Anesthesia monitor

Abstract: The invention provides an anesthesia monitor being able to directly make a separation and a determination in a real time of all components of a gas in which components having the same integer molecular weight exists an expiration and an inspiration as an analyzing object. The monitor has a small size, a low price and a operational facility. A microscopic quantity of the expiration gas is introduced from a circular route of an anesthesia circuits (31) for an inhalation anesthesia to the anesthesia monitor (1) through a material pipe-line (44). A material gas is transmitted by a rotary pump (48) through valves (46, 47) and opening and closing valve (51) to a measurement cell within a vacuum chamber arranged in a gap of magnetic poles of permanent magnets in a Fourier transformation mass analyzer so that the expiration gas is subjected to a high speed sampling. An ionization of the ions is carried out within the measurement cell. A cyclotron resonance is caused thereby causing a high frequent voltage which is received by receiving electrodes of the cell. After a digitalization of the signals, a computer executes a Fourier transformation mass analyzing process.

Description: The invention relates to an anesthesia monitor, and more particularly to an anesthesia monitor for analyzing continuously a part of the inspiration and expiration of a living body so as to perform movement analyses about the respiration, the circulation and the metabolism thereof. From WO-90/14687 an apparatus for producing an arbitary excitation spectrum for Fourier transform mass spectrometry is known. However, the resolution of the known apparatus is poor. Known anesthesia monitors analyze concentrations of N 2 , O 2 , CO, CO 2 , N 2 O and added anesthetics involved in the inspiration or expiration of patient in order to keep patient's conditions well. Normally, an inhalation anesthesia employs nitrous oxide (N 2 O). Further, anesthethics such as halothane in which a hydrogen atom of alkane or ether is substituted by a halogen atom are recently employed. Thus, the variety of anesthetics tends to be increased. It is required to perform the concentration analyses of such anesthetics comprising many components. The conventional anesthesia monitors have normally utilized an infrared spectroscopy or a mass spectrometry as a analysis method of the anesthetic concentration involved in the expiration or the inspiration. The mass spectrometry usually employs a uniconvergence method or a quadruple-pole method to analyze the expiration or the inspiration. As described above, since the variety of anesthetics tends to be increased, the anesthesia monitor is required to possesses the following performances. First requirement is that the anesthesia monitor is able to make a measurement of various components involved in the expiration and the inspiration. Second requirement is that the anesthesia monitor is able to make a separation and a determination of components which have analogous properties to one another. Third, the anesthesia monitor is able to make a measurement of many components in the real time. Fourth, the anesthesia monitor has a suitable size to an operation room, in addition facilities of installation and operation thereof. It will be investigated whether or not the above analyzing methods of the concentration comply with the above requirements. The infrared spectroscopy has the following problems in a separation of the concentration of mixed gases. First problem N 2 O has an intensive spectrum peak in the range of the wavelength from 4.4 micrometers to 4.6 micrometers. In contrast, CO 2 has an intensive spectrum peak in the range of the wavelength from 4.2 micrometers to 4.4 micrometers. Thus, the intensive spectrum peaks of N 2 O and CO 2 overlap with one another in the vicinity of a wavelength of 4.4 micrometers. A normal anesthesia performed on condition of a high concentration of N 2 O and a low concentration of CO 2 forces the measurement results to have an error. Second problem is that the molecular collision causes a spectral line to be broad. In mixed gases, molecules of gas as a measuring object makes collisions with other molecules thereby causing an interchange of molecular energies. The molecular energy is varied according to the molecular weight and the dipole moment of the collision gas. As a result, the infrared absorption band becomes broad and the dummy absorption wavelength is also influenced. Thus, An error in the measurement results is appeared depending upon circumstances of other components in the mixed gases. The third problem is that it is difficult to make a measurement of halide anesthetics which are reently developed frequently. The halide anesthetics have intensive absorption lines in the vicinity of a wavelength of 3.1 micrometers respectively. This makes it impossible to distinguish individuals of the halide anesthetics. Fourth problem is that the infrared spectroscopy unable to make a measurement of components which are subjected to no variation of its dipole moments by a molecular oscillation such as a diatomic molecule. Thus, it is impossible to measure N 2 O and CO 2 and the like as serving basic components on an artificial respiration. The mass spectrometry has the following problems. It is difficult to make a separation measurement of the component of any gases as measuring objects. Foe example, nitrous oxide (N 2 O) which is frequently used for a general anesthesia has a molecular weight of 44.001. Carbon dioxide (CO 2 ) which frequently becomes on analyzing object for the respiration analysis has a molecular weight of 43.990. The both molecules have the same integer mass number. The difference in the precise mass number thereof is 0.011 amu only. The accomplishment of a direct separation determine of the above molecule components by measuring its molecular peaks requires a resolution of much more 10000. The resolution is defined by Resolution » mass number / ( peak interval / 2 ) = 8000. The conventional mass spectrometry utilizing the mono-convergence system or the quadruple-pole system has a resolution of approximately 1000 only. Thus, it is difficult to make directly the separation measurement. As a result, the conventional anesthesia monitor unwillingly uses the following methods. In a first method, fragment peaks of all components expected to be involved in the mixed gases are compared, after which peaks, or uni-peaks which do not overlap with one another are selected. The height of the selected peak is regarded as a quantity of a component of the above mixed gases. There exists a second method utilizing a multiple regression method which solves simultaneous equations or normal equations by the least square method. In the simultaneous equations, patterns coefficients of all components expected to be involved in the mixed gases are so utilized that unknown letters are the concentrations of the above all components. With respect to the first method, the separation measurements of N 2 O and CO 2 unable to use molecular peaks having maximum intensity respectively. The separation measurement of N 2 O uses a fragment peak of M/z 30. The separation measurerment of CO 2 uses a fragment peak of M/z 12. As well known, such fragment peaks has its intensity being considerably lower than that of the molecular peaks as base peaks. This causes the accuracy of the measurement to be lowered. With respect to the second method, as known, when there exists on unexpected component in a material gas or a ratio of measurement peak signal to a noise is not sufficiently large, an unexpected large error is appeared. Further, there exists a gas chromotograph mass spectrometry method. In the method, the gas chromatograph used for the normal organic analyses are previously prepared. the components of the mixed gases are separated according to specific retention time, followed by the mass analyzing. Since such method has on analyzing period in the range from several minutes to several ten minutes, the above mentioned real time measuring condition is not complied and thus the method is not applicable to the expiration measurement. In addition, there exists a Fourier transformation moss spectrometer being commercially available. The applicability of the method to the expiration and inspiration analyses is disclosed in Anal. Chem. 60, pp. 341-344, 1988. Disclosed therein is a large and extremely expensive apparatus utilizing a super-conductance magnet, which have not been applied to a general clinical. Furthermore, there exists a large double focusing mass spectrometer possessing a resolution more than 10 4 . Although such spectrometer is capable of making the separation measurement of N 2 O and CO 2 by using those molecular peaks, that is practically unsuitable for the anesthesia monitoring in a large installation arcs, its complicated operations, a long measuring time at a high resolution. A high price thereof is bar to its application. Besides, from EP-A-0 515 690, which is relevant under Art.54(3),(4) EPC only, a Fourier-transform mass spectrometer with a permanent magnet is known which can be used as anasthesia monitor able to seperate nitrous oxide from carbon dioxide. Accordingly, it is a primary object of the present invention to provide an improved anesthesia monitor using an mass spectrometry. It is a further object of the present invention to provide on anesthesia monitor using an mass spectrometry utilizing a Fourier transformation ion cyclotron resonance of expiration and inspiration gas caused by a magnetic field provided by a permanent magnet in which analyzing objects includes components having equivalent integer molecular weights, which exist in the expiration and the inspiration. It is a still further object of the present invention to provide an anesthesia monitor capable of making directly a separation and a determination of all gas components in a real time. It is a yet a further object of the present invention to provide an anesthesia monitor having a small size, a low price and a facility in its operation. The above and other objects, features and advantages of the present invention will be apparent from the following descriptions. An anesthesia monitor according to the present invention is defined in claim 1. It comprises a first unit for introducing mixed gases used for anesthesia or expirations into a measurement cell within a high vacuum chamber arranged in a gap of magnetic poles of permanent magnets and a second unit for applying, in a short time after an ionization of introduced gases, high frequent voltages to irradiation electrodes constructing a part of the cell to cause an ion cyclotron resonance and for making a detection and amplification of a high frequent signal voltage caused at receiving electrodes constructing a part of the cell and for converting the signal into digital signals and for storing the digital signals in a memory of a computer and for executing a Fourier transform process for stored digital signals to obtaining mass spectrums of the introduced gases so as to perform a separation and determination for each of components of the introduced gases. In the anesthesia monitor of the present invention, the mixed gases added with anesthetics are ionized within the measurement cell of the high vacuum chamber. The ionized ions are applied with a high frequent voltage so as to cause a cyclotron resonance. The cyclotron resonance causes a high frequency voltage which is received by the receiving electrodes of the cell. The received signals are amplified and then converted into digital signals. The digital signals are subjected to a Fourier transformation mass analyzing process by the computer so as to make the separation and determination measurements of the mixed gases in a real time. Preferred embodiment of the present invention will hereinafter fully be described in detail with reference to the accompanying drawings. FIG. 1 is a block diagram illustrative of an anesthesia monitor and anesthesia circuits of the present invention. FIG. 2 is a block diagram illustrative of a structure of a Fourier transformation mass analyzing unit as a main unit of an anesthesia monitor of the present invention. FIG. 3 is a schematic perspective view illustrative of a cubic cell as a high vacuum cell used in a Fourier transformation mass analyzing unit. FIG. 4 is a view illustrative of a result of a measurement of components of N 2 O and CO 2 in a mixed gas. The measurement of an anesthesia monitor of the present invention utilizes a Fourier transformation mass analyzing method. In FIG. 2, the Fourier transformation moss analyzer 1 comprises a high vacuum cell 2, a permanent magnet 3, pulse control circuits 6 including an emission controller, a high frequency transmitter 7, a resonance signal detector 8, an arithmetic controller 9, a key board 11 and a CRT display 10. The high frequency transmitter 7 also comprises a clock generator 17, a high frequency oscillator 15 and a high frequency transmitter 16. The high frequency transmitter 7 transmits its output to the high vacuum cell 2. The resonance signal detector 8 comprises a preamplifier 20 inputted with measurement signals of the high vacuum cell 2, a high frequency amplifier 21, a low pass filter 22 and an analog digital converter 23 for converting the detected signals to digital signals. The digital data of the measurement signals is transmitted to the arithmetic controller 9. The arithmetic controller 9 comprises a computer 27, a memory 28, an output unit 29 and an interface 30. The computer 27 is connected to a key board 11 and a CRT display 10 so as to control the pulse control circuits 6, the high frequency amplifier 21 and the low pass filter 22. The output of the pulse control circuits 6 is transmitted to the high frequency generator 15, the high frequency transmitter 16 and the high vacuum cell 2. The high vacuum cell 2 is protected by a super-high vacuum chamber 13 and accomodated within a constant temperature bath which is not illustrated. Available as the high vacuum cell 2 is a cubic cell which comprises a pair of electrodes perpendicular to a direction of a magnetic field provided by the permanent magnet 3, a pair of irradiation electrodes parallel to the direction of the magnetic field, in addition both of which are perpendicular to one another and a pair of receiving electrodes. An example of usable cubic cells is disclosed in R.T. McIver Jr. Rev. Sci. Instrum., 41, p.555, 1970. In FIG. 3, with respect to the cubic cell 2, a pair of electrodes P and P' are so arranged that the magnetic field of the permanent magnet 3 across the electrodes P and P' in the right angle. In front of the electrode P of the cubic cell 2, a grid 2a is provided to be spaced apart from the electrode P and has a single opening for the passage of ionized gas for controlling of the current of the ionized gas. Further, a filament 2b is also provided. The electrodes P and P' are applied an insignificant positive potential, for example, 0.1 to 2 voltages in order to prevent ions within the high vacuum cell 2 to be drifted in the magnetic field direction. The irradiation electrodes T and T' are arranged between the electrodes P and P' so as to be parallel to the magnetic field and to face one another. Ions generated within the cubic cell 2 are applied in a short time, for example, 0.1 to 10 ms with high frequency signals from the high frequency transmitter 7 so as to excite a cyclotron resonance. The receiving electrodes R and R' are arranged in parallel to the magnetic field so as to face one another and to be perpendicular to both of the electrodes P and P' and T and T'. The receiving electrodes R and R' receive a high frequency signal voltage caused by the cyclotron resonance. The received high frequency signals are amplified by the preamplifier 20 and the high frequency amplifier 21, both of which exist within the resonance signal detector 8. After that, the amplified signals are to be transmitted through the low pass filter 22 to the analog digital convertor 23 and then are converted into digital signals. The digital signals are transmitted to the arithmetic controller 9. The arithmetic controller 9 stores the digital signals in the memory 28, after which the computer 27 executes the Fourier transformation mass analyzing process by using the stored data. The constant temperature bath as an additional unit prevents a temperature at the magnetic field of the permanent magnet 3 to be varied by the variation of the circumstantial temperature. The permanent magnet 3 is provided with a pair of magnets facing one another so as to sandwich the high vacuum cell 2. According to the present invention the permanent magnet 3 is used for the Fourier transformation mass analyzer 1. On the other hand, when contrary to claim 1 a super-conductance magnet is used, the stability of the magnetic field is very high. Although the mass spectrum is subjected to neither a variation of the temperature nor a secular change, a large apparatus is very expensive as described above. In contrast, when the permanent magnet or contrary to claim 1 an electromagnet is used, the magnetic field is varied by a circumstantial temperature. The electromagnet and an alkali-magnet have temperature coefficients of approximately -2 X 10 -4 /°C and -2 X 10 -3 /°C respectively. To secure a resolution in the range from 10 4 to 10 5 , it is required to compensate the variation of the magnetic field depending upon the temperature and the like. The method of compensating the variation of the magnetic field caused by the temperature variation is disclosed in PCT/JP91/01581, corresponding to EP-A-0 515 690. In FIG. 1, commercially available anesthesia circuits encompassed by a dotted line 31 performs the inhalation anesthesia. The anesthesia monitor is encompassed by a broken line 43. The Fourier transformation mass analyzer 1 is illustrated but only its gas inlet port. The anesthesia circuits 31 is connected through a gas inlet valve 35 transmitted from an airline 38 and through a coil 33 to a mask putting on an anesthesia patient. The expiration of a patient is transmitted through the coil 34 and through an outlet valve provided with a bag 37 to a carbon dioxide gas absorption unit 40 such as a canister, in addition, to an end connection 42 of a discharge unit for discharging an unnecessary gas. A gas circulation route is so form. The anesthesia circuits are further provided with an internal pressure gage 39 for measuring a gas pressure within the circuits and a pop-off valve 41 at a branched portion to the end connection 42. A part of the expiration is transmitted through the gas circulation route of the anesthesia circuits 31 to the anesthesia monitor 43. The material gas is transmitted through a variable valve 46 existing at a side of a pile-line inlet port 45 and a variable valve 47 existing at an inlet port of a rotary pump 48 so that a microscopic amount of the expiration gas is subjected to a high speed sampling. For the measurement cell 2 of the Fourier transformation mass analyzer 1, The pressure matching between the introduction gas pressure of approximately 133.3 to 133.3 X 10 -2 Pa (1 to 1 X 10 -2 Torr) and the measurement pressure of approximately 133.3 X 10 -7 to 133.2 X 10 -9 Pa (1 X 10 -7 to 1 X 10 -9 Torr) the Fourier transformation mass analyzer 1 is performed by an orifice 49. The measurement pressure is adjustable by the variable valves 46 and 47. Thus, when the variable valve 46 is closed and the variable valve 47 is opened, a quantity of the introduced material gas is reduced. In contrast, when the variable valve 46 is opened and the variable valve 47 is closed, a quantity of introduced gas into the measurement cell 2 within the vacuum chamber 13 is increased. The measurement pressure of the Fourier transformation mass analyzer 1 is controlled so as to be suitable in the above mentioned range. The values of the measurement pressure is indicated by a vacuum gage 50. The anesthesia monitor 43 involves an opening and closing valve 51. The mark "B" indicates a direction of the magnetic field. In FIG. 4, a vertical axis indicates a relative intensity and a lateral axis indicates a molecular weight. As described above, although carbon dioxide and nitrous oxide have near molecular weights respectively, it is understood that the above components are so measured as to be separated from one another. Since each area ratio of the peaks of both the relative intensities is proportional to the concentration of the each component, the concentrations of the components are defined by finding the peak area ratio. Analogous measurements are applicable to a measurement of nitrogen and carbon mono-oxide. The separation measurement of important components involved in the expiration and the inspiration of the living body is performed in the real time. Since it is possible to separate N 2 O and CO 2 , the anesthesia monitor serving for the general inhalation anesthesia is able to perform the recognition of a suitable ventilation, diagnoses of an air embolism and a shock and the like in the real time. As described above, the anesthesia monitor according to the present invention employs a mass analysis utilizing the Fourier transformation ion cyclotron resonance of the expiration and inspiration ions by the magnetic field of the permanent magnet. The anesthesia monitor directly makes in the real time the separation and the determination of all components existing in the expiration and the inspiration as the analyzing objects in which there exist components having the same integer molecular weight. Whereas modifications of the present invention will no doubt be apparent to a person of ordinary skill in the art, it is to be understood that the embodiments shown and described by way of illustration are by no means intended to be considered in a limiting sense. Accordingly, it is to be intended by the claims to cover all modifications of the invention which fall within the scope of the invention as defined in the claims.

Claims: An anesthesia monitor comprising: means (31) for introducing an expiration or a mixed gas for anesthetics into a measurement cell (2) within a high vacuum chamber (13) arranged in a gap of magnet poles of a permanent magnet (3); and means (43) for applying for a short time a high frequency voltage to irradiation electrodes constructing a part of said cell after the ionization of said introduced gas so as to cause a cyclotron resonance of said ions; means for making a detection and amplification of a high frequency signal voltage caused by said resonance at receiving electrodes constructing a part of said cell; means for converting said signals into digital signals; means for storing said digital signals in a memory of a computer; means for executing a Fourier transformation process for said stored digital signals to obtain a mass spectrum of said introduced gas so as to perform a separation and a determination of each component of said introduced mixed gas, said components having analogous properties to one another, said means for executing a Fourier transformation process comprising a pulse control circuit (6) for controlling pulses applied to the measurement cell (2) and to the high frequency transmitter (16) which supplies a high frequency signal to the measurement cell (2), and said gas introducing means (31) being coupled to a gas circulation circuit. The anesthesia monitor as claimed in claims 1, wherein said means for applying the high frequency voltage comprises a clock generator, a high frequency oscillator and a high frequency transmitter. The anesthesia monitor as claimed in claims 1, wherein said means for making the detection and amplification comprises receiving electrodes, a preamplifier, a high frequency amplifier and a low pass filter. The anesthesia monitor as claimed in claims 1, wherein said means for converting the signals comprises an analog digital converter. The anesthesia monitor as claimed in claims 1, wherein said means for storing the digital data comprises a memory device of a computer. The anesthesia monitor as claimed in claims 1, wherein said means for executing the Fourier transformation process comprises a computer.

Inventors: IRITANI YUICHI, NAKAGAWA KAZUO, TAKAKUWA YASUSHI, YAMAZAKI HIROMI, IRITANI, YUICHI, NAKAGAWA, KAZUO, TAKAKUWA, YASUSHI, YAMAZAKI, HIROMI, Iritani, Yuichi, c/o Nikkiso Co., Ltd., Nakagawa, Kazuo, c/o Nikkiso Co., Ltd., Takakuwa, Yasushi, c/o Nikkiso Co., Ltd., Yamazaki, Hiromi, c/o Nikkiso Co., Ltd.
Applicants: NIKKISO CO LTD, NIKKISO CO., LTD.
Application year: 1993
Main classification: A61B5
IPC codes: A61B10, A61B5, A61M16, H01J49