Abstract:
Exemplary embodiments of devices and methods for treating a lung including, for example, treatments for chronic obstructive pulmonary disease are disclosed. A device may include a plurality of media and a deployment member. The media may be configured for deployment into one or more airways of a lung. The deployment member may be configured for insertion into or proximate the one or more airways of the lung. Also, the deployment member may be configured to deploy the plurality of media substantially simultaneously. Further, the plurality of media may be configured to be retained within the one or more airways of the lung.

Description:
CROSS REFERENCE TO RELATED APPLICATIONS 
     This application claims the benefit of U.S. Provisional Application No. 61/864,075, filed Aug. 9, 2013, the disclosure of which is incorporated herein by reference in its entirety. 
    
    
     TECHNICAL FIELD 
     The disclosed embodiments relate to devices and methods for treating a lung and, in an embodiment, chronic obstructive pulmonary disease (COPD). More particularly, the present disclosure relates to devices and methods of manipulating airways of lungs. 
     BACKGROUND 
     Chronic obstructive pulmonary disease (COPD) is a serious progressive lung disease which makes it harder to breath. It currently affects over fifteen million people in the United States alone and is currently the third leading cause of death in the country. The overwhelming primary cause of COPD is inhalation of cigarette smoke, responsible for over 90% of COPD cases. The economic and social burden of the disease is both substantial and increasing. 
       FIG. 1  illustrates the anatomy of healthy lungs  100  including the trachea or wind pipe  102 . As air flows in through the nose and mouth of an individual, the trachea  102  delivers the air to the lungs  100  for respiratory functions. The trachea  102  divides into the right main stem bronchus  104  and the left main stem bronchus  108 . The right main stem bronchus  104  enters the right lung  106 - 1  and the left main stem bronchus  108  enters the left lung  106 - 2 . In the lungs  100 , both the right main stem bronchus  104  and the left main stem bronchus  108  divide into a plurality of bronchi  110 , which further divide into a plurality of smaller airways referred to as bronchioles  112 . Finally, these bronchioles  112  terminate into a plurality of alveoli  114 . The alveoli  114  are small elastic air sacs which enable gas exchange. That is, they permit oxygen diffusion into the blood stream, and receive and expel CO 2  during exhalation. 
     During inhalation, air is delivered to the lungs  100  and is received within the alveoli  114  via the bronchial passages or airways including the right and left main stem bronchi  104  and  108 , bronchi  110 , and bronchioles  112 . The air inflates the alveoli  114 , which later recoils to exhale air. This operation of lungs  100  during the inhalation and exhalation of air may be disturbed due to certain malfunctions or diseases, such as chronic obstructive pulmonary disease (COPD). 
     COPD includes both chronic bronchitis and emphysema.  FIG. 2A  illustrates a left lung  200  suffering from chronic bronchitis, which is shown in more detail in  FIG. 2B . Chronic bronchitis is characterized by chronic cough with increased sputum, expelled mucus and saliva, production. Chronic bronchitis also causes airway inflammation  204 , mucus hyper-secretion  206  that lines airway walls, airway hyper-responsiveness, and eventual fibrosis of the airway walls, which causes a serious limitation on airflow and gas exchange. The diameter of airways may also be reduced by one or more bronchoconstrictions  208 , which constrict the airways in the lungs due to the tightening of surrounding smooth muscle. Airway restrictions may significantly increase the resistance to airflow through the airways, thereby preventing air from reaching or being expelled from alveoli  214 . This resistance may be calculated according to Poiseulle&#39;s Equation (Equation 1) relating to laminar flow through a tubular member: 
                   R   =       8   ⁢           ⁢   η   ⁢           ⁢   l       π   ⁢           ⁢     r   4                 (   1   )               
Where:
 
R=Resistance to flow
 
η=viscosity of fluid (here, air)
 
l=length of tube (i.e., airway)
 
r=radius of the tube (i.e., airway)
 
     Equation 1 indicates that the resistance to the flow of fluid, i.e., air, is proportional to the fourth power of the radius of the tube, i.e., airway. Thus, if the radius of the airway is reduced to half, the resistance to airflow in the lungs becomes 16 times the normal resistance. This increased resistance or limitation to airflow due to chronic bronchitis causes insufficient removal of carbon dioxide (CO 2 ) from the lung  200 , and manifests into hypercapnia (high blood gas levels of carbon dioxide). Hypercapnia leads to acidosis (lowering of blood pH levels), which correlates to a significantly greater risk of mortality. 
     There are thousands of small airways in the lungs and expanding or maintaining patency of these airways may facilitate better ventilation. However, due to the vast number of small airways, expansion or patency of these adversely affected airways may be very difficult. Moreover, breathing causes significant expansion and contraction of airways which may make deployment of rigid or semi-rigid airway support structures challenging and possibly impractical. 
       FIG. 3A  illustrates a left lung  300  suffering from emphysema, which is shown in more detail in  FIG. 3B . Emphysema is characterized by the destruction of the lung parenchyma, the functioning portions of the lung. The parenchyma includes alveoli walls, bronchioles, and bronchi. Destruction of the lung parenchyma may lead to loss of elastic recoil and tethering (i.e., ability to hold open walls of airways, including the bronchioles  112 , leading to the alveoli  314  throughout much of inhalation and expiration), which maintains airway patency. Unlike larger lung airways, the bronchioles  112  are not supported by cartilage and thus have little intrinsic support. As a result, the bronchioles  112  are susceptible to collapse or reduce in diameter when destruction of tethering occurs, particularly during exhalation. A collapsed airway  304  is shown in  FIG. 3B . 
     This loss in elastic recoil of an airway  304  leads to trapping of air and hyperinflation of the lungs, and also causes poor gas exchange. As a result, the alveoli  314  deteriorate into large, irregular pockets with gaping holes in their inner walls. This damages the alveoli  314  and reduces the surface area of the lungs and, in turn, the amount of oxygen that reaches an individual&#39;s blood stream. 
     Additionally, it may cause an increase in residual volume of the lungs, resulting in increased CO 2  retention and reduced oxygen supply to the damaged alveoli  306 . One existing approach to treat emphysema is performing lung volume reduction surgery, which removes or kills a portion of a diseased lung to allow greater expansion of remaining lung tissue. However, this approach is restricted to the upper portions (e.g., airways) of the lungs and poses a substantial risk of serious post-operative complications due to its invasive nature. Other existing approaches involve less-invasive techniques, including the use of endobronchial valves, reduction coils, heated water vapour, cryogenic therapy, and polymeric injections. However, the success of these approaches is heavily reliant upon the lack of collateral flow (shown in  FIG. 4 ) between the targeted region of the lung and adjacent, non-targeted regions of the lung. For example, if an endobronchial valve or occlusion device  402  is implanted in a target airway  404  to prevent airflow into that region of the lung, if a collateral flow pathway  406  exists distal to the endobronchial valve  402 , then airflow can still occur in the targeted region of the lung and atelectasis fails to fully occur. This limitation is common among a large portion of COPD patients. 
     Moreover, when a severe COPD patient is placed under exercise intensity, e.g., the patient is stressed due to exercise, dynamic hyperinflation occurs in the lungs due to which the patient is unable to expire quickly enough, causing further inflation of lungs with each successive breath. Additionally, the patient may suffer from dyspnea (i.e., significant shortness of breath), which deteriorates the patient&#39;s quality of life. 
     It may, therefore, be beneficial to provide a less-invasive technique of appropriately manipulating airways of the lungs for treating COPD, or other lung conditions. 
     SUMMARY 
     The disclosed embodiments relate to devices and methods for manipulating lung airways in a patient for treating, for example, chronic obstruction pulmonary diseases. One exemplary embodiment may include a device for treating lung disease. The device may include a plurality of media configured for deployment into one or more airways of the lung. Additionally, the device may include a deployment member configured for insertion into or proximate the one or more airways of the lung. The deployment member may be configured to deploy the plurality of media substantially simultaneously. Also, the plurality of media may be configured to be retained within the one or more airways of the lung. 
     Additionally, the device may include one or more of the following features: wherein at least one of the plurality of media may include an expansion element such that upon activation, the at least one of the plurality of media may radially expand; wherein at least one of the plurality of media may be drug-eluting; wherein each of the plurality of media may be an air-blocking media such that upon deployment, the plurality of media may be configured to inhibit the passage of air through the one or more airways in which the media are retained; wherein each of the plurality of media may include a spherical shape, a cylindrical shape, an ovular shape, an irregular shape, or a cubical shape; wherein each of the plurality of media may be a flow-through media such that upon deployment, the plurality of media may be configured to allow the passage of air through the one or more airways in which is the media are retained; wherein each of the plurality of media may include a porous frame; wherein the porous frame may include at least one of the following: a starburst shape, a buckey-ball shape, a cubical shape, an ovular shape, a spherical shape, and an irregular shape; and wherein substantially simultaneous deployment of the plurality of media includes deploying the plurality of media between zero and one seconds. 
     Another exemplary embodiment may include a device for treating lung disease. The device may include a first plurality of media, a second plurality of media, and a deployment member. The first plurality of media may be configured for deployment into one or more airways of a lung. Also, the second plurality of media may be configured for deployment into the one or more airways of the lung. The deployment member may be configured for insertion into the one or more airways of the lung. Additionally, the deployment member may be configured to deploy each of the first plurality of media substantially simultaneously, and may be configured to deploy each of the second plurality of media substantially simultaneously. Also, each of the first and second pluralities of media are configured to be retained within the one or more airways of the lung. 
     Additionally, the device may include one or more of the following features: wherein each of the first plurality of media has a first size, and each of the second plurality of media has a second size, wherein the first size is smaller than the second size; wherein at least one of the first plurality of media and/or at least one of the second plurality of media includes an expansion element such that upon activation, the at least one of the first plurality of media and/or the at least one of the second plurality of media radially expands; wherein substantially simultaneous deployment of the first plurality of media includes deploying the first plurality of media between zero and one second, and wherein substantially simultaneous deployment of the second plurality of media includes deploying the second plurality of media between zero and one second; wherein each of the first and second pluralities of media is an air-blocking media such that upon deployment, the first and second pluralities of media are configured to inhibit the passage of air through the one or more airways in which the media are retained; wherein each of the first and second pluralities of media is a flow-through media such that upon deployment, the first and second pluralities of media are configured to allow the passage of air through the one or more airways in which the media are retained; wherein the deployment device includes a balloon catheter; and the device further including a third plurality of media configured for deployment into the one or more airways of the lung, the deployment member being further configured to deploy each of the third plurality of media substantially simultaneously. 
     An exemplary method for treating lung disease may include inserting a deployment member into or proximate one or more airways of the lung. The method may further include deploying a first plurality of media configured for deployment into a portion of the lung substantially simultaneously. The first plurality of media may be configured to be retained within one or more airways of the lung. 
     Additionally, the method may include one or more of the following features: deploying a second plurality of media configured for deployment into the one or more airways of the lung substantially simultaneously, where the second plurality of media may be configured to be retained within one or more airways of the lung; and wherein deploying the first plurality of media substantially simultaneously includes deploying the first plurality of media between zero and one second. 
     The above summary of exemplary embodiments is not intended to describe each disclosed embodiment or every implementation of the present disclosure. The Figures, and Detailed Description, which follow, more particularly exemplify these embodiments. 
    
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
       The drawings illustrate the design and utility of exemplary embodiments of the present disclosure, in which similar elements are referred to by common reference numerals. In order to better appreciate how the above-disclosed and other advantages and objects of the present disclosure are obtained, a more detailed description of the present embodiments will be rendered by reference to the accompanying drawings. Understanding that these drawings depict only exemplary embodiments of the disclosure and are not therefore to be considered limiting in scope, the disclosure will be described and explained with additional specificity and detail through the use of the accompanying drawings in which: 
         FIG. 1  illustrates the anatomy of healthy lungs in accordance with the present disclosure; 
         FIGS. 2A and 2B  illustrate a left lung suffering from a first chronic obstructive pulmonary disease; 
         FIGS. 3A and 3B  illustrate a left lung suffering from a second chronic obstructive pulmonary disease; 
         FIG. 4  illustrates a prior art device for treatment of an unhealthy target region of a lung; 
         FIG. 5  illustrates a device for deploying exemplary media in the airway of an unhealthy lung according to a first embodiment of the present disclosure; 
         FIG. 6  illustrates the exemplary media deployed in the airway of the lung of  FIG. 5  according to the first embodiment of the present disclosure; 
         FIG. 7  illustrates an alternative exemplary media according to a second embodiment of the present disclosure; 
         FIG. 8  illustrates another alternative, exemplary media according to the second embodiment of the present disclosure; 
         FIG. 9  illustrates a device for deploying the exemplary media of  FIG. 7  in the airway of an unhealthy lung according to the second embodiment of the present disclosure; 
         FIG. 10  illustrates the exemplary media of  FIG. 7  deployed in the airway of the lung of  FIG. 9  according to the second embodiment of the present disclosure; and 
         FIG. 11  illustrates a schematic illustration of the exemplary media of  FIG. 7  in the lung airway according to the second embodiment of the present disclosure. 
     
    
    
     DETAILED DESCRIPTION OF EXEMPLARY EMBODIMENTS 
       FIG. 5  illustrates a device  500  for deploying exemplary air-blocking media  510  in the airway  504  of a lung suffering from, for example, COPD according to a first exemplary embodiment of the present disclosure. The device  500  includes a deployment member  502  configured for insertion into or proximate airways  504  in communication with a diseased portion of a lung of a patient. The deployment member  502  may be a steerable delivery catheter, such as a balloon catheter  516 , to target particular diseased portions of the lung. Alternatively, the deployment member  502  may be a steerable catheter, bronchoscope, or alternative introducer sheath with or without a balloon. The deployment member  502  may have a cross-sectional configuration adapted to be received in the airway  504 . The cross-section of the deployment member  502  may be substantially circular; however, other suitable cross-sectional shapes, for example, elliptical, oval, polygon, irregular, etc., may be employed. 
     The balloon catheter  516  includes a balloon  508  that is configured to transition between a first substantially deflated configuration and a second substantially expanded configuration. The balloon catheter  516  may be introduced into or proximate the airway  504  in communication with a diseased portion of a lung while in the first substantially deflated configuration. Upon reaching a targeted location within or proximate a selected airway  504 , the balloon  508  may be inflated via an inflation lumen (not shown) extending through balloon catheter  516  such that balloon  508  expands to the second substantially expanded configuration and contacts an inner surface of the selected airway  504 . In this way, balloon  508  may stabilize balloon catheter  516  and prevent media  510  from travelling up the airways  504 , proximally of the balloon  508 . 
     In an exemplary embodiment, the balloon catheter  516  includes one or more lumens  512  extending from the distal end to a proximal portion (not shown) of the balloon catheter  516 . At least one lumen  512  is configured to deploy media  510  therethrough. For example, the lumen  512  may be configured to deliver a plurality of media  510  in batches. That is, lumen  512  may deliver a first batch (i.e., plurality) of media  510  substantially simultaneously, and subsequently, lumen  512  may deliver a second batch (i.e., plurality) of media  510  substantially simultaneously. Each batch may include any number of media  510 . For example, each batch may include a few, hundreds, or even thousands of media  510 . Also, in this context, it is understood that substantially simultaneously includes a single or continuous activation of deployment member  502  which delivers media  510  from the lumen  512 , although not all media  510  may exit the distal end of lumen  512  at the exact same time. Indeed, substantially simultaneous deployment of media  510  may include deploying the media  510  between zero and thirty minutes. Further, substantially simultaneous deployment of media  510  may include deploying the media  510  between zero and five minutes, between zero and one minute, or between zero and one second. For example, a user may activate the deployment member  502  a first time, so as to deploy a first batch (i.e., plurality) of media  510 . Then, a user may activate the deployment member  510  a second time (or any number of additional times), so as to deploy a second batch (i.e., plurality) of media  510 . Optionally, deployment member  502  may be configured to deliver media  510  via a pressurized fluid source (not shown). That is, deployment member  502  may be in communication with a pressurized fluid (e.g., air) which may be fluidly coupled to lumen  512  such that the pressurized fluid may aid in moving media  510  out of the distal end of lumen  512 . That is, the source of pressurized fluid may assist in “pushing” media  510  out of the lumen  512 , thereby achieving better penetration depth of the media  510  into the airway  504 . 
     Any number of batches of the media  510  useful to achieve atelectasis may be deployed via lumen  512 . Additionally, it is understood that the batches, e.g. the first and second batches of media  510 , may be sized differently. That is, the first batch of media  510  may have a first dimension (e.g., diameter) whereas the second batch of media  510  may have a second dimension (e.g., diameter) larger than the first dimension. The dimensions of the batches of media  510  may be selected such that upon deployment in the airway  504 , the media  510  block (i.e. occlude) airway  504 . Alternatively, the dimensions of media  510  may be selected such that upon deployment in the airway  504 , a plurality of media  510  may be configured to interlock and span the airway  504  so as to collectively block (i.e. occlude) the airway  504 . In this way, progressively larger media  510  may be introduced into airway  504  to occlude progressively larger portions of airway  504 . Said differently, smaller media  510  (e.g., media  510  in a first batch) may travel further distally through airway  504  of a patient while larger media  510  (e.g., media in a second batch) may not travel as far. 
     The media  510  may be made of a biocompatible polymer or metal, or a combination thereof. Optionally, media  510  may be manufactured of an expandable polymer so as to include an expansion element, which expands radially outward once the media  510  are deployed in the airway  504 , e.g., after coming in contact with humidity in the airway  504  causing swelling of the polymer. 
     Also, the media  510  may be configured to have other suitable shapes including, but not limited to, cubical, triangular, cylindrical, and irregular shapes. It is understood than any three dimensional shape sized so as to occlude airway  504  may be employed. That is, any air-blocking shape configured to obstruct airway  504  may be used. Further, the media  510  may be coated or impregnated with a drug, such as corticosteroid, which functions to reduce airway inflammation. Alternatively, other types of drugs, such as antibacterial agents, mucolytic agents, bronchodilators, or other drugs may be coated on the media  510  for treating airway  504 . 
     During operation, the deployment member  502  may be advanced through a natural opening of the body (e.g., via a mouth or nose) into or proximate the airway  504  of the lung of a patient, and positioned adjacent to the desired treatment region using, e.g., a bronchoscope. Alternatively, the deployment member  502  may be introduced without the use of a bronchoscope or similar device, or the deployment member  502  may be the bronchoscope or similar device itself. Once positioned, the balloon  508  may be inflated to contact the interior walls of the airway  504  and to seal the airway  504  to prevent media  508  from travelling proximate of balloon  508  into adjacent regions of the lung not intended to be treated during the procedure. In an exemplary embodiment in which media  510  are to be deployed with the assistance of pressurized fluid (e.g., air), the balloon  508  may also prevent pressurized fluid from travelling proximally of balloon  508 . That is, balloon  508  may assist in directing pressurized fluid such that media  510  may achieve better penetration depth into the airway  504 . 
     After the balloon  508  seals the airway  504 , the media  510  are injected into the airway  504  in batches or individually through the lumen  512 . Optionally, deployment may be assisted by applying pressurized air to the target regions of the lung. Alternatively, the media  510  may be deployed with a fluid or gel that contains drugs, such as antibiotics, intended to reduce infections in the acute phase while atelectasis occurs. Over time the fluid or gel may get absorbed into the airway  504  wall. 
       FIG. 6  depicts a plurality of media  510  deployed at different points within the airway  504  to prevent (or at least reduce) airflow in different regions of a lung. The variable sizes of the media  510 , which have a cross-sectional diameter of approximately the same as that of respective airway  504  into which it is received, facilitates stable retention of the media  510  in the airway  504  and blocks the passage of air. Consequently, the effect of a collateral flow channel  506  into the target airway  504  is significantly reduced. That is, since only a small portion of airway  504  receives collateral flow during inhalation, e.g., collateral flow area  514 , only the collateral flow area  518  may be prevented from complete atelectasis. Said differently, in contrast to the prior art embodiments shown in  FIG. 4  in which collateral channel  406  may deliver air to a large portion of airway  404  distal of endobronchial valve or occlusion device  402 , thereby reducing the effectiveness of endobronchial valve or occlusion device  402 , the present exemplary embodiment limits the amount of air that may be delivered to the airway  504 , thereby enabling vastly improved atelectasis of airway  504 . 
       FIG. 7  illustrates an alternative exemplary media  710  according to a second exemplary embodiment of the present disclosure. Media  710  are configured to maintain patency of an airway of a patient, that is, they are flow-through media. That is, rather than occlude an airway like media  500  according to the first exemplary embodiment, media  710  may be designed to promote the flow of fluid (e.g., air) through the airway of a patient. The media  710  includes a stent-like structure having a starburst shape. As shown, the media  710  includes a central base  720 , arms  722  extending radially outwards from the outer surface of the base, and contact members  724 , each connected to a distal end of the arms  722 . Alternatively, as shown in  FIG. 8 , flow-through media  810  including a porous frame having interconnecting arm members  822 , which define large openings therebetween may be used to maintain airway patency. Media  810  may have a buckey-ball, for example, including a porous frame surrounding a hollow core (e.g., a geodesic form) shaped design as shown, or alternatively media  810  may be configured to have different hollow framed shapes including, but not limited to, cubical, ovular, spherical, cylindrical, and/or irregular shapes. It is understood that media  710 ,  810  may have any flow-through shape configured to maintain airway patency. 
     Returning to  FIG. 7 , the cross-section of the base  720  may be substantially circular; however, other suitable cross-sectional shapes, for example, cylindrical, elliptical, oval, polygon, irregular, etc., may be employed. The media  710  (i.e., the base  720 , the arms  722 , the contact members  724 , or any combination thereof) and the media  810  may optionally be configured to transition from a collapsed state to an expanded state. That is, similarly to media  510  described above, media  710  and/or,  810  may include an expandable polymer (e.g., expandable element) which expands radially outward once the media  710  and/or  810  are deployed in an airway, e.g., after coming in contact with humidity in the airway. The media  710  and  810  are designed to ensure minimal contact with the airway wall in any orientation of the media  710 ,  810  within the airway  504 . 
     Both media  710  and media  810  are configured to have minimal impact on cilia, which removes foreign particles and mucus from the lungs. Similarly to media  510 , described above, media  710  and  810  may be deployed in batches. Any number of batches of the media  710 ,  810  useful to maintain airway patency may be deployed. Additionally, it is understood that the batches, e.g. the first and second batches of media  710 ,  810 , may be sized differently. That is, the first batch of media  710 ,  810  may have a first dimension (e.g., diameter) whereas the second batch of media  710 ,  810  may have a second dimension (e.g., diameter) larger than the first dimension. The dimensions of the batches of media  710 ,  810  may be selected such that upon deployment in the airway, the media  710 ,  810  promote airflow in the airway. Additionally or alternatively, the dimensions of media  710 ,  810  may be selected such that upon deployment in the airway, a plurality of media  710 ,  810  may be configured to interlock and span the airway so as to collectively promote airflow in the airway. In this way, progressively larger media  710 ,  810  may be introduced into airway to open-up progressively larger portions of airway. Said differently, smaller media  710 ,  810  (e.g., media  710 ,  810  in a first batch) may travel further distally through airway of a patient while larger media  710 ,  810  (e.g., media  710 ,  810  in a second batch) may not travel as far. In some exemplary embodiments, the base  720  may be partially biodegradable so that a lumen and or passageway through base  720  (not shown) is created after a period of time and to further reduce interaction with the cilia. 
       FIG. 9  illustrates a device  900  for deploying the exemplary media  710  of  FIG. 7  (or the exemplary media  810  of  FIG. 8 ) in the airway  904  of a lung suffering from, for example, COPD according to a second exemplary embodiment of the present disclosure. The device  900  includes a deployment member  902  configured for insertion into or proximate airways  904  in communication with a diseased portion of a lung of a patient. The deployment member  902  may be a steerable delivery catheter, such as a balloon catheter  916 , but other types of known, related art, or later developed steerable delivery catheters can be used to target particular diseased regions of unhealthy lungs. The deployment member  902  may have a cross-sectional configuration adapted to be received in the airway  904 . The cross-section of the deployment member  902  may be substantially circular; however, other suitable cross-sectional shapes, for example, elliptical, oval, polygon, irregular, etc., may be employed. 
     The balloon catheter  916  includes a balloon  908  configured to transition between a first substantially deflated configuration and a second substantially expanded configuration. The balloon catheter  916  may be introduced into or proximate the airway  904  in communication with a diseased portion of a lung while in the first substantially deflated configuration. Upon reaching a targeted location within or proximate a selected airway  904 , the balloon  908  may be inflated via an inflation lumen (not shown) extending through balloon catheter  916  such that balloon  908  expands to the second substantially expanded configuration and contacts an inner surface of the selected airway  904 . In this way, balloon  908  may stabilize balloon catheter  916  and prevent media  710 ,  810  from travelling up the airway  904 , proximally of the balloon  908 . 
     In an exemplary embodiment, the balloon catheter  916  includes one or more lumens  912  extending from the distal end to a proximal portion (not shown) of the balloon catheter  916 . At least one lumen  912  is configured to deploy media  710 ,  810  therethrough. For example, the lumen  912  may be configured to deliver a plurality of media  710 ,  810  in batches. That is, lumen  912  may deliver a first batch (i.e., plurality) of media  710 ,  810  substantially simultaneously, and subsequently, lumen  912  may deliver a second batch (i.e., plurality) of media  710 ,  810  substantially simultaneously. Each batch may include any number of media  710 ,  810 . For example, each batch may include a few, hundreds, or even thousands of media  710 ,  810 . Also, in this context, it is understood that substantially simultaneously includes a single or continuous activation of deployment member  902  which delivers media  710 ,  810  from the lumen  912 , although not all media  710 ,  810  may exit the distal end of lumen  912  at the exact same time. For example, a user may activate the deployment member  902  a first time, so as to deploy a first batch (i.e., plurality) of media  710 ,  810 . Then, a user may activate the deployment member  902  a second time (or any number of additional times), so as to deploy a second batch (i.e., plurality) of media  710 ,  810 . Optionally, deployment member  902  may be configured to deliver media  710 ,  810  via a pressurized fluid source (not shown). That is, deployment member  902  may be in communication with a pressurized fluid (e.g., air) which may be fluidly coupled to lumen  912  such that the pressurized fluid may aid in moving media  710 ,  810  out of the distal end of lumen  912 . That is, the source of pressurized fluid may assist in “pushing” media  710 ,  810  out of the lumen  912 , thereby achieving better penetration depth of the media  710 ,  810  into the airway  904 . 
     Due to the shape of the media  710 ,  810 , it can be rapidly deployed since it supports the airway  904  in an open position regardless of its orientation (shown in  FIG. 10 ). Additionally, the design of the media  710 ,  810  allows it have minimal contact with cilia the inner diameter  920  of the airway  904  in a given cross-section plane (shown in  FIG. 11 ). However, a media, such as the media  810 , can also be used for this purpose. The media  710  and the media  810  can be made of the same or different materials and be drug-eluting similarly to media  510  discussed above. 
     In yet another exemplary embodiment, a device, such as the devices  500 ,  900 , can be configured to deploy the media  510 ,  710 ,  810  in any combination into an airway, such as the bronchi  110  and bronchioles  112 , for treatment of the lung and, for example, the treatment of COPD. The deployed media  510 ,  710 ,  810  may be of variable sizes in order to treat airways of varying size (e.g., varying diameter). 
     Although the exemplary embodiments described above have been disclosed in connection with devices for manipulating lung airways, those skilled in the art will understand that the principles set out above can be applied to any bronchial device and can be implemented in different ways without departing from the scope of the disclosure as defined by the claims. In particular, constructional details, including manufacturing techniques and materials, are well within the understanding of those of skill in the art and have not been set out in any detail here. These and other modifications and variations are well within the scope of the present disclosure and can be envisioned and implemented by those of skill in the art. 
     Moreover, while specific exemplary embodiments may have been illustrated and described herein, it should be appreciated that combinations of the above embodiments are within the scope of the disclosure. Other exemplary embodiments of the present disclosure will be apparent to those skilled in the art from consideration of the specification and practice of the exemplary embodiments disclosed herein. It is intended that the specification and examples be considered as exemplary only, and departures in form and detail may be made without departing from the scope and spirit of the present disclosure as defined by the following claims.