to the outlet opening 1764 in the elliptical lobe. The outlet opening 1764 is also formed partially by the outer one of the subplates to receive an end of the fluid outlet 1714. An additional, fourth subplate may extend between the second annulus 1726 and the third inner subplate and also define a portion of the central opening 1728, as shown in Figure 21. [00106] The central portion of the housing defining the central opening 1728 and bracketing or sandwiching the membrane module 1730 in the middle is comprised of the first and second annulus 1724, 1726. As shown in Figure 21, the outlet and inlet plates 1720, 1722 abut the outer planar surfaces of the corresponding adjacent ones of the first and second annulus, respectively. Mediating the transition between the plates and annuluses are gaskets 1768 that are nestled in an enlarged portion of the central opening 1728 defined by the inner one of the subplates and a recess defined through the outer surface of the annulus. [00107] Each of the annuluses 1724, 1726 defines a portion of the central opening 1728 such as by defining a centrally placed cylindrical opening. These cylindrical openings align when the annuluses 1724, 1726 are connected to each other and around the membrane module 1730. The four fasteners that extend through the circular lobe of the inlet and outlet plates 1722, 1720 also extend through and hold together the annuluses. [00108] Each of the annuluses 1724, 1726 defines a pair of openings extending from an outside curved surface into the central opening and at right angles to each other. As shown in Figures 17-18 and 21 these openings receive the bubble detection sensors 1715a, 1715b and the bubble vents 1717a, 1717b. Each of these openings may also be sealed by washers or gaskets to mediate the spaces between the sensors or vents of the openings in the annuluses. [00109] The membrane module 1730 includes a membrane manifold 1732 and a hollow fiber membrane (HFM) 1740 that define the gas pathway 1731. For example, when the device 1700 is employed in an ECMO machine, the gas pathway 1731 conducts oxygen or other gases through a pathway where transport occurs into the fluid pathway 1770, such as blood. [00110] The membrane manifold 1732, as shown in Figures 20, 22 and 23, defines the gas pathway 1731 and holds the HFM 1740. The membrane manifold includes a gas inlet 1734, a gas outlet 1735, a bubble trap vent 1736, a central aperture 1738, an inlet-facing surface 1739a and an outlet facing surface 1739b. As seen in Figure 21, the membrane manifold 1732 may be constructed of a pair of subplates including a main subplate including the inlet facing surface 1739a and cover subplate including the outlet facing surface 1739b. The inlet and outlet facing surfaces are named to indicate the direction of flow in the fluid pathway – the inlet facing surface faces fluid coming into the membrane manifold 1732 and the outlet facing surface faces the fluid exiting the membrane manifold 1732, as shown in Figure 21. [00111] The main subplate is machined out to form a majority of the gas pathway 1731, as shown in Figure 22. In particular, the main subplate defines channels extending from the gas inlet 1734 to the central aperture 1738 (holding the HFM 1740), and from the HFM 1740 to the gas outlet 1735. In addition, a side pathway is defined extending from the lateral edges of the HFM 1740 to the bubble trap vent 1736. In addition, as shown in Figure 23, part of the main subplate may form a backboard 1737 that extends into the central aperture 1738 and over the HFM 1740. The backboard 1737 can include a chamfer or other shaping configured to capture and direct bubbles toward the channel leading to the bubble trap vent 1736. The cover subplate primarily covers the main subplate and traps – without cutting off gas flow – the HFM 1740 into place within the manifold 1732. The cover subplate also defines a portion of the central aperture 1738 to provide access for the fluid flow. [00112] The HFM 1740 is constructed primarily of a side-by-side array of individual hollow fibers or lumens 1742a – l742n and includes a gas inlet interface 1744 and a gas outlet interface 1745. An exemplary hollow lumen 1742 is shown in Figure 24 via an electron microscope photograph as a very small polymeric tube that has a microporosity facilitating passage of gases, such as oxygen, through its wall structure and into the surrounding fluid. The gas inlet interface 1744 is a structure to which the lumens 1742 are adhered in the array to position them for receiving the gas flow. The gas outlet interface 1745, similar to the inlet interface, is a structure to which the lumens 1742 are adhered in the array for the exiting gas flow. Together the interfaces 1744, 1745 organize and support the small lumens 1742 and provide a structure to be trapped between the main and cover plates of the membrane manifold 1732. Although the area of the HFM 1740 can be varied and multiple mats can be stacked in blocks or other bulk arrays for different applications, the exemplary HFM 1740 is about 10 inches by 10 inches. [00113] It should be noted that the HFM 1740 can be scaled up to larger numbers of hollow lumens depending on the rate of desired transport. On the other hand, embodiments of the present invention use sonic energy to increase the rate of transport of the membranes formed by the hollow lumens and so, generally, the number of the hollow lumens is substantially reduced compared to configurations not using sonic energy. When the diffusion device 1700 is used for ECMO, for instance, achieving the same rate of oxygenation with smaller surface areas can reduce the amount of exposure of blood to clotting risks. This in turn can reduce the amount of blood thinners employed – such as heparin – thus improving patient outcomes. Similarly, for industrial uses, the reduction in the number and surface area of membranes can reduce clogs or the head needed to drive fluid flows. Also, transport rates can be enhanced without increasing the size or surface area of membranes for transport because of the use of sonic energy. [00114] Generally, the spacing and other positioning of the HFM 1740 (as well as that of multiple, stacked HFMs) can be configured based on the modulation of the ultrasound waves. For example, as described herein multiple HFMs 1740 can be arranged to be at areas of high or low pressure depending on desired effect on membrane transport rate. Also, generally, areas where ultrasound waves cross and cancel each other out would be avoided – although it is expected that few configurations would avoid such cancellation entirely. Control systems described below can modulate the generation of ultrasound by the transducer module 1750 to adapt to the geometry of the chamber, spacing of the mats, desired transport rate, temperature and other factors. [00115] The transducer module 1750 includes a transducer 1752 and a mounting member 1754. As shown in Figure 21, the mounting member 1754 is constructed of multiple subplates similar to the outlet and inlet plates 1720, 1722. There are four subplates including an outer plate and an inner plate sandwiching two middle plates between them. The outer plate and first adjacent middle plate are held together by four fasteners which are offset about 45 degrees from the fasteners attaching the transducer module 1750 to the housing 1710. The transducer itself extends through and is secured within a central circular opening (Figure 20) and is encircled by a pair of washers or gaskets to mediate leakage from the fluid pathway 1770. The transducer has a cylindrical shape and extends out of the mounting member 1754 at its inner and outer surfaces. On the inner surface, the transducer 1752 extrudes into the central opening 1728 defined by the housing 1710, as described above in more detail. [00116] The transducer module 1750 need not be limited to a single transducer 1752 but could have an array of transducers, such as an array of parallel transducers that extend along a rectangular mat of hollow fibers. [00117] The bubble detection sensors 1715a, 1715b and the bubble vents 1717a, 1717b can detect bubbles and/or vent those bubbles away out of the fluid pathway 1770. Generally, air bubbles flow to the top of the fluid pathway and are suctioned out by the bubble vents which have a position at the top of the fluid pathway. [00118] The fluid inlet 1712 and outlet 1714 are tubular fixtures that provide attachment points for tubing with serrated outer nozzle portions and have inner portions that are encircled by fixation collars which can be transfixed by fasteners to attach them to the inlet plate 1722 and outlet plate 1720, respectively. Any type of inlet or outlet that can receive and communicate fluids to the various pathways (gas or fluid) can be used for the diffusion device 1700. [00119] Returning to Figure 21, the fluid pathway 1770 starts at the fluid inlet 1712 and extends down into the channel 1760 defined by the inlet plate 1722. Then the fluid pathway extends into the central opening 1728, over the inner face of the transducer 1752, toward the membrane module 1730. Then the fluid pathway extends through the HFM 1740 where it and the gas pathway 1731 intersect. The transducer module 1750 bathes the HFM 1740 in ultrasound which, through various processes described elsewhere herein, facilitates the transport of the gas from the gas pathway 1731 into the fluid pathway 1770 (e.g., diffusion of oxygen from the gas pathway 1731, through the HFM 1740, and into blood in the fluid pathway 1770). (Note in some aspects transport will be between gases or between fluids (such as dialysis) or fluid to gas.) In addition, diffusion can occur from the fluid pathway 1770 into the gas pathway 1731 (e.g., CO ₂ diffusing from the blood in the fluid pathway 1770 into the HFM 1740 and into the gas pathway 1731). [00120] Once the gas concentration in the fluid has been increased, the fluid pathway 1770 extends through the remainder of the central opening 1728 toward the channel 1766 defined in the outlet plate 1720. The fluid pathway 1770 continues to extend toward and out of the fluid outlet 1714 for delivery, for example, to a patient via the remainder of the ECMO machine. In this manner, the fluid inlet 1712 and fluid outlet 174 can be attached to the rest of a mechanism that handles access and return of a fluid, such as an ECMO machine that will handle removal of blood needing oxygen from a patient and returning the oxygenated blood to the patient. The diffusion device 1700 could also be used in other existing applications such as hemodialysis and water filtration, for example. Also portions of the device may be regularly replaceable such as the membrane module 1730 for the purposes of cleaning or refreshing of the HFM. Also, the device 1700 is not limited necessarily to an HFM but could also be used with parallel planar or other shaped membranes. [00121] As shown in Figure 22, the gas pathway 1731 (which might be another fluid pathway) extends from the gas inlet 1734 through the membrane manifold 1732 toward the gas inlet interface 1744, through the hollow fibers of the HFM 1740, and out the gas outlet interface 1745. The gas pathway 1731 extends from the HFM 1740 through the membrane manifold 1732 toward the gas outlet 1735. In this manner, the gas can be transported out of the walls of the hollow fibers and into the fluid pathway 1770. [00122] Generally, without being wed to theory, the diffusion device 1700 routes the gas through the inner hollow portions of every one of the hollow fibers. The transducer 1752 transmits ultrasound to the HFM 1740 and surrounding blood. Microstreaming occurs at each individual pores of the gas/liquid interface at the surface of each hollow fiber. Gas permeates through the walls of the hollow fibers. Menisci in the pores between the blood and gas at the surface of the hollow fibers experience a pressure differential from the ultrasound. The menisci fluctuate or oscillate in and out of the pores and create micro-vortexes or push into the fluid which stirs the fluid up for increased transport. Again, without being wed to theory, it is believed that the blood mixing around the membrane disrupts laminar flow and improves the efficiency of gas transport. [00123] Increasing diffusion efficiency can result in decreased foreign surface area in contact with biological tissues. The amount of foreign surface area and the time of exposure may be decreased to improve patient outcomes. For example, the device can improve patient outcomes by reducing the use of anti-coagulants. Also reducing surface area reduces biofouling of the diffusion device 1700 and or the entire system. [00124] Fig. 25 shows an example computing environment in which example embodiments of control and operation of enhanced transport systems disclosed herein and aspects thereof may be implemented in, e.g., a diffusion device or devices including a diffusion device, among others. The computing device environment is only one example of a suitable computing environment and is not intended to suggest any limitation as to the scope of use or functionality. [00125] Numerous other general-purpose or special purpose computing devices environments or configurations may be used. Examples of well-known computing devices, environments, and/or configurations that may be suitable for use include, but are not limited to, personal computers, server computers, handheld or laptop devices, mobile phones, wearable devices, multiprocessor systems, microprocessor-based systems, network personal computers (PCs), minicomputers, mainframe computers, embedded systems, distributed computing environments that include any of the above systems or devices, and the like. [00126] Computer-executable instructions, such as program modules, being executed by a computer may be used. Generally, program modules include routines, programs, objects, components, data structures, etc. that perform particular tasks or implement particular abstract data types. Distributed computing environments may be used where tasks are performed by remote processing devices that are linked through a communications network or other data transmission medium. In a distributed computing environment, program modules and other data may be located in both local and remote computer storage media including memory storage devices. [00127] With reference to Fig. 25, an example system for implementing aspects described herein includes a computing device, such as computing device 1400. In its most basic configuration, computing device 1400 includes at least one processing unit 1402 and memory 1404. Depending on the exact configuration and type of computing device, memory 1404 may be volatile (such as random-access memory (RAM)), non-volatile (such as read-only memory (ROM), flash memory, etc.), or some combination of the two. This most basic configuration is illustrated in Figure 25 by dashed line 1406. Computing device 1400 may have additional features/functionality. For example, computing device 1400 may include additional storage (removable and/or non-removable) including, but not limited to, magnetic or optical disks or tape. Such additional storage is illustrated in Figure 25 by removable storage 1408 and non-removable storage 1410. Computing device 1400 can include a variety of computer readable media. Computer readable media can be any available media that can be accessed by the device 1400 and includes both volatile and non-volatile media, removable and non-removable media. Computer storage media include volatile and non-volatile, and removable and non-removable media implemented in any method or technology for storage of information such as computer readable instructions, data structures, program modules or other data. Memory 1404, removable storage 1408, and non-removable storage 1410 are all examples of computer storage media. Computer storage media include, but are not limited to, RAM, ROM, electrically erasable program read-only memory (EEPROM), flash memory or other memory technology, CD-ROM, digital versatile disks (DVD) or other optical storage, magnetic cassettes, magnetic tape, magnetic disk storage or other magnetic storage devices, or any other medium which can be used to store the desired information, and which can be accessed by computing device 1400. Any such computer storage media may be part of computing device 1400. Computing device 1400 may contain communication connection(s) 1412 that allow the device to communicate with other devices. Computing device 1400 may also have input device(s) 1414 such as a keyboard, mouse, pen, voice input device, touch input device, etc., singly or in combination. Output device(s) 1416 such as a display, speakers, printer, vibratory mechanism, etc. may also be included singly or in combination. All these devices are well known in the art and need not be discussed at length here. [00128] Figure 26 illustrates examples of computers 1300, including ones with the structure shown in Figure 25, that may include the kinds of software programs, data stores, and hardware that can implement control of the enhanced transport systems disclosed and described herein according to certain embodiments. As shown, the computing system 1300 includes, without limitation, a central processing unit (CPU) 1305, a network interface 1315, a memory 1320, and storage 1330, each connected to a bus 1317. The computing system 1300 may also include an I/O device interface 1310 connecting I/O devices 1312 (e.g., keyboard, display and mouse devices) to the computing system 1300. Further, the computing elements shown in computing system 1300 may correspond to a physical computing system (e.g., a system in a data center) or may be a virtual computing instance executing within a computing cloud. [00129] The CPU 1305 retrieves and executes programming instructions stored in the memory 1320 as well as stored in the storage 1330. The bus 1317 is used to transmit programming instructions and application data between the CPU 1305, I/O device interface 1310, storage 1330, network interface 1315, and memory 1320. Note, CPU 1305 is included to be representative of a single CPU, multiple CPUs, a single CPU having multiple processing cores, and the like, and the memory 1320 is generally included to be representative of a random access memory. The storage 1330 may be a disk drive or flash storage device. Although shown as a single unit, the storage 1330 may be a combination of fixed and/or removable storage devices, such as fixed disc drives, removable memory cards, optical storage, network attached storage (NAS), or a storage area-network (SAN). [00130] Illustratively, the memory 1320 includes a temperature control component 1340, a fluid flow rate control component 1342, a gas flow rate control component 1344, and a transducer control component 1346, all of which are discussed in greater detail above. Further, storage 1330 includes temperature data 1348, fluid flow rate data 1350, gas flow rate data 1352, transducer data 1354, ultrasound data 1356 and transport data 1358, all of which are also discussed in greater detail elsewhere herein. Generally, embodiments of enhanced transport systems described herein can have sensors for collecting temperature data along the fluid and/or gas flow paths, flow rate (e.g., pressure sensors) data for the fluids and gases, electrical data for controlling the operation of the transducer, ultrasound data for determining the output of the transducer and transport data for determining the effectiveness of the transport across the membrane. As also disclosed above, embodiments may include bubble detection and generation mechanisms which can supply bubble data and control the generation or removal of bubbles in liquids of the various transport systems. [00131] The device 1700 may also include an oxygen sensor in the gas flow path 1731. In this case, the gas flow rate control component 1344 may monitor the percent Oxygen (%O2) concentration of the “sweep gas” that is sent through the HFM. This allows increasing or decreasing %O2 in response to patient needs, such as when the transport data 1358 indicates patient blood oxygen levels are dropping. [00132] The transducer control component 1346 may be configured to monitor the power consumption of the transducer which may indicate overheating and/or failure. The transducer control component then, for example, could reduce power or shut off power or send a warning not the operator. [00133] The computer systems disclosed herein can modulate the operation of the various controls to study, improve or optimize the transport data. For example, when used with ECMO, the blood temperature can be monitored with sensors, data from those sensors (temperature data 1348) stored and used as feedback to the temperature control component 1340 to maintain blood temperature within certain ranges. Also, the performance of the transport across the membrane can be monitored and collected to inform the temperature control component and its control of blood heating and cooling as part of the ECMO system. In another aspect, the pressure of the gas and fluids can be sensed and controlled to enhance membrane transport. In addition, controls may be used to enhance the safety of the system or needs of a patient. For example, the pressure within the system may be monitored to adjust fluid or gas flow rates to avoid pressure spikes. Bubbles may also be monitored for creation, control or removal. Also, the needs of the patient may be monitored and used as a closed loop feedback control for the system, for example to supply a certain amount of oxygen, the system may increase fluid (blood) and gas flow rates. [00134] In yet another aspect, the inputs to the transducer(s) can be controlled using the transducer control component 1346. The transducer could be electrically excited, for example with a 1MHz sine wave or could be pulsed with alternating on/off cycles. The temperature of the transducer can be monitored and overheating avoided by flowing cooled fluids for the transducer or the remainder of the system, such as the fluid or gas flow paths. [00135] It should be understood that the various techniques described herein may be implemented in connection with hardware components or software components or, where appropriate, with a combination of both. Illustrative types of hardware components that can be used include Field-programmable Gate Arrays (FPGAs), Application-specific Integrated Circuits (ASICs), Application-specific Standard Products (ASSPs), System-on-a-chip systems (SOCs), Complex Programmable Logic Devices (CPLDs), etc. The methods and apparatus of the presently disclosed subject matter, or certain aspects or portions thereof, may take the form of program code (i.e., instructions) embodied in tangible media, such as floppy diskettes, CD- ROMs, hard drives, or any other machine-readable storage medium where, when the program code is loaded into and executed by a machine, such as a computer, the machine becomes an apparatus for practicing the presently disclosed subject matter. [00136] Although certain implementations may refer to utilizing aspects of the presently disclosed subject matter in the context of one or more stand-alone computer systems, the subject matter is not so limited but rather may be implemented in connection with any computing environment, such as a network or distributed computing environment. Still further, aspects of the presently disclosed subject matter may be implemented in or across a plurality of processing chips or devices, and storage may similarly be effected across a plurality of devices. Such devices might include personal computers, network servers, and handheld devices, for example. [00137] Figure 27 shows a graph depicting enhanced diffusion of CO ₂ across the HFM 1740 as a function of increasing the power of the ultrasound-emitting transducer 1752, where a 1MHz ultrasound test was performed on CO ₂ primed DI water and the rate of diffusion through membranes was measured by recording CO2 PPM in a gas outlet line. As reflected in Figure 27, CO ₂ -primed deionized water (“DI water”) was pumped along the fluid pathway 1770 at 150 ml/min (e.g., into the fluid inlet 1712 and out of the fluid outlet 1714) while O ₂ gas (“sweep gas”) was passed through the gas pathway 1731 at 300 ml/min (e.g., into the gas inlet 1734, through the HFM 1740, and out of the gas outlet 1735). Simultaneously, the transducer 1752 was powered to emit 1 MHz ultrasound at different power levels (e.g., 0 Vpp, 2 Vpp, 3 Vpp, and 4 Vpp). [00138] As shown in Figure 27, the diffusion of CO ₂ from the DI water into the sweep gas increased as a function of the transducer’s power. For example, when the transducer’s power was set to 0 Vpp, the average measured CO ₂ in the sweep gas was 1069.35 ppm. When the transducer’s power was increased to 2 Vpp, the average measured CO ₂ in the sweep gas was 1345.79 ppm. When the transducer’s power was increased to 3 Vpp, the average measured CO ₂ in the sweep gas was 1507.78 ppm. And when the transducer’s power was increased to 4 Vpp, the average measured CO ₂ in the sweep gas was 1732.86 ppm. Thus, the results in Figure 27 demonstrate that the ultrasound emitted by the transducer 1752 enhances the rate of diffusion of CO ₂ from the DI water, through the HFM 1740, and into the sweep gas, and does so with increasing effectiveness as the transducer power is increased. [00139] Exemplary Aspects: [00140] In view of the described processes and compositions, hereinbelow are described certain more particularly described aspects of the disclosures. These particularly recited aspects should not, however, be interpreted to have any limiting effect on any different claims containing different or more general teachings described herein, or that the “particular” aspects are somehow limited in some way other than the inherent meanings of the language and formulas literally used therein. [00141] Example 1: An apparatus for diffusing gases into blood comprising a porous membrane, blood on one side of said porous membrane, a gas on the other side of said membrane, and an ultrasound source configured to direct ultrasound energy into the blood, aimed toward said membrane. [00142] Example 2: The apparatus according to any example herein, particularly example 1, further comprising a membrane with pore size between 0 to 1nm, 1nm to 3nm, 3nm to 5nm, 5nm to 10nm, 10nm to 100nm, 100nm to 500nm, or 500nm to 1 micrometer. [00143] Example 3: The apparatus according to any example herein, particularly example 1, comprising a membrane made out of polypropylene (PP), or polymethyl pentene (PMP) or polytetrafluoroethylene (PTFE) or polyvinylidene fluoride (PVDF) or a composite made out of polyvinylidene fluoride and inorganic oxides. [00144] Example 4: The apparatus according to any example herein, particularly example 1, further comprising of a hollow fiber membrane (HFM) with lumen size 10-50μ, 50-100μ, 100-200μ, 200-300μ, 300-400μ, 400-500μ, 500-600μ, or 600-700μ. [00145] Example 5: The apparatus according to any example herein, particularly example 1, further comprising of a plurality of HFMs bundled together. [00146] Example 6: The apparatus according to any example herein, particularly example 1, further comprising an ultrasound source device which creates sound waves between 20KHz to 100KHz, 100KHz to 1MHz, 1 MHz to 10 MHz, or 10 MHz to 100 MHz. [00147] Example 7: The apparatus according to any example herein, particularly example 1, further comprising an ultrasound source configured to direct ultrasound energy along a direction perpendicular to said membrane. [00148] Example 8: The apparatus according to any example herein, particularly example 1, further comprising an ultrasound source configured to direct ultrasound energy along a direction tangential to said membrane. [00149] Example 9: The apparatus according to any example herein, particularly example 1, further comprising an ultrasound source configured to direct ultrasound energy along a direction at an angle between parallel and perpendicular to said membrane. [00150] Example 10: The apparatus according to any example herein, particularly example 1, where the gas is oxygen. [00151] Example 11: The apparatus according to any example herein, particularly example 1, where the gas is a combination of oxygen and nitrogen. [00152] Example 12: The apparatus according to any example herein, particularly example 1, where the gas is a combination of several gases, which can include oxygen, nitrogen, carbon dioxide, argon, nitric oxide, and any gases commonly found in air. [00153] Example 13: An apparatus for enhanced diffusion of gases into blood comprising a porous membrane, blood on one side of said porous membrane, a gas on the other side of said membrane, and an acoustic device placed in the gas in the vicinity of the porous membrane. [00154] Example 14: The apparatus according to any example herein, particularly example 13, further comprising a membrane with pore size between 0 to 1nm, 1nm to 3nm, 3nm to 5nm, 5nm to 10nm, 10nm to 100nm, 100nm to 500nm, or 500nm to 1 micrometer. [00155] Example 15: The apparatus according to any example herein, particularly example 13, comprising a membrane made out of polypropylene (PP), or polymethyl pentene (PMP) or polytetrafluoroethylene (PTFE) or polyvinylidene fluoride (PVDF) or a composite made out of polyvinylidene fluoride and inorganic oxides. [00156] Example 16: The apparatus according to any example herein, particularly example 13, further comprising of a hollow fiber membrane (HFM) with lumen size 10-50μ, 50-100μ, 100-200μ, 200-300μ, 300-400μ, 400-500μ, 500-600μ, or 600-700μ. [00157] Example 17: The apparatus according to any example herein, particularly example 13, further comprising of a plurality of HFMs bundled together. [00158] Example 18: The apparatus according to any example herein, particularly example 13, further comprising an acoustic device which creates sound waves between 0KHz to 100KHz, 100KHz to 1MHz, 1 MHz to 10 MHz, or 10 MHz to 100 MHz. [00159] Example 19: The apparatus according to any example herein, particularly example 13, further comprising an ultrasound source configured to direct ultrasound energy along a direction perpendicular to said membrane. [00160] Example 20: The apparatus according to any example herein, particularly example 13, further comprising an ultrasound source configured to direct ultrasound energy along a direction parallel to said membrane. [00161] Example 21: The apparatus according to any example herein, particularly example 13, further comprising an ultrasound source configured to direct ultrasound energy along a direction at an angle between parallel and perpendicular to said membrane. [00162] Example 22: An apparatus for the diffusion of excretable solutes in blood into a secondary solution comprising a porous membrane, blood on one side of said porous membrane, a liquid with osmotic pressure similar to blood on the other side of said membrane and an ultrasound source configured to direct ultrasound energy toward said membrane. [00163] Example 23: The apparatus according to any example herein, particularly example 22, further comprising a membrane with pore size between 0 to 1nm, 1nm to 3nm, 3nm to 5nm, 5nm to 10nm, or 10nm to 100nm. [00164] Example 24: The apparatus according to any example herein, particularly example 22, comprising a membrane made out of polysulfone, or polyether sulfone or polymethyl methacrylate or sulfonated polyacrylonitrile. [00165] Example 25: The apparatus according to any example herein, particularly example 22, further comprising of a hollow fiber membrane (HFM). [00166] Example 26: The apparatus according to any example herein, particularly example 22, further comprising of a plurality of HFMs formed into a bundle. [00167] Example 27: The apparatus according to any example herein, particularly example 22, further comprising an acoustic device which generates ultrasound between 20KHz to 100KHz, 100KHz to 1MHz, 1 MHz to 10 MHz, or 10 MHz to 100 MHz. [00168] Example 28: The apparatus according to any example herein, particularly example 22, further comprising an ultrasound source configured to direct ultrasound energy along a direction perpendicular to said membrane. [00169] Example 29: The apparatus according to any example herein, particularly example 22, further comprising an ultrasound source configured to direct ultrasound energy along a direction parallel to said membrane. [00170] Example 30: The apparatus according to any example herein, particularly example 22, further comprising an ultrasound source configured to direct ultrasound energy along a direction at an angle between parallel and perpendicular to said membrane. [00171] Example 31: The apparatus according to any example herein, particularly example 22, wherein the ultrasound source is placed in the blood on the blood side of said membrane. [00172] Example 32: The apparatus according to any example herein, particularly example 22, wherein the ultrasound source is placed in the liquid side (not the blood side) of said membrane. [00173] Example 33: The apparatus according to any example herein, particularly example 22, where the non-blood liquid is dialysate. [00174] Example 34: A method of improving the gas transfer through a porous membrane into blood comprising the use of ultrasound energy passed through the blood. [00175] Example 35: The method according to any example herein, particularly example 34, where the ultrasound energy in the blood is between 0KHz to 100KHz, 100KHz to 1MHz, 1 MHz to 10 MHz, or 10 MHz to 100 MHz. [00176] Example 36: The method according to any example herein, particularly example 34, where the ultrasound energy is directed from the blood towards the membrane. [00177] Example 37: The method according to any example herein, particularly example 34, where the ultrasound energy is directed in the blood tangentially to the membrane. [00178] Example 38: A method of improving gas transfer through a porous membrane into blood comprising the application of acoustic energy through a gas on the gas side of the membrane. [00179] Example 39: The method according to any example herein, particularly example 38, where the acoustic energy is directed at the membrane. [00180] Example 40: The method according to any example herein, particularly example 34, where the acoustic energy in the gas is between 1 Hz to 100KHz, 100KHz to 1MHz, 1 MHz to 10 MHz, or 10 MHz to 100 MHz. [00181] Example 41: An apparatus for enhancing the diffusion of gases into blood comprising, an acoustically active porous membrane, blood on one side of said porous membrane, a gas on the other side of said membrane. [00182] Example 42: An apparatus for the diffusion of excretable solutes in blood into a secondary solution comprising an acoustically active porous membrane, blood on one side of said porous membrane, and a liquid with osmotic pressure similar to blood on the other side of said membrane. [00183] Example 43: An apparatus for the diffusion of excretable solutes in blood into a secondary solution comprising a porous membrane with gas bubbles adhered to its surface or embedded within it, blood on one side of said porous membrane, a liquid with osmotic pressure similar to blood on the other side of said membrane, and an ultrasound source configured to direct ultrasound energy towards said membrane. [00184] Example 44: An apparatus for diffusing gases into blood comprising, a porous membrane with gas bubbles adhered to its surface or embedded within it, blood on one side of said porous membrane, a gas on the other side of said membrane and an ultrasound source configured to direct ultrasound energy into the blood. [00185] Example 45: The apparatus according to any example herein, particularly examples 43 or 44, wherein said bubbles are anchored to a pattern of hydrophobic regions on said membrane. [00186] Example 46: The apparatus according to any example herein, particularly examples 43 or 44, wherein said bubbles are encapsulated and said encapsulated bubbles are anchored to said membrane. [00187] Example 47: The apparatus according to any example herein, particularly examples 43 or 44, wherein said bubbles are encapsulated within said membrane. [00188] Example 48: An apparatus for diffusing gases into blood comprising a porous membrane, blood on one side of said porous membrane, a gas on the other side of said membrane, a bubble injector that injects bubbles into said blood. [00189] Example 49: An apparatus for the diffusion of excretable solutes in blood into a secondary solution comprising a porous membrane, blood on one side of said porous membrane, a liquid with osmotic pressure similar to blood on the other side of said membrane, an ultrasound source configured to direct ultrasound energy within said blood and / or said liquid, a bubble injector that injects bubbles into said liquid and / or said blood. [00190] Example 50: The apparatus according to any example herein, particularly examples 1 or 13 or 34 or 38 or 41 or 44 or 48, wherein the membrane is naturally hydrophobic and coated with a biocompatible coating at least in the blood contacting side. [00191] Example 51, The apparatus according to any example herein, particularly example 50, wherein the biocompatible coating is either immobilized heparin, protein, phosphocholine functionalized lipids or polymers, or polyethylene glycol. [00192] Example 52: The apparatus according to any example herein, particularly examples 22 or 42 or 43 or 49 wherein the membrane is hydrophilic by nature or coated with a hydrophilic coating to improve its biocompatibility. [00193] Example 53: The apparatus according to any example herein, particularly example 52, wherein the biocompatible coating on the membrane includes poly-N- vinylpyrrolidinone (PVP), polyethylene co-vinyl alcohol and polyethylene glycol, poly sulfobetaine methacrylate, or sulfobetaine silane. [00194] Example 54: The apparatus according to any example herein, particularly example 52, wherein the biocompatible coating partially neutralizes the zeta potential of porous membrane allowing highly negatively charged solutes, such as inorganic phosphates, to pass through. [00195] Example 55: An apparatus for the diffusion of excretable solutes in blood into a secondary solution comprising a porous membrane, blood on one side of said porous membrane, a liquid with osmotic pressure similar to blood on the other side of said membrane, an ultrasound source and an optional acoustic device. [00196] Example 56: The apparatus according to any example herein, particularly example 55, wherein the excretable solute includes urea, inorganic phosphate or any other small molecule with molecular weight < 1KDa. [00197] Example 57: The apparatus according to any example herein, particularly example 55, wherein the excretable solute includes β-microglobulin or any macromolecule with molecular weight ranging between 1-5 KDa, 5-10 KDa, or 10-15 KDa. [00198] Example 58: The apparatus according to any example herein, particularly example 55, wherein the porous membrane does not allow macromolecules of >59KDa molecular weight to pass through. [00199] Example 59: The apparatus according to any example herein, particularly example 55, wherein the membrane allows water to remove 1-10 ml/h/mmHg/m2, 10-20 ml/h/mmHg/m2, 20-40 ml/h/mmHg/m2, or 40-80 ml/h/mmHg/m2. [00200] Example 60: A system for enhancing transport of a matter between a first medium and a second medium, the system comprising a membrane separating the first medium from the second media wherein the first media contacts at least one surface area of the membrane, and at least one transducer configured to direct acoustic energy into the first medium proximate the at least one surface area of the membrane to accelerate transport of the matter from the first media into the second media. [00201] Example 61: The system according to any example herein, particularly example 60, wherein the first medium has a higher concentration of the matter than the second medium. [00202] Example 62: The system according to any example herein, particularly example 60, wherein the second medium has a higher concentration of the matter than the first medium. [00203] Example 63: The system according to any example herein, particularly examples 60 or 61, wherein the first medium is blood and wherein the matter includes oxygen. [00204] Example 64: The system according to any example herein, particularly example 60, wherein the matter transport is enhanced by at least about twofold. [00205] Example 65: The system according to any example herein, particularly example 60, wherein the matter transport is enhanced by at least about one of threefold, fourfold, fivefold or sixfold. [00206] Example 66: The system according to any example herein, particularly example 60, further comprising a source of bubbles coupled to at least one of the first media or second media and configured to inject a plurality of bubbles thereinto. [00207] Example 67: The system according to any example herein, particularly example 60, wherein the acoustic energy has a frequency of at least 20KHz. [00208] Example 68: The system according to any example herein, particularly example 60, wherein the at least one transducer includes a focusing mechanism configured to focus the acoustic energy toward the at least one surface area. [00209] Example 69: The system according to any example herein, particularly example 60, wherein the at least one surface area of the membrane is free of interfering deposits from the first medium. [00210] Example 70 The system according to any example herein, particularly example 60, wherein the at least one transducer is configured to generate a near-field and far- field transition near the at least one surface area of the membrane. [00211] Example 71: The system according to any example herein, particularly example 70, wherein the at least one transducer is configured to auto-focus the near-field and far field transition. [00212] Example 72: The system according to any example herein, particularly example 60, wherein the at least one transducer is physically focused to localize the acoustic field near to the transducer. [00213] Example 73: The system according to any example herein, particularly example 60, wherein the at least one transducer is configured to present a flat surface to the first medium. [00214] Example 74: The system according to any example herein, particularly example 60, wherein the at least one transducer includes a phased array focusing system. [00215] Example 75: The system according to any example herein, particularly example 74, wherein the phased array focusing system is configured to steer the acoustic energy. [00216] Example 76: The system according to any example herein, particularly example 60, wherein the at least one transducer includes a plurality of transducers in a checkerboard pattern. [00217] Example 77: The system according to any example herein, particularly example 76, wherein white transducers of the checkerboard pattern are configured to alternate with black transducers of the checkboard pattern in directing acoustic energy. [00218] Example 78: The system according to any example herein, particularly example 60, wherein the at least one transducer includes an encapsulant acoustically matched to the first medium. [00219] Example 79: The system according to any example herein, particularly example 60, further comprising a thermal management system associated with the transducer. [00220] Example 80: The system according to any example herein, particularly example 60, wherein the membrane is associated with a plurality of bubbles. [00221] Example 81: The system according to any example herein, particularly example 80, wherein the bubbles are contained within the membrane. [00222] Example 82: The system according to any example herein, particularly example 60, wherein the membrane is a hollow fiber membrane. [00223] Example 83: The system according to any example herein, particularly example 82, wherein the at least one transducer is further configured to inhibit deposition of proteins on the hollow fiber membrane via directed acoustic energy. [00224] Example 84: A method of enhancing transport of a matter from a first medium across a membrane to a second medium, the method comprising supplying power to at least one transducer to generate acoustic energy, directing the acoustic energy into the first medium proximate at least one surface area of the membrane, and accelerating transport of the matter from the first medium through the membrane into the second medium using the acoustic energy. [00225] Example 85: The method according to any example herein, particularly example 84, wherein accelerating transport includes accelerating transport by at least one of about twofold, threefold, fourfold, fivefold or sixfold. [00226] Example 86: The method according to any example herein, particularly example 85, further comprising injecting a plurality of bubbles into the first medium. [00227] Example 87: The method according to any example herein, particularly example 84, further comprising focusing the acoustic energy toward the at least one surface area. [00228] Example 88: The method according to any example herein, , particularly example 84, further comprising directing acoustic energy to prevent interfering deposits on the membrane. [00229] Example 89: The method according to any example herein, particularly example 84, further comprising generating a near field and far-field transition near the at least one surface area of the membrane. [00230] Example 90: The method according to any example herein, particularly example 84, wherein the at least one transducer includes a plurality of transducers arranged in a checkerboard pattern and further comprising alternating white transducers with black transducers. [00231] Example 91: The method according to any example herein, particularly example 84, further comprising managing a temperature of the first medium. [00232] Example 92: The method according to any example herein, particularly example 84, wherein the one of the first or second media includes a dialysate and the matter includes a waste product. [00233] Example 93: The system according to any example herein, particularly example 60, wherein the one of the first or second media includes a dialysate and the matter includes a waste product. [00234] Example 94: The system according to any example herein, particularly example 60, wherein the at least one transducer includes an acoustically active component of the membrane. [00235] Example 95: A system for enhancing transport of waste products between blood and dialysate, the system comprising a dialysis membrane separating the blood from the dialysate wherein the blood contacts at least one surface area of the membrane and the dialysate contacts an opposite surface area of the membrane, and at least one transducer configured to direct acoustic energy into one of the blood or dialysate proximate the at least one surface area and the opposite surface area of the membrane to accelerate transport of the waste products from the blood into the dialysate. [00236] Example 96: The system according to any example herein, particularly example 95, wherein the waste products are excretable solutes. [00237] Example 97: The system according to any example herein, particularly example 96, wherein the excretable solute includes urea, inorganic phosphate or any other small molecule with molecular weight < 1KDa. [00238] Example 98: The system according to any example herein, particularly example 95, wherein the dialysate has an osmotic pressure similar to the blood. [00239] Example 99: The system according to any example herein, particularly example 95, further comprising a bubble injector configured to inject bubbles into one of the blood or the dialysate. [00240] Example 100: The system according to any example herein, particularly example 95, wherein the waste products transport is enhanced by at least about one of twofold, threefold, fourfold, fivefold or sixfold. [00241] Although several embodiments of the invention have been disclosed in the foregoing specification, it is understood by those skilled in the art that many modifications and other embodiments of the invention will come to mind to which the invention pertains, having the benefit of the teaching presented in the foregoing description and associated drawings. It is thus understood that the invention is not limited to the specific embodiments disclosed hereinabove and that many modifications and other embodiments are intended to be included within the scope of the appended claims. Moreover, although specific terms are employed herein, as well as in the claims which follow, they are used only in a generic and descriptive sense and not for the purposes of limiting the described invention nor the claims which follow. We, therefore, claim as our invention all that comes within the scope and spirit of these claims.