Patent Publication Number: US-2021177321-A1

Title: Methods and systems for endobronchial diagnostics

Description:
CROSS-REFERENCE TO RELATED APPLICATION 
     The present application is a continuation of U.S. patent application Ser. No. 16/107,849 (Attorney Docket No. 20920-762.402), filed Aug. 21, 2018, which is a divisional of U.S. patent application Ser. No. 14/339,197 (Attorney Docket No. 20920-762.401), filed Jul. 23, 2014, now U.S. Pat. No. 10,076,271, which is a divisional of U.S. patent application Ser. No. 13/174,633 (Attorney Docket No. 20920-762.201), filed Jun. 30, 2011, now U.S. Pat. No. 8,808,194, which claims priority under 35 U.S.C. Section 119(e) to U.S. Provisional Patent Application Ser. No. 61/360,811 (Attorney Docket No. 20920.762-101), filed Jul. 1, 2010, the full disclosures of which are hereby incorporated by reference. 
    
    
     BACKGROUND OF THE INVENTION 
     1. Field of the Invention 
     This invention relates generally to methods for diagnosis and treatment of lung disease. 
     2. Description of the Related Art 
     Chronic obstructive pulmonary disease (COPD), including emphysema and chronic bronchitis, is a significant medical problem currently affecting around 16 million people in the U.S. alone (about 6% of the U.S. population). In general, two types of diagnostic tests are performed on a patient to determine the extent and severity of COPD: 1) imaging tests; and 2) functional tests. Imaging tests, such as chest x-rays, computerized tomography (CT) scans, Magnetic Resonance Imaging (MRI) images, perfusion scans, and bronchograms, provide a good indicator of the location, homogeneity and progression of the diseased tissue. However, imaging tests do not provide a direct indication of how the disease is affecting the patient&#39;s overall lung function and respiration. Lung function can be better assessed using functional testing, such as spirometry, plethysmography, oxygen saturation, and oxygen consumption stress testing, among others. Together, these imaging and functional diagnostic tests are used to determine the course of treatment for the patient. 
     One of the emerging treatments for COPD involves the endoscopic introduction of endobronchial occluders or one-way valve devices (“endobronchial valves” or “EBVs”) into pulmonary passageways to reduce the volume of one or more hyperinflated lung compartments, thus allowing healthier compartments more room to breathe and perhaps reducing pressure on the heart. Examples of such a method and implant are described, for example, in U.S. patent application Ser. No. 11/682,986 and U.S. Pat. No. 7,798,147, the full disclosures of which are hereby incorporated by reference. One-way valves implanted in airways leading to a lung compartment restrict air flow in the inhalation direction and allow air to flow out of the lung compartment upon exhalation, thus causing the adjoining lung compartment to collapse over time. Occluders block both inhalation and exhalation, also causing lung collapse over time. 
     It has been suggested that the use of endobronchial implants for lung volume reduction might be most effective when applied to lung compartments which are not affected by collateral ventilation. Collateral ventilation occurs when air passes from one lung compartment to another through a collateral channel rather than the primary airway channels. If collateral airflow channels are present in a lung compartment, implanting a one-way valve or occluder might not be as effective, because the compartment might continue to fill with air from the collateral source and thus fail to collapse as intended. In many cases, COPD manifests itself in the formation of a large number of collateral channels caused by rupture of alveoli due to hyperinflation, or by destruction and weakening of alveolar tissue. 
     An endobronchial catheter-based diagnostic system typically used for collateral ventilation measurement is disclosed in U.S. Patent Publication No. 2003/0051733 (hereby incorporated by reference), wherein the catheter uses an occlusion member to isolate a lung segment and the instrumentation is used to gather data such as changes in pressure and volume of inhaled/exhaled air. Current state of the art methods for collateral ventilation measurement are disclosed in U.S. Pat. No. 7,883,471 and U.S. Patent Publication Nos. 2008/0027343 and 2007/0142742 (all of which are hereby incorporated by reference), in which an isolation catheter is used to isolate a target lung compartment and pressure changes therein are sensed to detect the extent of collateral ventilation. The applications also disclose measurement of gas concentrations to determine the efficiency of gas exchange within the lung compartment. Similar methods are disclosed in PCT Application No. WO2009135070A1 (hereby incorporated by reference), wherein gas concentration changes in a catheter-isolated lung portion allow collateral ventilation to be determined. 
     Quantifying collateral ventilation via collateral resistance measurement and calculations typically takes about two to five minutes. During this time, the physician must ensure the patient is tolerating sedation, manage secretions to prevent occlusion within the catheter lumen, and maintain balloon seal/position within the target airway. Any one of these factors may extend the assessment time and compromise the assessment results. Thus, there is a need to quantify the magnitude of collateral ventilation within a lung compartment (lobe, segment, sub-segment, or the like) more quickly and efficiently. 
     Another unmet need is a simple and accurate method for determining the perfusion status of a lung segment (i.e., how well a lung segment is being supplied with blood). The current gold standard for determining perfusion status is using ventilation/perfusion scintigraphy (Wang S C et al. Perfusion scintigraphy in the evaluation for lung volume reduction surgery: correlation with clinical outcome. Radiology. 1997 October; 205(1): 243-8.). This method requires the use of a gamma camera following the injection of radioactive microspheres. This scanning technique is highly sensitive for detection of regional abnormalities of blood flow and is primarily used for the diagnosis of pulmonary embolism. It has also been tried in lung volume reduction surgery; the goal is to determine what regions of the lung are non-functional based on a mismatch of ventilation and perfusion. Though promising, the accuracy and application of ventilation/perfusion scintigraphy has yet to be proven due to lackluster results in its application to lung volume reduction surgery. Further, the dyes and separate scanning machinery necessary for scintigraphy means that this system is both complicated and costly to use. 
     It would also be desirable to measure oxygen absorption within the lung, since this could be indicative of the functionality of the lung. Diseased lung portions presumably would not absorb oxygen in the blood stream as well as non-diseased portions. It would thus be desirable to provide a method for assessing and comparing oxygen absorption between the various lung segments. 
     Yet another unmet need in diagnostics is the determination of how well a target lobe is ventilating. If the target lobe is not ventilating well as compared to other lobes, then a viable treatment option would be to isolate the lobe via Endoscopic Lung Volume Reduction (ELVR) to allow better ventilating lobes to utilize the same space and thereby increase the overall efficiency of the lung. In case the lobe has collateral ventilation (CV positive) and does not ventilate well, the treatment may constitute closing off the lobe using ELVR (e.g., endobronchial valves). ELVR then becomes a method to divert airflow to lobes with better ventilation and perfusion rather than a means to reduce lobe size. 
     If the target lobe ventilates well, then one may not want to isolate the lobe with valves, even if other disease parameters are present in that lobe. For example, if a lobe does not have collateral ventilation (CV negative) but still ventilates well, one may not want to close off the lobe using ELVR. One measurable parameter that can determine how well a lobe is ventilating is tidal expiratory and/or inspiratory flow. One could also monitor other parameters that may correlate to lobe function including airway resistance and pressures, such as the perfusion efficiency of blood in the capillaries of the alveoli. 
     There is also a need to determine abnormalities in gas exchange/blood flow to aid with targeting of lobes for endoscopic lung volume reduction in real-time. If the segment/lobe has collateral ventilation, a physician may still want to treat the lobe if the gas exchange is sub-optimal. Ultimately, such a method would enable physicians to treat both heterogeneous and homogeneous patients using EBVs or other pulmonary implants that cause lung collapse. 
     Therefore, it would be advantageous to have new diagnostic techniques for evaluating the state of lung disease progression, such as determining the presence and degree of collateral ventilation, the viability of lung tissue using parameters such as blood flow and oxygen permeation, as well as ranking a lung portion for severity of disease using a function of the diagnostic parameters. At least some of these objectives will be met by the embodiments described herein. 
     SUMMARY OF THE INVENTION 
     This application discloses methods and systems for targeting, accessing and diagnosing diseased lung compartments. In one aspect, a method of determining collateral ventilation in a patient comprises introducing a diagnostic catheter with an occluding member at its distal end into a lung segment via an assisted ventilation device, inflating the occluding member to isolate the lung segment, and performing a diagnostic procedure with the catheter while the patient is ventilated via the assisted ventilation device. The proximal end of the diagnostic catheter is configured to be attached to a console, and data from the diagnostic procedure may be displayed on the console. In one embodiment, the diagnostic procedure comprises determining one or more characteristics of respiration such as flow rate, pressure, or resistance. The characteristics may be used, for example, to determine the presence of collateral ventilation. In one embodiment, the assisted ventilation device may include a ventilation mask. 
     In another aspect, a method of assessing the functionality of a lung segment in a patient comprises introducing a diagnostic catheter with an occluding member at its distal end into the lung segment, inflating the occluding member to isolate the lung segment, and monitoring blood oxygen saturation of the patient. The proximal end of the diagnostic catheter is configured to be attached to a console, and in some embodiments the method may involve viewing data on the console related to the lung segment being assessed. The monitoring step may comprise monitoring oxygen saturation before and after the inflating step. After the monitoring step, the occluding member may be deflated. Oxygen saturation may be further monitored after deflating the occluding member. Oxygen saturation may be monitored by a pulse oximeter. 
     In yet another aspect, a method of assessing the functionality of a lung segment of a patient comprises introducing a diagnostic catheter with an occluding member at its distal end into the lung segment, determining tidal flow volume in the lung segment, determining total lung capacity of the patient, and determining a flow rank value based on the tidal flow volume of the lung segment and the total lung capacity. The proximal end of the diagnostic catheter is configured to be attached to a console, and at least the tidal volume and total lung capacity are typically displayed on the console. In one embodiment a treatment option is determined based on the flow rank value. The occluding member may be inflated to isolate the lung segment. 
     The method may further comprise determining the presence of collateral ventilation in the lung segment and a treatment option may be determined based on the presence of collateral ventilation. 
     Further aspects and embodiments of the present invention are described in further detail below, in reference to the attached drawings. 
    
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
       The invention has other advantages and features which will be more readily apparent from the following detailed description of the invention and the appended claims, when taken in conjunction with the accompanying drawings, in which: 
         FIG. 1  shows a diagnostic or assessment catheter used in the disclosed methods according to some embodiments of the present invention. 
         FIG. 2  shows the placement of the catheter shown in  FIG. 1  in the lung. 
         FIG. 3  shows a console configured to receive the catheter shown in  FIG. 1 . 
         FIG. 4  is a flow diagram illustrating one embodiment of the present invention. 
         FIGS. 5A-5C  show an example of results obtained by using the method illustrated in  FIG. 4 . 
         FIG. 6  is a flow diagram illustrating another embodiment of the present invention. 
         FIG. 7  shows results obtained by using the catheter shown in  FIG. 1 . 
         FIG. 8  is a flow diagram illustrating another embodiment of the present invention using the results obtained in  FIG. 7 . 
         FIG. 9  is a flow diagram illustrating another embodiment of the present invention using the results obtained in  FIG. 7 . 
         FIG. 10  is a chart showing results obtained by using the methods shown in  FIGS. 8 and 9 . 
         FIG. 11  is a chart showing results obtained by using the methods shown in  FIGS. 8 and 9 . 
     
    
    
     DETAILED DESCRIPTION 
     Although the detailed description contains many specifics, these should not be construed as limiting the scope of the invention but merely as illustrating different examples and aspects of the invention. Various modifications, changes and variations may be made in the disclosed embodiments without departing from the spirit and scope of the invention. 
     The present application provides methods and systems for targeting, accessing and diagnosing diseased lung compartments. Such compartments could be an entire lobe, a segment, a sub-segment or any such portion of the lung. Diagnosis is achieved in the disclosed embodiments by isolating a lung compartment to obtain various measurements to determine lung functionality. Though COPD is mentioned as an example, the applicability of these methods for treatment and diagnosis is not limited to COPD, but can be applicable to any lung disease. 
     The methods are minimally invasive in the sense that the required instruments are introduced through the mouth, a tracheostomy, or other site, typically via a bronchoscope, assisted ventilation device, or other non-surgical device passed through the mouth into the trachea and airways. In some embodiments, the patient is allowed to breathe normally during the procedures. Some embodiments may be used with assisted (or positive pressure) ventilation. The methods involve detecting the presence or characteristics (e.g., concentration or pressure) of one or more naturally occurring or introduced gases to determine the presence of collateral ventilation and/or to measure one or more other characteristics of a target lung compartment, such as oxygen saturation of tissue. 
     In some of the present embodiments, isolation of the lung comprises sealingly engaging a distal end of a catheter in an airway feeding a lung compartment, as shown in  FIGS. 1 and 2 . Such a catheter has been disclosed in co-pending published U.S. patent application Ser. No. 10/241,733, which is incorporated herein by reference. As shown in  FIG. 1 , the catheter  100  comprises a catheter body  110 , and an expandable occluding member  120  on the catheter body. The catheter body  110  has a distal end  102 , a proximal end  101 , and at least one lumen  130 , extending from a location at or near the distal end to a location at or near the proximal end. 
     The proximal end of catheter  100  is configured to be coupled with an external control unit (or “console,” not shown), and optionally comprises an inflation port (not shown). The distal end of catheter  100  is adapted to be advanced through a body passageway such as a lung airway. The expandable occluding member  120  is disposed near the distal end of the catheter body and is adapted to be expanded in the airway which feeds the target lung compartment. In one embodiment, the occluding member  120  is a compliant balloon made of transparent material. The transparent material allows visualization using the bronchoscope through the balloon. The occluding member  120  is inflatable via a syringe that is configured to be coupled to the inflation port. Optionally, catheter  100  comprises visual markers at the proximal and distal ends of the balloon to identify the location of the occluding member  120  within the airway prior to inflation. The occluding member  120  material inflates and seals with inflation pressures between 5-20 psi to prevent balloon migration within the airway. This inflation pressure also aids the occluding member  120  in maintaining a symmetrical configuration within the airway, thereby ensuring that the catheter (which is centered within the occluding member  120 ) will remain centered within the airway. The occluding member  120  material and attachment are also configured to minimize longitudinal movement of the occluding member  120  relative to the catheter body  110  itself. To accommodate the higher inflation pressure, the occluding member  120  is made of a polyurethane such as Pellethane  80 A, but can be made of any material that is configured to maintain structural integrity at a high inflation pressure. 
     Additionally and optionally, catheter  100  further comprises at least one sensor  140  located within or in-line with the lumen  130  for sensing characteristics of various gases in air communicated to and from the lung compartment. The sensors may comprise any suitable sensors or any combination of suitable sensors, and are configured to communicate with control unit  200 . Examples of sensors include pressure sensors, temperature sensors, air flow sensors, gas-specific sensors, or other types of sensors. As shown in  FIG. 1 , the sensors  140  may be located near the distal end  102  of the catheter  100 . Alternatively, the sensors  140  may be located at any one or more points along the catheter  100 , or in-line with the catheter  100  and within the control unit with one or more measuring components. 
     As shown in  FIG. 2 , at least a distal portion of the catheter body  110  is adapted to be advanced into and through the trachea (T). The catheter may optionally be introduced through or over an introducing device such as a bronchoscope. The distal end  102  of the catheter body  110  can then be directed to a lung lobe (LL) to reach an airway (AW) which feeds a target lung compartment (TLC), which is to be assessed. When the occluding member  120  is expanded in the airway, the corresponding compartment is isolated with access to and from the compartment provided through the lumen  130 . 
     The proximal end of the catheter  100  is configured to be coupled with a control unit (or “console”)  200 , as shown in  FIG. 3 . The control unit  200  comprises one or more measuring components (not shown) to measure lung functionality. The measuring components may take many forms and may perform a variety of functions. For example, the components may include a pulmonary mechanics unit, a physiological testing unit, a gas dilution unit, an imaging unit, a mapping unit, a treatment unit, a pulse oximetry unit or any other suitable unit. The components may be disposed within the control unit  200 , or may be attached to the unit  200  from an external source. The control unit  200  comprises an interface for receiving input from a user and a display screen  210 . The display-screen  210  will optionally be a touch-sensitive screen, and may display preset values. Optionally, the user will input information into the control unit  200  via a touch-sensitive screen mechanism. Additionally and optionally, the control unit  200  may be associated with external display devices such as printers or chart recorders. At least some of the above system embodiments will be utilized in the methods described below. 
     CV Assessment in Ventilated Patients. One embodiment includes a method of assessing collateral ventilation in a lung of a patient under an assisted breathing arrangement such as a ventilation mask. In this embodiment, the method involves placing an assisted breathing device, for example the ventilation mask, over the patient&#39;s mouth. The catheter  100  is introduced into the lung via a viewing scope, which is in turn introduced into the oral opening of the ventilation mask. Once the catheter has been introduced to the TLC, the TLC is isolated by inflating the occluding member  120 . The flow and pressure variations in the isolated lung compartment are then measured while the patient is allowed to breathe under a positive pressure through the ventilation mask. In the absence of collateral channels in a normal lung, expiratory flow from the isolated TLC continuously decreases over several cycles of respiration. In the presence of collateral channels connected to the TLC, there is little or no drop in expiratory flow after isolation of the TLC, which is used to measure the nature and degree of collateral ventilation. 
     The specific steps involved in this method are shown in greater detail in the flow diagram of  FIG. 4 . In step  401 , a bronchoscope is inserted into a patient lung through the ventilator mask. Thereafter, in step  402 , the bronchoscope is used to observe the lung and identify a target segment or lobe of interest. In step  403 , the endobronchial diagnostic catheter  100  is inserted into the airway leading to the lung compartment of interest, and the occluding member  120  is inflated to isolate the target lung compartment. Using console  200 , the expiratory flow waveforms are then recorded in step  404  for a few cycles of respiration, which may last less than a minute. Thereafter, in step  405 , the occlusion balloon is deflated and the diagnostic catheter  100  moved to another lung compartment for another measurement. The procedure may be repeated for several other lung compartments. 
     The data is then analyzed to obtain information on the collateral ventilation status of each of the compartments analyzed. Analysis of respiratory waveforms in normal subjects and patients under ventilation is shown in  FIGS. 5A-5C .  FIG. 5A  shows the variation of respiratory flow and pressure over several breath cycles in a normal lung (i.e., one not subject to collateral ventilation) when no ventilator is used. After occlusion, as indicated by the first vertical line, expiratory flow continuously decreases to a baseline that is roughly equal to zero. Further, negative pressure is also detected, and as shown, roughly increases with the duration of the occlusion. 
     In contrast,  FIGS. 5B and 5C  show the results of using ventilator-applied positive pressure on a diseased lung segment (i.e., one subject to collateral ventilation). The ventilator creates positive pressure, which is applied relatively uniformly across the lung. This pushes air through adjacent segments/lobes, including through the collateral channels, and ultimately into the catheter  100 . As is apparent in  FIG. 5B , the net positive pressure does not allow the flow rate to descend to the zero baseline as occurred in  FIG. 5A . Instead, a new flow baseline is established. Further, negative pressure, which was apparent in  5 A, is not detected until after the occlusion is removed (as shown in  FIG. 5C ). 
     Using the above methods, collateral ventilation can be quantified in any of the following ways: 
     A. The average expiratory air flow volume versus time can be measured. An increase in volume is indicative of greater collateral ventilation. 
     B. The average maximum air flow magnitude can also be measured. An increase in maximum air flow magnitude is indicative of greater collateral ventilation. 
     C. An increase in the baseline value for flow could be measured. An increase in baseline flow value is indicative of greater collateral ventilation. 
     D. The average change (delta) between flow baseline and the standard zero value could be measured. A greater average change is indicative of greater collateral ventilation. 
     E. Alternatively, the physician could decrease or increase the amount of positive pressure during the assessment period. The drop or rise in flow baseline as a result of the change in positive pressure, respectively, may be correlated to the magnitude of collateral ventilation. 
     In each of the above circumstances, an additional method may optionally be used to normalize flow data recorded from a particular lobe/segment due to differences in lobe/segmental volumes and airway resistances. 
     The primary advantage of this method is the rapid determination of the presence of collateral flow—often in less than a minute of assessment under ventilation, while other previously known methods require at least 2-5 minutes of measurement. The method also provides for more accurate determination of the degree of collateral ventilation, as a single measurement provides sufficient data to obtain several different parameters relating to collateral flow as detailed above. 
     Another advantage of this method is that since it applies positive pressure, it may also open hidden collateral channels that are closed due to a layer of secretions. These collateral channels may not be open for study using methods that do not use such positive pressure. Ventilator based assessment may thus forcibly open these occluded channels and provide detection of these hidden collateral pathways. 
     Method of Assessing Health of a Lobe Using Oxygen Saturation. Another method of improved diagnosis is a method of assessing abnormalities in gas exchange/blood flow within a target lung compartment using the level of oxygen perfusion. Specifically, a TLC is isolated while the overall oxygen saturation of the blood is monitored using a pulse oximeter. A change in the overall oxygen saturation of the blood indicates the level of functioning of the lobe. 
     This method is described in further detail in the flow diagram in  FIG. 6 . As shown in  FIG. 6 , in the first step  601 , a bronchoscope is inserted into a patient&#39;s lung and a TLC is identified. Catheter  100  is then introduced in step  602  through the working channel of the bronchoscope and positioned within the airway leading to the TLC. At this location, a pulse oximeter is used to measure oxygen saturation of the tissues in step  603  to provide a baseline value. The TLC is then isolated by inflating the occlusion element ( 604 ), and oxygen saturation is continuously recorded by the oximeter until a new equilibrium level is reached ( 605 ). The balloon is then deflated and post-deflation, the oxygen saturation is again continuously recorded till the original baseline is reached again ( 606 ). The process is repeated for all lobes/segments of interest ( 607 ). 
     The oxygen saturation data may be used in any of several ways to determine the perfusion efficiency of the TLC: 
     A. The rate at which oxygen concentration decreases (slope of oxygen saturation versus time) once TLC is isolated is correlated to the percentage the targeted lobe contributes to the overall perfusion of the lung. 
     B. The rate at which oxygen concentration increases (slope of oxygen saturation versus time) once the isolation is ceased is correlated to the percentage the targeted lobe contributes to the overall perfusion of the lung. 
     C. The difference in oxygen saturation between pre-isolation and post-isolation is also correlated to the percentage the TLC contributes to the overall perfusion of the lung. 
     D. Based on the oxygen saturation data received from all lobes, the rate of change in saturation is compared and normalized to adjust for differences in volumes of different lung compartments. 
     E. Furthermore, using console  200 , flow rate is optionally recorded to quantify ventilation from each lobe. The ventilation data is then optionally used to calculate ventilation and perfusion and potentially determine mismatches between ventilation and perfusion in real-time. 
     In practice, as the oxygen saturation is constantly in flux based on the degree of sedation, breath rate, position of bronchoscope, secretion status, and other factors, it is important that the above assessment is done fairly quickly to minimize the effects of these other factors on the results. In addition, the oximeter needs to have a sufficiently fine resolution to detect a drop in oxygen saturation due to occlusion. The pulse oximeter may be connected directly to the console  200  for continuous monitoring and recording of oxygen saturation data. 
     Degree of Oxygen Absorption. In a related embodiment, the degree of oxygen absorption in various lung lobes can be determined in order to determine lung functionality. In this situation, the patient is given supplemental oxygen. The oxygen concentration is then measured in a portion of the bronchial tree where there is no gas exchange (e.g., in a prelobar segment of the bronchus). The oxygen is then measured in various segments downstream of the first measurement. The values are then compared. Segments with poor function will exhibit values similar or closer to the first measurement. Those segments that exhibit values similar or closer to the first measurement (at portion with no gas exchange) are presumed to have decreased functionality. 
     Method of Assessing the Health of a Lung Compartment Using Flow Ranking. Another method disclosed in the present application is a method of assessing the health of a lung compartment by determining the ability of the compartment to ventilate. A poorly ventilating lobe provides reduced functional benefit to the patient&#39;s overall lung function and is thus considered an encumbrance to the rest of the lung. If the target lobe is not ventilating well in comparison to other lobes, the lobe can be isolated via endoscopic lung volume reduction (ELVR) to allow better ventilating lobes to utilize the same space and thereby increase the overall efficiency of the lung. 
     The method thus involves ranking various segments on the basis of the presence and degree of collateral ventilation within the segment and the segment&#39;s ventilation status, as determined by the expiratory and/or inspiratory flow, airway resistance and pressures. The ranking data is then used to determine the course of treatment, which may include placing a one-way valve. 
     For example, if the target segment ventilates well, then one may not want to isolate the lobe with valves. This may be true even when a segment has no collateral ventilation (CV negative), which would ordinarily have subject it to treatment using an EBV. If such a segment ventilates well, it may still be useful to the functioning of the lung as a whole and a user may choose to not isolate it. Similarly, if a segment has collateral ventilation (CV positive), it would not be indication for treatment with valves. However, if such a segment did not ventilate well, it may indicate that the lobe would benefit from ELVR (e.g., endobronchial valves). ELVR thus becomes a method to divert airflow to lobes with higher perfusion and ventilation rates rather than exclusively a means to reduce lobe size. 
     The ventilation status of a lung compartment is measured using the same catheter and method of using a catheter that was shown in  FIGS. 1-3 . The assessment catheter  100  is introduced into a TLC in a patient. Occluding member  120  is then inflated to isolate the target lung compartment. Characteristics of the air flowing into and out of the TLC are then measured. A result is shown in  FIG. 7 , where the respiratory flow into and out of the target lung compartment is shown as a function of time. Regular air flow is measured as shown to the left of the line marked “CV assessment”. The average tidal flow volume (ATFV) is determined by calculating the average flow rate over the course of a few breath cycles. In this case, the ATFV is determined by looking at the average tidal expiratory volume (ATEV) over the course of three cycles. 
     Then, when CV assessment begins, the TLC is isolated, resulting in the wave form shown to the left of the line marked “CV assessment”. The volume of air expired decreases gradually over time. This indicates an absence of collateral ventilation, since the isolated lung compartment is apparently not receiving inflow even though expiratory flow takes place. The expiratory air flow shown is thus obtained from a normal lung compartment with no collateral ventilation (CV negative). 
     After sufficient measurements are obtained as shown above, the course of treatment to be followed is determined using a flow ranking parameter and is illustrated in  FIG. 9 . Flow rank is defined by the relation: 
     Flow Rank=ATEV (ml)/TLV (liters)*10, where ATEV—is the average tidal flow volume in ml and TLV—the total lung capacity (volume) in liters. Both ATEV and TLV are values obtained from the console  200 . The multiplier  10  is added to obtain a convenient numerical value. 
     Further, if necessary, ATEV may be calculated as follows: 
     ATEV=TTEV/number of cycles, where TTEV is the total tidal expiratory volume during the given number of cycles. 
     Both collateral ventilation values and flow rank values for each segment measured are compared to values obtained from the general population, other lobes within the patient, or the same segment within the patient over the course of time. For the purposes of providing an example, a flow rank (FR) value greater than 15 is deemed to indicate a segment that ventilates well, and a FR value less than 5 is deemed to indicate a segment that ventilates poorly. 
     Using such parameters, a proposed method for determining the course of treatment using both collateral flow characteristics and Flow Ranking is shown in  FIG. 8 . As shown by option A, when the target lobe does not show collateral ventilation (CV negative), but ventilates less than optimally (FR&lt;15), the lobe is treated by placing a valve. However, as shown in case B, if the lobe is CV− but ventilates very well (FR&gt;15), valve placement is not recommended. If collateral ventilation is strongly present, as in case C, regardless of ventilation status, valve placement is presumed to not significantly influence gas exchange and is not recommended. If, as in case D, a lobe has weak collateral ventilation and does not ventilate well (FR&lt;5), valve placement is recommended, in which case ELVR becomes a method to divert airflow to lobes with higher perfusion and ventilation capabilities, rather than a means to reduce lobe size. If, however, as in case E, the target lobe still shows the ability to ventilate (FR&gt;5), then the lobe is not isolated with valves. 
     An example of Flow Rank calculation and treatment using the above scheme is shown below, where the average tidal expiratory volume is calculated based on three expiratory cycles. As an example, the values obtained from the graph shown in  FIG. 7  are used: 
     Total Tidal Expiratory Volume (TTEV) over 3 samples (Based on Assessment Displayed in  FIG. 7 )=42.15 mL and Average Tidal Expiratory Volume (ATEV)=TTEV/3=42.15/3=14.05 mL. 
     Patient&#39;s Total Lung Capacity=5.78 liters. 
     Flow Rank=ATEV (ml)/TLC (liters)*10=(14.05/5.78)*10=24.3. 
     Based on the Assessment shown in  FIG. 7 , Lobe is CV—but F.R. of 24.3&gt;=15. 
     Valve Placement Not Recommended. 
     Optionally, treatment options can also be determined without assessment of collateral ventilation, e.g., using Flow Ranking alone, as shown in  FIG. 9 , in which case the decision to place a valve is based on whether the ventilation status is poor (place valve) or good (do not place valve). 
     Additionally or optionally, the method of the invention may adopt a baseline flow rate to eliminate patient-to-patient variability. Such as baseline may be obtained by normalizing the flow data with the overall total lung capacity or other lobe/lung volume data. Another solution may be to normalize the values for the target lobes against unaffected or healthy lobes within the same patient to determine the target lobe&#39;s proportional output. 
     Additionally or optionally, other parameters can be measured by console  200  which could also be predictors, such as airway resistance (high tidal resistance=poor ventilating lobe), pressure (low tidal pressure=poor ventilating lobe) and oxygen perfusion efficiency. The inclusion of one or more of the above parameters may provide a better method of ranking overall lobe function (based on resistance, pressure, flow and perfusion) as well as utilizing CV assessment data to guide ELVR therapy decisions. 
     Clinical Data. The effect of treatments using the five options in  FIG. 8  was studied in a clinical setting, and the results are shown in  FIGS. 10 and 11 .  FIG. 10  represents data for patients who received a valve.  FIG. 11  represents data for patients who did not receive a valve. The patients in both cases were assessed under three parameters—a) SGRQ (St. George&#39;s Respiratory Questionnaire), b) FEV1 (ratio of forced expiratory volume in 1 second to forced vital capacity), and c) 6MWT (6 minute walk test). The change between baseline (pre valve-placement) and post-30 day follow up values were determined in patients treated using the several options. 
     Some results for patients implanted with a valve are shown in  FIG. 10 . The chart reflects data collected for patients: 
     Who Received Emphasys Valves; 
     With Atelectasis of the Target Lobe; 
     For Whom the Collateral Ventilation Assessment Measured CV-negative; 
     For Whom the Flow Rank with Collateral Ventilation Assessment diagnostic algorithm recommends a valve; and 
     For Whom the Flow Rank without CV assessment recommends a valve. 
     Some results for patients implanted with a valve are shown in  FIG. 11 . The chart reflects data collected for patients: 
     With no Atelectasis in Target Lobe; For Whom Collateral Ventilation Assessment Measured CV-positive in Target Lobe; 
     For Whom the Flow Rank with Collateral Ventilation Assessment diagnostic algorithm does not recommend a valve; and 
     For Whom the Flow Rank without CV assessment does not recommend a valve. 
     As observed in  FIGS. 10 and 11 , among all the methods of screening patients, Flow Ranking both with and without CV assessment appears to identify those patients who would benefit from ELVR therapy most optimally, as the positive values of test parameters are highest for these two categories of patients. 
     The flow ranking measurement and algorithm potentially opens treatment options to both heterogeneous and homogeneous emphysema patients and offers an opportunity to screen homogeneous emphysema patients with low flow rank. 
     Although certain embodiments of the disclosure have been described in detail, certain variations and modifications will be apparent to those skilled in the art, including embodiments that do not provide all the features and benefits described herein. It will be understood by those skilled in the art that the present disclosure extends beyond the specifically disclosed embodiments to other alternative or additional embodiments and/or uses and obvious modifications and equivalents thereof. In addition, while a number of variations have been shown and described in varying detail, other modifications, which are within the scope of the present disclosure, will be readily apparent to those of skill in the art based upon this disclosure. It is also contemplated that various combinations or subcombinations of the specific features and aspects of the embodiments may be made and still fall within the scope of the present disclosure. Accordingly, it should be understood that various features and aspects of the disclosed embodiments can be combined with or substituted for one another in order to form varying modes of the present disclosure. Thus, it is intended that the scope of the present disclosure herein disclosed should not be limited by the particular disclosed embodiments described above. For all of the embodiments described above, the steps of any methods need not be performed sequentially.