the following description is merely exemplary in nature and is not intended to limit the present disclosure , application , or uses . it should be understood that throughout the drawings , corresponding reference numerals indicate like or corresponding parts and features . fig1 illustrates generally an example of a system including an adapter apparatus 5 for processing respiratory air temperature and pressure change transducer signals . referring to fig1 , there is indicated generally by numeral 1 a typical sleep laboratory patient who has been outfitted with a respiratory air temperature and pressure change sensor 2 to measure respiratory air flow . a pair of temperature signal leads 3 and a pair of pressure signal leads 4 connect the respiratory air temperature and pressure change sensor 2 to the adapter apparatus 5 for processing respiratory air temperature and pressure change transducer signals . this specific exemplary embodiment shows two polarity indicating output wire pairs 6 and 7 connecting the adapter apparatus 5 for processing respiratory air temperature and pressure change transducer signals and presenting same to a conventional , commercially - available psg machine 8 , such as : model polysmith available from nihon kohden america of foothill ranch , calif . ; model easy ii available from cadwell laboratories , inc of kennewick , wash . ; all trademarks are property of their respective owners . this list is only exemplary in nature and does not claim to be comprehensive or complete . in a typical sleep laboratory application , temperature signal output 6 is configured to produce the respiratory air temperature change showing inhalation as an upward deflection of respiratory effort and showing exhalation as a downward deflection of respiratory effort on the psg machine 8 display . furthermore , pressure signal output 7 is configured to produce the respiratory air pressure change showing inhalation as an upward deflection of respiratory effort and showing exhalation as a downward deflection of respiratory effort on the psg machine 8 display . it is by international convention and by requirement of the american association of sleep medicine ( aasm ) that a patient &# 39 ; s inhalation produces an upward deflection and exhalation produces a downward deflection on the psg machine 8 display . fig2 illustrates generally an example of a system including an adapter apparatus 5 for processing respiratory air temperature and pressure change transducer signals , including an example of wiring connections connecting the adapter apparatus 5 to the respiratory air temperature and pressure change sensor 2 . in an example , the respiratory air temperature and pressure change sensor 2 can include a temperature change sensing pvdf film transducer 10 and a pressure change sensing pvdf film transducer 20 . a pair of temperature signal leads 3 and a pair of pressure signal leads 4 connect the respiratory air temperature and pressure change sensor 2 to the adapter apparatus 5 for processing respiratory air temperature and pressure change transducer signals . this specific exemplary of the embodiment shows two polarity indicating output wire pairs 6 and 7 connecting the adapter apparatus 5 for processing respiratory air temperature and pressure change transducer signals to a conventional , commercially - available psg machine 8 . fig3 illustrates generally an example of a system including an adapter apparatus 5 for processing respiratory air temperature and pressure change transducer signals , including an example of functional components included in the adapter apparatus 5 . the temperature change sensing pvdf film transducer 10 in one example is constructed in accordance with the teachings of the commonly - assigned reinhold henke et al . u . s . provisional application 61 / 075 , 124 , entitled “ polarized respiratory air temperature and pressure change sensor ,” filed on jun . 24 , 2008 , incorporated herein in its entirety . the sensor 10 is adapted to sense a patient &# 39 ; s inspiratory and expiratory air temperature . in an example , the temperature change sensing pvdf film transducer 10 connects to the respiratory air temperature signal path differential amplifier and integrator with resistive reset 40 via a pair of input wire leads 2 - 14 . in this example , wire 12 of the input wire pair is indicated to represent the positive terminal of the temperature change sensing pvdf film transducer that goes positive when patient is inhaling . further , wire 14 of the input wire pair is indicated to represent the negative terminal of the temperature change sensing pvdf film transducer that goes positive when patient is inhaling . the differential amplifier and integrator with resistive reset 40 of the respiratory air temperature change signal path comprises a differential type amplifier which functions to increase the common - mode rejection of the adapter apparatus 5 so as to make it less susceptible to 60 hz noise present in the environment as well as to motion artifacts . the signal integrator with resistive reset serves to slowly average the incoming signal over time so that the differential amplifier only amplifies signals that are within the response time of interest , i . e ., the patient &# 39 ; s respiratory response time . in various examples , the averaging signal integrator may operate with a fixed time constant of about 62 . 5 ms . without limitation , the differential amplifier and integrator with resistive reset 40 may have a gain in the range of from 2 to 10 with about 6 . 2 being quite adequate . the output signal from the differential input amplifier and integrator with resistive reset 40 on lead 42 is applied to a 3 rd - order butterworth low pass filter 44 . it should be understood by those skilled in the art that the type of filter response is neither limited to a 3 rd - order filter nor is it limited to a butterworth response . other filter responses may also be used . typically , but not limited to , the cut - off frequency for the third order butterworth low pass filter 44 may be about 125 mhz . as seen in the example of fig2 , the output 72 of the respiratory air temperature change signal path low pass filter 44 can connect to an input of the respiratory air temperature change signal path output attenuator module 84 . in an example , the respiratory air temperature change signal path output attenuator 84 attenuates the signal coming from the respiratory air temperature change signal path low pass filter module 44 in order to reduce the temperature change signal path amplitude to a level that is compliant with the requirements of the input specifications of the input jack of the particular psg machine 8 employed by way of lines 90 and 92 respectively . it should be clear to those skilled in the art that the entire temperature signal path starting from the polarized piezoelectric film sensor 10 and ending at the psg machine 8 is dc coupled , thus ensuring that the relationship of polarized piezoelectric film sensor polarity and indication of respiration effort between inhalation and exhalation on the psg machine is purposely maintained . the pressure change sensing pvdf film transducer 20 is in some examples is constructed in accordance with the teachings of the afore - referenced patent application of reinhold henke and entitled “ polarized respiratory air temperature and pressure change sensor ”. the sensor 20 is adapted to sense a sleep lab subject &# 39 ; s inspiratory and expiratory air pressure . the pressure change sensing pvdf film transducer 20 connects to the respiratory air pressure signal path differential amplifier and integrator with resistive reset 60 via a pair of input wire leads 22 - 24 . wire 22 of the input wire pair is indicated to represent the positive terminal of the pressure change sensing pvdf film transducer that goes positive when patient is inhaling . wire 24 of the input wire pair is indicated to represent the negative terminal of the pressure change sensing pvdf film transducer that goes positive when patient is inhaling . the differential amplifier and integrator with resistive reset 60 of the respiratory air pressure change signal path comprises a differential type amplifier which functions to increase the common - mode rejection of the adapter apparatus 5 so as to make it less susceptible to 60 hz noise present in the environment as well as to motion artifacts . the signal integrator with resistive reset serves to slowly average the incoming signal over time so that the differential amplifier only amplifies signals that are within the response time of interest , i . e ., the patient &# 39 ; s respiratory response time . in various examples , the averaging signal integrator may operate with a fixed time constant of about 62 . 5 ms . without limitation , the differential amplifier and integrator with resistive reset 60 may have a gain in the range of from 2 to 10 with about 6 . 2 being adequate . the output on wire 62 from the differential input amplifier and integrator with resistive reset 60 is applied to a third order butterworth low pass filter 64 . the input of the respiratory air pressure change signal path low pass third order butterworth filter 64 is connected to the output wire 62 of the differential input amplifier 60 . it should be understood by those skilled in the art that the type of filter response is neither limited to a third order filter nor is it limited to a butterworth response . other filter responses may also be used . typically , the cut - off frequency for the third order butterworth low pass filter 64 may be about 1 hz , but limitation thereto is not intended . the output on line 74 of the respiratory air pressure change signal path low pass filer 3rd order butterworth filter module 64 connects to the input of the respiratory air pressure change signal path output attenuator module 88 . the respiratory air pressure change signal path output attenuator 88 functions to attenuate the signal coming from the respiratory air pressure change signal low pass filter 3rd order butterworth filter module 64 in order to reduce the pressure change signal path amplitude to a level that is compliant with the requirements of the input specifications of the input jack of the psg machine 8 by way of lines 96 and 98 respectively . it should be clear to those skilled in the art that the entire pressure signal path starting from the polarized piezoelectric film sensor 20 and ending at the psg machine 8 is dc coupled , thus ensuring that the relationship of polarized piezoelectric film sensor polarity and indication of respiration effort between inhalation and exhalation on the psg machine is purposely maintained . having described an example overall configuration of the adapter apparatus of fig3 , a more detailed explanation of a specific implementation of the adapter will now be presented and , in that regard , reference is made to the schematic circuit diagram of fig4 . fig4 illustrates generally an example of a schematic diagram of an adapter apparatus 5 for processing respiratory air temperature and pressure change transducer signals . in an example , the adapter apparatus 5 can be integrated with the cable used to couple the temperature change and pressure change sensing pvdf film transducers 10 and 20 , respectively , to the polysomnograph machine 8 . as such , it incorporates its own power supply and virtual ground generator 50 in the form of a single lithium battery 52 with its positive battery voltage terminal 53 identified as v + and its negative battery voltage terminal 54 labeled v -. a resistor 55 connects the positive battery voltage terminal to a virtual ground point 59 . a resistor 56 connects the negative battery voltage terminal to the virtual ground point 59 . resistors 55 and 56 are preferably of equal value in establishing virtual ground point 59 . a polarized capacitor 57 connects in parallel with resistors 56 to form a low alternating current ( ac ) impedance return path from the negative battery terminal 54 to the virtual ground point 59 . the input terminal 12 to the differential amplifier and integrator with resistive reset 40 is coupled , via resistor 402 to the inverting input of operational amplifier 416 , to the gain setting and integrator resetting resistor 410 and to the integrating capacitor 412 . the input terminal 14 connects to the non - inverting input of differential operational amplifier and integrator with resistive reset 416 , via a resistor 404 and to an input load resistor 408 . the output from the differential input amplifier circuit 416 appears on lead 42 and connects to the respiratory air temperature change signal path third order butterworth low - pass filter circuit 44 . referring to filter circuit 44 , the input appearing on lead 42 is applied , via series connected resistors 442 , 448 and 450 , to the non - inverting input of an operational amplifier 460 and those resistors , along with capacitors 446 , 454 and 458 cooperate with the operational amplifier 460 to function as a low - pass butterworth filter . the output of the operational amplifier 460 is presented to lead 72 . the values of the resistors 442 , 448 and 450 and the capacitors 446 , 454 and 458 may be set to establish a cut - off frequency of the third order butterworth low - pass filter circuit 44 to about 125 mhz as mentioned previously . lead 72 feeds into the respiratory air temperature change signal path output attenuator 84 , which comprises a voltage divider including resistors 902 and 904 to drop the polarized piezoelectric film sensor based signal component to acceptable levels of the psg machine to which the polarized piezoelectric film sensor is being interfaced via a pair of lead wires 90 and 92 , respectively . the input terminal 22 of the differential amplifier and integrator with resistive reset 60 is coupled , via resistor 602 to the inverting input of operational amplifier 616 , to the gain setting and integrator - resetting resistor 610 and to the integrating capacitor 612 . the input terminal 24 of the differential amplifier and integrator with resistive reset 60 is coupled , via resistor 604 to the non - inverting input of operational amplifier 616 and to the input load resistor 608 . the output from the differential input amplifier circuit 616 appears on lead 62 and connects to the respiratory air pressure signal path third order butterworth low - pass filter circuit 64 . referring to filter circuit 64 , the input appearing on lead 62 is applied , via series connected resistors 642 , 654 and 650 , to the non - inverting input of an operational amplifier 660 and those resistors , along with capacitors 646 , 652 and 658 cooperate with the operational amplifier 660 to function as a low - pass filter . the output of the operational amplifier 660 is presented on lead 74 . the values of the resistors 642 , 648 and 650 and the capacitors 646 , 654 and 658 may be set to establish a cut - off frequency of the third order butterworth low - pass filter circuit 64 to about 1 hz as mentioned previously . lead 74 feeds into the respiratory air pressure change signal path output attenuator 88 , which comprises a voltage divider including resistors 962 and 964 to drop the polarized piezoelectric film sensor based signal component to acceptable levels of the psg machine to which the polarized piezoelectric film sensor is being interfaced via a pair of lead wires 96 and 98 , respectively . the list of specific components used to assemble a printed circuit board assembly is known in the industry as a bill - of - materials ( bom ). below is an example of a bom for one embodiment of the components of fig4 . during operation in a typical application , such as in a sleep laboratory , a patient is fitted with a polarized respiratory air temperature and pressure change sensor . in an example , the polarized respiratory air temperature and pressure change sensor can be connected using an adapter apparatus to a psg machine . the adapter apparatus has been described herein for sleep scientists , sleep physicians and sleep technicians to see , detect and properly diagnose specific sleep disorders and diseases which including abnormal respiratory events including events occurring in the upper airway of the patient . this invention has been described herein in considerable detail in order to comply with the patent statutes and to provide those skilled in the art with the information needed to apply the novel principles and to construct and use such specialized components as are required . however , it is to be understood that the invention can be carried out by specifically different equipment and devices , and that various modifications , both as to the equipment and operating procedures , can be accomplished without departing from the scope of the invention itself . the description of the various embodiments is merely exemplary in nature and , thus , variations that do not depart from the gist of the examples and detailed description herein are intended to be within the scope of the present disclosure . such variations are not to be regarded as a departure from the spirit and scope of the present disclosure .
an apparatus or method can be configured to receive information indicative of respiratory air temperature of a subject from a respiratory air temperature piezoelectric film sensor and information indicative of respiratory air pressure of the subject from a respiratory air pressure piezoelectric film sensor , and to simultaneously process the received respiratory air temperature information and the received respiratory air pressure information to produce a first electronic signal output indicative of respiratory air temperature and a second electronic signal output indicative of respiratory air pressure .