the lung is shown at maximum exhalation in fig1 and at maximum inhalation in fig2 . to produce these images the patient is positioned in an mr scanner such that the lung lies in the fov . an mr exposure is generated at each of various phase points of the respiration , in the shown exemplary embodiment at maximum inhalation and maximum exhalation . the change of the proton density dependent on the phase point of the respiration ( or the time ) provides a measure for the homogeneity and thus also for possible functional lung illnesses . for this purpose the 2d image of the lung can be subdivided in a computer into macroscopic areas , for example 100 squares . for each square the computer then determines the signal difference in comparison to the air at inhalation and exhalation . the computer also segments the blood vessels of the lung and associates the segments with these vessels . in order to compare the same lung region in each of the inhaled state and exhaled state , thus for example in order to compare the measurement volume m 1 in fig1 in an appropriate manner with the same measurement volume m 1 in fig2 in spite of the displacement that occurs upon inhalation ( in which measurement volume m 1 in fig2 the schematically indicated blood vessels 1 and 2 as well as the remaining tissue have significantly altered their separation ( b & gt ; a )), the segmentation described above is effected with regard to the vessels or other features such as , for example , the bronchi or the diaphragm . the computer then determines the displacement of each segment between inhalation and exhalation and the density change . fig3 and 4 respectively show a measurement volume , for example the measurement volume m 1 in fig1 and 2 in the inhaled state and in the exhaled state . this cubic measurement volume m 1 is filled by n 1 alveoli in the exhaled state according to fig1 . the total mr signal s 2 is assuming that it is healthy lung tissue , the cubic measurement volume is filled by fewer ( namely n 2 ) alveoli in the inhaled state . the signal of a single alveole remains the same since an unchanged tissue proportion is present . the entire mr signal is wherein s r is the signal of the background noise ( the inhaled air ). fig5 shows an mr image , whereby three measurement regions m 1 , m 2 and m 3 in which different lung functions are present are marked in the right drawn lobe of the lung . fig6 shows the proton density over two respiration cycles , respectively in the region of the areas m 1 , m 2 and m 3 , whereby the noise signal ( which is negligible in practice ) is additionally also plotted . fig7 shows the regional ventilation ( which can be calculated from the measurement data ) in ml / cm 3 , which indicates significant differences for the three lung regions represented by the measurement volumes m 1 , m 2 and m 3 . the determined data can be shown in the manner by the computer superimposing a color - coded map of the segments on the anatomical image of the thorax , wherein each color segment is inked corresponding to the proton density change and / or the speed of the change . in place of the determination of the proton density change and the tissue density change with the method described in the preceding , the computer can also directly determine the expansion of the lung segments from the displacement of the blood vessels and then combine these measurement values with the previously specified measurement . if one assumes that emphysema is present at a specific point , this means that both adjacent blood vessels do not change their separation , in contrast to a convergence in the remaining lung region . this enables a determination of the expansion of the corresponding lung segments . the computer takes into account not only the maximum inhalation and exhalation but also phase points in - between . the local inhalation speed and exhalation speed can be determined from this and be shown alternatively or additionally , for example color - coded . the invention represents a new paradigm for the diagnosis of functional lung illnesses . due to the short measurement time and the absent radiation exposure for the patient , it can be used cheaply and also in the framework of screenings . over the long term juvenile ventilation defects lead to types of emphysemas , meaning a rapid degradation of the lung vitality . these patients then already require an overnight oxygen feed as of 50 or 60 years of age and , due to the high susceptibility to , for example , different pneumonias ( lung inflammations ), have a low life expectancy . fig8 shows a flowchart of a method for quantitative evaluation of the effectiveness of an asthma therapy in accordance with the invention . the patient is initially registered and positioned in an mr scanner . a functional mr measurement of the lung ( fmrl ) subsequently ensues for determination of the initial position . a substance for inhalation that comprises an asthma provoker is subsequently administered to the patient , and preferably with a dose having an effect that is not measurable over the entire lung with a lung function measuring modality because the change lies below the biologically - provided margin of deviation . an fmrl measurement subsequently ensues in turn . if no reaction occurs due to the asthma provoker , the stage of the provoker administration is repeated with a higher dose and the preceding measurement cycle is implemented again . if a reaction due to the asthma provoker occurs , a bronchodilator / asthma therapeutic is administered and subsequently measured in turn in order to establish whether the asthma therapeutic has responded . if the dose was not sufficient or the agent was not effective , an administration of the asthma therapeutic at a higher dose or with a different substance can ensue again . if the dose was sufficient such that a satisfactory improvement has occurred , the evaluation method is ended . although modifications and changes may be suggested by those skilled in the art , it is the invention of the inventors to embody within the patent warranted heron all changes and modifications as reasonably and properly come within the scope of their contribution to the art .
in a method for diagnosing functional lung illnesses , image exposures of the lungs are obtained at various phase points in time of the respiration of a subject , such as at maximum inhalation and maximum expiration , and the image exposures are segmented and at least two of the image exposures are compared on a segment - by - segment basis to identify a change in tissue density between the compared segments , as an indicator of lung functioning .