KR950000057B1 - Endotracheal tube and mass spectrometer - Google Patents

Abstract

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Description

Compact mass spectrometers for medical instruments

1 is a perspective view of an endotracheal tube and a mass spectrometer inserted into a patient's mouth.

2 is an enlarged, side view of a partial cutaway of an endotracheal tube and a mass spectrometer and module.

3 is a cross-sectional view taken along line 3-3 of FIG.

4 is a cross-sectional view taken along line 4-4 of FIG.

5 is a perspective view of a mouthpiece as an alternative to an endotracheal tube.

6 is a cross-sectional view taken along line 6-6 of FIG.

7 is a cross-sectional view taken along line 7-7 of FIG.

8 is a cross-sectional view taken along line 8-8 of FIG.

9 is a schematic cross-sectional view showing the position of the passage in the valve of the manifold block.

10 is a cross-sectional view taken along line 10-10 of FIG.

11 is a sectional view taken along line 11-11 of FIG.

12 is a sectional view taken along line 12-12 of FIG.

13 is a cross-sectional view taken along line 13-13 of FIG.

FIG. 14 is a sectional view taken along line 14-14 of FIG. 9, shown rotated 90 degrees.

FIG. 15 is a sectional view taken along line 15-15 of FIG. 14, shown by being rotated 90 degrees.

16 is a partially exploded cross-sectional view of the motor pump, shown rotated 90 degrees.

Figure 17 is a schematic diagram of the present invention showing the main components.

18 is a circuit diagram of an electronic circuit for operating a novel endotracheal tube and mass spectrometer.

* Explanation of symbols for main parts of the drawings

10: waste gas fractionation and analysis device 11: endotracheal tube

12: motor pump and mass spectrometer module 13, 145: inner tube

14, 146: outer tube 27, 154: maternal limiting member

38: tracheal wall 39: tracheal aliquot cell

63: rotary valve 69: photoelectric sensor

71: gear motor pump unit 73: partition plate

74: motor chamber 75: pump chamber

86: drive gear 89, 93, 97: driven gear

100: mass spectrometer 101: housing

108, 110: sealing plate 120: spiral grid

129: linear accelerator 133, 133a: bus rail

135: ion collector plate 143: mouthpiece

144: mouthpiece tube 160: electronic circuit

179: differential pressure converter 180: multiplexer

182: analog-to-digital converter 185: microcomputer

187: Digital to Analog Converter

The present invention relates to an apparatus for measuring the amount and composition of inhalation and exhaust gas of a subject, whether conscious or unconscious, and calculating the lung function and cardiac output of the subject based on the data.

Determining the cardiac respiratory function of a subject is desirable and often necessary. The function of the cardiovascular and respiratory system is to supply oxygen-saturated blood to the human tissue and to remove the CO ₂ produced by the tissue so that the lungs are ventilated. The amount of blood injected or discharged as well as the amount of O ₂ and CO _{2 in} the blood as well as the ventilation of the lungs is a critical reflection of the adequacy of circulation and respiratory function.

During exercise, disease, or surgery, these physiological parameters may be altered or damaged as appropriate. In order to diagnose and treat cardiac respiratory dysfunction, it is necessary to measure and evaluate such parameters. This is particularly necessary when anesthesiologists under surgical anesthesia must maintain cardiac respiratory homeostasis, which may be damaged by anesthesia or complications during surgery. In the case of non-surgical patients with serious illness, it is also necessary to pre-evaluate such parameters. Moreover, prior evaluation of cardiac blood ejection and other cardiac respiratory functions, which should be the solution to the exercise test, is not routinely assessed because there is currently no effective non-insertion method that is acceptable.

Insertion devices are available (via catheter, etc.) but cannot be used routinely because they are time consuming and risky in the insertion process. Non-insertion devices, such as ultrasound Doppler devices, have been developed but cannot be used routinely and cannot accurately evaluate cardiac respiratory function.

It is an object of the present invention to provide a novel non-insertion device which continuously measures the amount and composition of the inhalation and exhaust gas of a subject and calculates lung function and cardiac blood ejection from the data.

More specifically, it is an object of the present invention to continuously maintain the PO ₂ and PCO ₂ of the tissue as well as O ₂ , CO ₂ , the total volume and temperature of respiratory air and other gases exchanged between organ tissues to determine cardiac blood output. It is to provide a compact mass spectrometer to measure with. Such measurements should be provided to determine the appropriateness of tissue perfusion as well as to quickly calculate cardiac output.

Accordingly, it is an object of the present invention to provide a novel compact mass spectrometer which interacts with an endotracheal tube to continuously and rapidly measure the cardiac respiratory function of a subject.

In order to achieve the object of the present invention, a compact mass spectrometer is connected to a specially designed endotracheal tube having a plurality of auxiliary passageways along its length. The ventilation function of the endotracheal tube is not changed and the sample gas is circulated through the secondary passage through the mass spectrometer for quantitative analysis. In a preferred embodiment of the present invention, the endotracheal tube is preferably used for single use and can be easily separated from the mass spectrometer motor pump module.

1 through 4, the waste gas fractionation and analysis device is shown at 10. The waste gas fractionation and analysis device 10 is composed of a disposable endotracheal tube 11 made of a soft plastic insert, and a motor pump and mass spectrometer module 12 detachably connected to the endotracheal tube. The endotracheal tube 11 is composed of an inner tube 13 and an outer tube 14. The double walled endotracheal tube 11 is manufactured by a conventional manufacturing process such as, for example, single-piece extrusion or assembled into two tubes. The inner tube 13 defines a central passage 15 penetrating in the longitudinal direction, and the central passage distributes fresh air to the lungs as in the conventional endotracheal tube.

The inner tube 13 and the outer tube 14 are connected to each other by a plurality of elongated connecting walls 16 which divide the inner annular space formed between the inner tube and the outer tube into a plurality of passages. The inner tube and the outer tube are connected at their respective lower ends 17 and the outward rigid annular member 18 is provided at the upper ends of the inner tube and the outer tube as shown in detail in FIG. 15. The connecting wall 16 divides the inner annular space arranged at the periphery of the central passage into the passages 19 to 26. These passages extend along the length of the endotracheal tube.

The capillary restricting member 27 is provided in a plurality of capillaries or passages 28 disposed in and through the inner tube 13 adjacent the lower end 17 of the endotracheal tube. 2 and 4 illustrate a capillary 28 extending through the capillary restricting member 27 axially so that the gas flowing through the longitudinal passage 15 can flow through the capillary 28. It can be seen that different pressures exist at both or both ends of the capillary restricting member 27.

2 shows an opening 29 in the inner tube 13 communicating with the passageway 19 at the lower end of the endotracheal tube 11. The second opening 30, located adjacent to the opening 29, communicates with the passage 2. The gas breathed from the subject continues to flow upward through the opening 30 to flow into the passage 20 forming the preparative passage. On the contrary, a part of the sample gas flows back through the passage 19 and is discharged through the opening 29 to the lower engine part. Thus, the passage 19 forms a return passage, and the gas flows in the downward or reverse direction.

In addition, the inner tube 13 has a gripping portion 31 located above the mother cap restricting member 27 communicating with the passage 21. The opening 32 in the inner tube 13 located below the capillary restricting member 27 communicates with the passage 23. The passages 21 and 23 are connected to the differential pressure transformer to determine the spirometry by detecting and analyzing the gas pressure above and below the capillary restricting member.

The outer tube 14 has a pair of soft sleeved members 33 secured adjacent to the lower end of the endotracheal tube. These soft sleeve-like members 33 have an upper annular edge 34 and a lower annular edge 35 which are spaced apart at regular intervals in the longitudinal direction from one another and are hermetically bonded to an outer tube. Each sleeve-like member 33 defines a chamber 36 in the volume space between the outer tubes. Each sleeve-like member 33 thus defines a pair of inflatable mechanisms that, in conjunction with the outer tube 14, allow the operator to selectively expand and contract.

In this regard, the outer tube 14 has a pair of openings 37 which are spaced apart at regular intervals in the longitudinal direction, each opening communicating with one of the chambers 36. In addition, each opening communicates with a passage 22 through which air for expanding or contracting each mechanism 33 passes. The instrument part serves a dual function, one of which is fitted to the tracheal wall of the subject to function as a support means.

In addition, the inflatable mechanical part 33 of the arterial PCO ₂ because by limiting the engine wall preparative cell for measuring the organ tissue O ₂ and CO _2, which reflects the PO ₂ of the artery with the organ wall of the subject is low metabolic rate of organ Provide an approximation.

Referring again to FIG. 2, the sleeve-like member or mechanism 33 is shown in an expanded state to fit and secure the engine wall 38. These instrument sections 33 define an engine fractionation cell 39 defined by a volume space located between the instrument section 33, the outer tube 14, and the engine wall 38 that are expanded with the engine wall 38. .

It can be seen that the outer tube 14 has an opening 40 communicating with the passage 24 therein. The outer tube 14 also has an opening 41 communicating with the passage 25 therein. When the mechanism portion 38 is in the expanded state, the opening 40 allows the passage 24 and the engine fractionation cell 39 to pass through each other, and the opening 41 allows the passage 25 and the engine fractionation cell 39 to pass through each other. do. Sample gas from the engine fractionation cell flows upward through the analysis fractionation passage 24 by the mass spectrometer, and the engine sample gas is returned to the engine fractionation cell through the return passage 25.

The upper end of the endotracheal tube is detachably connected to the motor pump and mass spectrometer module 12 by a manifold 42 that is part of the pump and mass spectrometer module. And a manifold body 43 having a reduction portion 43a protruding into the tube 13. The manifold body has a male threaded portion 44 screwed to a nut 45 having an inwardly annular lip 45a. The inwardly annular lip 45a engages with the hard annular member 18 fixed to the upper end of the endotracheal tube and detachably fixes the endotracheal tube to the multi-pipe. The hard annular member 18 has an opening therein for communicating with each passage of the endotracheal tube.

The manifold body 43 has an L-shaped passage 46 extending into the reduction portion 43a and communicating with the central passage 15 of the inner tube 13. The manifold body is provided with a connector 47 having a soft hose 48 connected to an oxygen and anesthetic gas source supplied to the subject's lungs in a conventional manner as detailed in FIG. 17. Thus, the mixture of oxygen and anesthesia gas enters into the central passage 15 for circulation of the endotracheal tube through the passage 46 and circulates in the subject's respiratory system when anesthetizing the subject.

Referring to FIGS. 7 to 9 and 14 and 15, it can be seen that the manifold body 43 is provided with a passage 49 for communicating with the aliquot passage 20 of the endotracheal tube 11. . In addition, the manifold body is provided with a passage 50, a passage 51, and a passage 52 therein. The passage 50 communicates with the return passage 19 of the endotracheal tube and the passage 51 communicates with the tracheal aliquot passage 24 of the endotracheal tube. The passage 52 in the manifold body communicates with the passage 25 of the endotracheal tube and returns the tracheal tissue sample gas to the tracheal aliquot cell 39.

Manifold body 43 is provided with passages 53, 59, and 56 therein, as shown in detail in FIG. 7. The passage 53 communicates with the passage 21 of the endotracheal tube and the passage 56 communicates with the passage 23 therein. The passage 59 communicates with the passage 22 in the endotracheal tube through which air of constant pressure, which expands or contracts the instrument portion 33.

It can be seen that the gas under pressure in each of the regions located above and below the mother pipe restricting member 27 flows through the passages 53 and 56 to the differential pressure transducer in which the lung capacity is measured. Here, the passage 53 is provided with a connector 54 to which the hose 55 is attached and eventually connected to the differential pressure transducer. Similarly, the passage 56 is provided with a connector 57 having a hose 58 in communication with the differential pressure transducer. Finally, the passage 59 is provided with a connector 60 having a hose 61 connected to the connector 60 and connected to a suitable small pump or similar pressure generating device which expands and contracts the mechanism 33.

In addition, the manifold 43 is provided with a cylindrical groove 62 for receiving the rotary valve 63. The rotary valve 63 includes a cylindrical valve body 64 having a pair of valve holes 65 and 66 spaced apart from each other as shown in detail in the eighth, ninth, 14th and 15th degrees. The valve body 64 is provided with a small handle 67 at one end thereof to facilitate the rotation of the valve body in the manifold. In addition, the valve body is provided with a sealing member 68 spaced apart in the axial direction of the conventional structure as shown in detail in FIG. The photoelectric position sensor 69 is fixed to the valve body 64 and is provided with a suitable electrical inducer for detecting the position of the valve body upon operation of the gas sensing device 10. Here, the valve body can rotate the passages 49 and 50 in an arc of 90 degrees such that the mass spectrometer or passages 51 and 52 selectively communicate with each other through the mass spectrometer apparatus. This arrangement makes it possible to fractionate and measure the gas in the lungs or alternatively to fractionate and measure the organ tissue gas. The photoelectric sensor 69 generates a visible signal indicating that a preparative procedure is observed.

Referring to FIGS. 10, 11, 13 and 16, it can be seen that the manifold is connected to an air driven motor pump 71 consisting of a cylindrical motor pump body 72. Appropriate means such as, for example, locking pins can be used to securely mount the gear motor pump 71 to the manifold 42. The motor pump body 72 has a hollow inner side provided with a partition plate 73 for dividing the inside of the pump body into the motor chamber 74 and the pump chamber 75. The partition plate 73 is engaged with the annular shoulder portion 72a in the pump body 72 which determines the proper position of the partition plate. The divider plate 73 has shaft pins 76 and 77 which are spaced apart by a predetermined distance protruding from one surface of the divider plate. The shaft pins 76 and 77 protrude toward the motor chamber 74 and define the center of the pair of cylindrical partition chambers of the motor chamber, respectively. The divider 73 also includes shaft pins 78 and 79 that extend to the other surface of the divider and are spaced apart at regular intervals protruding into the pump chamber 75. It should also be noted that the shaft pins 78 and 79 define the center of the pair of compartments in the pump chamber, respectively. It should also be noted that the shaft pin 76 is disposed coaxially with the shaft pin 78 and the shaft pin 77 is disposed coaxially with the shaft pin 79.

Referring again to FIGS. 9, 10, 11 and 14, the motor pump body 72 is provided with a pair of axial extension passages 80 and 81 disposed therein at regular intervals. The motor pump body 72 is also provided therein with an axial extension passage 82 and a radial extension passage 83. The passages 80 and 81 communicate with the pump chamber 75 and the passages 82 and 83 communicate with the motor chamber 74. The passage 80 defines a preparative passage to which the sample gas of the waste pipe preparative cell is directed, and the passage 81 defines a return passage through which the waste gas sample or the engine tissue gas sample returns. The passage 82 defines an inlet passage that provides the driving force for driving the motor pump. The air passage 83 defines an outlet passage through which air under the driving pressure of the motor pump is discharged. Here, the pump body is provided with a connector 84 having a hose 85 through which air discharged from the air outlet passage 83 flows.

Referring again to FIG. 10, the upper drive gear 86 has a central opening 87 therein and fits on an associated shaft pin 76 for rotation. The upper drive gear 86 is provided with a plurality of symmetrically arranged gear lobes 88 and arranged in engagement with the lower drive gear 89. The lower drive gear 89 is provided with a central opening 90 and fitted on the shaft pin 77. The lower drive gear 89 is also provided with a gear lobe 91 into which magnetic elements 92 are inserted. The drive gears 86 and 89 are arranged in the motor chamber such that the outer circumferential surface of each gear lobe almost comes into close contact with the inner surface of the adjacent motor chamber. Further, the rotation shafts of the drive gear 86 and the drive gear 89 respectively define a center of the division chamber of the motor chamber 74.

Referring to FIG. 11, the pump chamber 75 is provided with a lower drive gear 93 having a central opening 94 therein and fitted onto the shaft pin 79. The lower drive gear 93 has a plurality of gear lobes 95 each arranged symmetrically with one of the plurality of soft iron core elements inserted therein.

The lower drive gear 93 in the pump chamber 75 has a central opening 98 and is disposed in engagement with the upper drive gear fitted on the shaft pin 78. The drive gear 97 is also provided with a gear lobe 99. It should be noted that the outer circumferential surfaces of the drive gear 93 and the drive gear 97 are disposed close to the inner surface of the pump chamber 75. In addition, when the drive gear 86 of the air drive motor pump is driven by the pressure air introduced through the passage 82, the gear 86 drives the gear 89 and the rotational driving force is the interaction magnetic element, respectively. And soft iron core elements 92 and 96 and ultimately drive lower gear 93 and gear 97. Motor driving air flow is constantly discharged through the air passage 83 during the operation of the motor and pump.

The motor pump body 72 is provided with a sealing plate 110 having a central outlet 111 therein. The gas sample of one of the lung or tracheal aliquot cells is discharged from the pump chamber to the mass spectrometer 100 through the central outlet 111.

Referring to FIG. 13, the motor pump 71 is detachably connected to a small mass spectrometer 100 including a 101 of a cylindrical housing or body made of stainless steel or the like. Although not shown in the figures, it is to be pointed out that the housing 101 of the mass spectrometer is connected to the motor pump body 72 by suitable releasable connecting means, for example coupling pins, which facilitate assembly and disassembly of this part.

The housing 101 of the mass spectrometer is a double wall structure including an inner wall 103 spaced apart from the outer wall so as to form the cylindrical outer wall 102 and the cylindrical cooling chamber 104. The housing 101 also includes a front end wall 105 integral with the cylindrical inner and outer walls. The circular ceramic header 106 defines the back wall of the housing 101 and is fitted to the cylindrical double wall of the housing in a sealed relationship.

The front end wall 105 is provided with an axial opening 107 that is sealed by a closure plate 108 having a laser machined inlet 109. In the illustrated embodiment, three inlets are provided through which the sample gas to be measured is passed. The inlets 109 are close to each other and each have a diameter of about 0.5 microns. The use of three separation holes in the mass spectrometer is intended to mitigate blockage by foreign material. Since mass spectrometer vacuum systems operate within limited conductance, failure of one or several holes is immediately detected by a change in operating pressure. This blockage is signaled to the operator but does not interfere with the continued use of the mass spectrometer.

The sample gas to be measured is discharged through the outlet passage 111 of the motor pump and enters the inlet 109 of the mass spectrometer. However, the volume accumulator chamber 112 enters the inlet 109 of the mass spectrometer. However, it should be noted that the volume accumulating chamber 112 is defined between the sealing plate 108 of the mass spectrometer and the sealing plate 110 for the pump chamber 75.

The measured sample gas is directed through the inlet 109 to the interior 113 of the housing 101 of the mass spectrometer. The housing 101 is provided with an inlet connector 114 in communication with the cooling chamber 104. The inlet connector 114 is connected to a cooling air source under pressure to control the temperature of the interior 113 of the mass spectrometer. The passage 116 allows the cooling chamber 104 and the air inlet passage 82 in the motor pump body 72 to communicate with each other. Thus, the air under pressure used to cool the mass spectrometer is also used to drive the motor pump gear drive 71.

Referring to FIG. 13 again, the circular entrance plate or the electrode 117 having the central opening 118 therein is disposed at a predetermined distance from the sealing plate 108, but the central opening 118 and the inlet hole 109 are It is disposed adjacent to the sealing plate 108 to be arranged in a straight line. The inlet plate 117 extends through the header 106 and is connected to a suitable conductor 119 welded to the header 106. The spiral grating 120 is welded or otherwise secured to the entry plate 117 and projects there. The pair of small wire brackets 121 are fixed to the entrance plate and processed in the coil 120 of the spiral grid.

It will be appreciated that the axis of the spiral grating 120 is arranged coaxially with the opening 118 in the entry plate. The circular end plate or extraction electrode 122 having the central opening 123 protrudes and is connected to the conductor 124 coupled to the ceramic header 106. The opening 123 in the end plate 122 is disposed coaxially with the axis of the opening 118 and the spiral grating 120. The three-dimensional space formed between the spiral gratings 120 defines the ionization region and together with the entrance and end plates form the components of the ion generator.

The ion generator also includes a pair of electron emitting filaments arranged at an angle of 90 degrees with respect to each other, which are made of palladium and coated with conventional valium-strontium emitting chemicals. In normal operation, one of these filaments is heated until it releases electrons, and the other filament is kept warm to keep it uncontaminated. If the filament breaks down or becomes inoperative during use, the second filament is heated to take over the electron supply. The excited filaments are maintained at a potential 100 volts lower than the helical grating lead 120, so that the electrons are accelerated to an energy of 100 e.v. in the space between the excited filaments 125 and the helical grating 120.

Upon reaching the helical grating 120, some electrons arrive at the wire, causing a flow of current, commonly referred to as emission current. This current is sensed by the electrical circuit in a manner described in more detail below and stabilized to a constant value by the conversion of the power source to the filament.

Other electrons pass through the bend of the helical lattice to the ionization region. The ratio of electrons striking the lattice, and thus electrons passing through the electron to ionization regions that provide stabilization information, appears to be determined only by the transparency of the lattice. The transparency of the defect is the ratio of the conductor diameter to the bend spacing.

Inside the lattice, some electrons collide with gas molecules to cause ionization and fragmentation, while others pass through the lattice without interacting with the molecules or hitting the lattice coils. These non-reactive electrons pass through a conventional U-shaped trap electrode 127 that is maintained at the same potential as the helical grating 120. In this regard, each filament 125 has a U-shaped trap electrode 127 disposed opposite thereto. Each U-shaped trap electrode is provided with one ion collecting lead 128 which monitors the total number of ions generated per unit time to measure the gas pressure inside the spectrometer. An ion collection lead 128 of each U-shaped trap electrode 127 protrudes and is coupled to the header 106.

Therefore, the number of ions generated in the helical lattice depends upon the ionization cross section of the given kind, the number of ions of the type between the helical lattice and the electron density between the helical lattice when it is exploded into 100 e.v. electrons. Since the electron density is kept constant by the emission stabilizer and the ionization cross section does not change over time, a given kind of ionized water per unit time depends only on that kind of partial pressure in the ionization region. These ions migrate to the distal end of the spiral grating 120 away from the inlet gap 118 in the inlet plate 117. Some of these ions enter the linear accelerator 129 of the spectrometer through the opening 123 in the end plate 122.

It will be appreciated that the spectrometer components of the interior 113, including the linear accelerator, are attached to or made of a multi-fixed glass or ceramic feed through the header 106, which is a common standard structure. The linear accelerator 129 consists of a plurality of substantially identical triangular plates or acceleration electrodes 130 spaced apart in the axial direction, which are mounted rods 132 provided with an annular separator or spacing piece 132 made of mica. Overlapping or mounted on the The extended upper bus rail 133 and lower bus rail 133a energize the plate 130 so that these bus rails protrude and are coupled to the header 106. In the illustrated embodiment, the plates 130 are alternately connected to the rails 133 and the rails 133a, respectively. For example, the plates (1), (3), (5), (7) and (9)... Is connected to the top rail 133 shown in FIG. 13, while the plates 2, 4, 6, 8. Is connected to the lowermost rail 133a. Each plate 130 has a central opening 134 therein, the openings being axially aligned with each other and with respect to the opening 123 of the extraction active 122.

The linear accelerator also has an ion collecting element or plate 135 positioned adjacent to the header 106 and aligned with the axis of the opening 134 of the acceleration electrode. The ion collection plate 135 is provided with a suitable conductor 136 that protrudes and is coupled to the header 106. The shield box 137 is disposed around the ion collecting element 135 and has a gap 138 which is also disposed in the axial direction with the opening 134 of the acceleration electrode. The shield box 137 fixed to the conductor 139 mounted to the header 106 serves to minimize the high frequency transmitted to the ion collector plate 135 at the bottom.

The mass spectrometer housing 101 has an opening 140 therein in communication with the interior 113. The connector 141 is fixed to the housing in the opening 140 and the connector is fitted with a connecting member 142 for connection with a vacuum source. For example, the connecting member consists of a hydraulically formed thin film steel bellows having an effective diameter of 1.5 centimeters. The connecting member 142 is connected to a vacuum source such as a vacuum pump VP as shown in FIG. 17. Since the mass spectrometer device is a miniaturized structure, and as shown in the examples, the length of the passage is about 1 centimeter, the analyzer can be operated at a vacuum of 1E ^-3 torr. This degree of vacuum can be obtained by remote pumping, including variables that allow the power pump and mass spectrometer module to be mounted directly to the end of the endotracheal tube. Although the analyte shown is about 1 centimeter in passage length, it is believed that a reduced analyte having a passage length in the range of about 0.5 to 2 centimeters is also effective.

To understand the operation of a mass spectrometer, you need to define the potentials that exist within it. As noted, the electron emitting filament 125 operates at a voltage 100 volts lower than the helical grating 120 and the entrance plate 117. Spiral grating 120 and inlet plate 117 operate at a voltage several volts lower than the earth potential and ions generated between the helical grating or cage 120 are present at supertemperature energy at potentials several volts below the earth potential. . The exact potential of the initial ion can be adjusted during the initial setup of the assay system to establish the mass determination of the assay system at the desired value.

The ion collection lead 128 of each U-shaped trap electrode 127 operates at a 20 volt low potential for the connected electron emitting filament 125, thereby attracting positive ions, from the filaments reaching the collector lead Of electrons are avoided. It is pointed out that each U-shaped trap electrode and its associated ion collection lead are actually identical to that of a conventional Bayard Alpert ionization gauge. In a typical Bayard Alpert gauge run, the ion collecting lead is operated at zero potential to minimize leakage to, or from the collecting lead to the ground or other electrode.

However, in this embodiment, since the operating voltage of the analyzer is high, the ion flow is relatively large so that the loss of sensitivity or stability associated with this method of operation can be ignored.

The end plate 122 of the ionization region is operated at a potential 5 volts lower than the helical grating 120 and the entry plate 117. The ions in this region are therefore attracted to the end plate 122 and are directed to the linear accelerator 129 through the opening 123 therein.

As soon as the ions pass through the end plate 122 of the ion generator, they are accelerated by a potential of -100 volts supplied to the first electrode 130 of the linear accelerator 129. This acceleration reduces the two desired effects, namely, the rate expansion of the ionized particles by about 2.5%, and the end plate 122 and the first accelerator electrode 130 of the linear accelerator electrically cooperate with each other to form a gap lens. Do it. Particles emerging from the ionization zone branch and the gap lens recollects the particles to concentrate at the upstream end of the linear accelerator 129. Since the linear accelerator 129 itself is in focus, the intensity of this first lens is adjusted (by adjusting the spacing between the end plate 122 and the acceleration electrode 130) to bring the desired ions into the linear accelerator 129. In the ion collecting plate 135 at the downstream end of the.

The accelerator plate 130 is excited by the bus rails 133 and 133a, all of which are held at the same potential as the initial acceleration electrode downstream of the end plate 122. However, each of the bus rails 133 and 133a has an overlapping symmetric high frequency voltage with a peak value of 5 volts. Therefore, at a given time, if the top rail 133 is at +3 volts relative to the acceleration voltage, then the bottom rail 133a is at -3 volts. If the time to reach the space between the plates 1 and 2 of the linear accelerator 129 is an ion of the plate 1 +5 volts, the plate 2 is at -5 volts. This ion will be accelerated by the 10-volt potential and enter plate 2 with an energy greater than 10 electron volts than before.

Assuming that the velocity of this ion during the passage of the thickness of the plate 2 is this, the required time is equivalent to 1/2 cycle of high frequency energy. When ions are released from the plate 2 and enter the plate 3 across the gap, the bottom busrail 133a and plate 2 are at a potential of +5 volts, while the top rail 133 and plate ( 3) is -5 volts potential. Therefore, this ion gains an additional 10 electron volts of energy when entering the third plate. If the thickness of the plate or electrode is chosen so that these ions stay in phase and the time required to pass through the plate is always 1/2 cycle of high frequency, energy of 10 electron volts is obtained at each interval. The result is 150 electron volts of energy from the 5-spaced, six-plate stack.

Let's assume that ions continually flow out at an accurate initial rate of 1/2 cycle of high frequency to pass through the plate thickness, but reach all possible times depending on the potential of the high frequency cycle. Some ions will reach the gap at the optimal time as described above; Some ions will pass through the structure without being accelerated in the absence of a high frequency potential difference, while others will arrive when the high frequency potential is in the delay direction and will be present in the stack below the initial energy of 100 electron volts. .

Let's consider a case where ions reach the accelerator stack at the correct speed. Whatever the time to reach its first gap with respect to the instantaneous potential, due to the different time, high frequency energy, these ions will notice the plate thickness, so the moment of penetration of the inner plate gap is never exactly equal to the maximum acceleration potential difference in each gap. Cannot match. The phase of this ion is constantly changing with respect to the phase of the high frequency potential difference across each gap. Best of all, these erroneous ions are only part of the maximum acceleration and are present between the gap structures with less than the maximum possible energy.

Velocity is proportional to the inverse of the square root of mass. Thus, for a given frequency of high frequency energy, only one mass of ions with the correct velocity of maximum acceleration when passing through all the gaps will correspond. Therefore, when the frequency of the high frequency energy changes, the optimum residence time in each plate also changes. Thus, changing the high frequency is a way to fit the analytical system to different accelerations, and therefore optimal acceleration ions of different masses.

In order to perform the desired measurement function, the optimum accelerated ions must be identified by all gaps in the acceleration region. Ions are collected by the earth potential electrode plate 135 facing the opening 134 of the final accelerator plate 130. Since ions were generated in the ionization region at a negative potential with respect to zero, unaccelerated ions cannot reach on the collecting plate 135. By changing this potential to a more negative value, more acceleration may be required by the ions prior to reaching the collector plate surface, thereby generating an ion flow signal as an ion outflow measure. For example, when the helical grating 120 is operated at a potential of -30 volts, the ions need to obtain 30 electron volts (e.v.) in the linear accelerator to reach the collecting plate. Therefore, by requiring energy of expected magnitude, for example, only a certain mass of ions can reach the collecting plate 135. This selectivity can be arbitrarily changed by altering the desired energy gain, usually in exchange for more rejection of the correct mass of ions.

To test the quantitative form of the ion outflow curve, we follow an effective way to perform mote Carlo calculations, starting with particles with different injection angles and different velocities at the inlet to linear accelerator 129 at random times for high frequency cycles. . Following these particles through the accelerator stack allows for effluent distribution and high frequency at any particle velocity combination (and therefore for mass).

Mass spectrometer 100 avoids the inefficiency that many of these ions do not reach the ion collector plate 135 because many ions of the selected mass reach the first gap of the linear accelerator 129 at the wrong phase of the high frequency cycle. This inefficiency, however, does not exist in the present invention. Since the acceleration of ions is generated by the electric field in the axial direction, there may be a difference depending on the type of ions in the extremely dense structure. As pointed out above, the average free path required for the majority of ions that can reach the collection plate 135 without large angle collapse is very small, which means that the mass spectrometer 100 of the described embodiment is about 10E- ³ . It can be effectively operated at a pressure of 10E ^-2 torr. In addition, since the mass spectrometer of this invention measures the respiratory gas from a human body object, this sample gas can be calculated | required in liter amount to the atmospheric pressure of the part facing the atmosphere of the inlet or hole 109 of a mass spectrometer.

5 and 6, a disposable mouthpiece device 143 is shown, which is an alternative to endotracheal tubes as a device for continuously rotating the gas measured through the motor pump and mass spectrometer module 12. You will see that it is constructing. Disposable mouthpiece device 143 is formed of a suitably flexible plastic material and includes a double-walled mouthpiece tube 144 consisting of an inner tube 145 and an outer tube 146. Although not shown in the figure, the parts of the wall connecting the suitable interior connect the interior and exterior tubes and define four auxiliary passages rather than the seven passages specified in the endotracheal tube 11. Inner tube 145 defines a central large passageway in the manner of an endotracheal tube. Again in FIG. 6, the mouthpiece tube 144 extending to the tube length of the mouthpiece is provided with an extension passage 148 and an unison passage 149. The lower end of the mouthpiece tube is provided with an opening for passing through the passage 148 and an opening 154 for passing through the passage 149. Sample gas from the waste will travel straight through passage 148 through opening 150, while some of these gases will return through passage 149 and exit outlet 151. Thus, the passage 148 constitutes a passage of the sample gas while the passage 149 means a return passage.

The face attachment flange element 152 is in close contact with the outer tube 146 and is suitable for attaching to the outer surface of the face adjacent the subject's lips. The capillary restricting member 154 is proximate to the lower end of such a mouthpiece tube and the capillary restricting member is equipped with a plurality of capillaries or passages 155 extending as shown in FIG. In this respect, the assembly of the capillary restraint member is substantially the same as that shown in the endotracheal tube.

The inner tube 145 has an opening 157 located below the cap restricting member 154 and also has an opening 158 adjacent but slightly above the cap restricting member. Although not shown in the figure, the opening 157 is connected to a passage through which the gas of the lung moves to the differential pressure converter via the manifold. Similarly, opening 158 is also connected to a passage through which the gas of the lung travels through the manifold to the differential pressure transducer. Thus, the disposable mouthpiece device 143 vanes gas measurement of the lungs by a mass spectrometer and also allows spirometry by means of a differential pressure transducer means.

Disposable mouthpiece devices are primarily intended for testing cardiac blood ejection and other deep breathing functions during office visits for non-anesthetized patients, and for measuring exercise response or drug response, such as aberration methods. . Since lung gas is obtained from the back of the subject's mouth, it will be seen that the mouthpiece device does not have some efficiency for the endotracheal tube. The dead space defined between the posterior or lower portion of the mouthpiece device and the lower or lower bronchus portion makes it less efficient in the mouthpiece body than the endotracheal tube. However, the mouthpiece device can be readily used with a cognitive patient with little or no discomfort.

17 and 18 schematically show an analyzer circuit together with the mass spectrometer 100. The electronic circuit device is generally indicated by reference numeral 160 and consists of a base device 161 and an upper device 162. The top device, including calculation readings and arithmetic inputs, is of a lightweight mobile assembly and can be installed in the anesthesia vehicle as shown in FIG. The reservoirs do not require an operator or anesthesiologist to handle or otherwise interact with the part so that the vacuum module and the steel can be positioned horizontally with other parts.

Since the analyzer requires an approximate 100V potential and is close to the patient, all analyzer electricity supply requirements are assembled in an ungrounded manner using an ungrounded transformer and assemblies approved in this application. The purpose of this non-grounding approach is to ensure that leakage or other leakage to the ground via the patient causes non-detection currents, thus protecting the patient from injury. In addition, active currents in the ground detected from the ungrounded electronics will generate an immediate interruption and signal the operator's fault condition.

The transmission of the top and base devices is by means of two fiber optics that not only provide an ungrounded image but also eliminate the transmission of electromagnetic interference to the top device. In the presented embodiment, any one of the fiber optic cables 165 conveys information that changes the frequency of the high frequency energy used in the analyzer to tune with ions of different masses. In the ion collecting plate 135 of the analyzer, the outward optical fiber cable 166 receives digital information of the ion current collected by the ion collecting lead 128 and measures the electric potential supplied to the analyzer device in the absence of a defect state. to provide.

The base device 161 includes a direct current power source having a filament current source 164 and controlled by the electron emission current received on the spiral grating 120 in the ionization zone, and stabilizing such emission current to a given value. The filament current source 164 also senses the non-flowing state of the filament current with respect to the voltage used and, if found, switches to the second filament. The upper unit confirms the completion of the changeover and signals the operator by visual or audio signal. During operation of the device 10, the top device also detects and determines that current is passing through both filaments and to shut down if only one filament can be activated. The current for the inert filament will be supplied through the resistor until further filament is needed.

The DC power supply 163 also has a 100V electron accelerated current source 168 and forms a feedback signal for the filament source 167. The 120-V supply current 169 deflects the pressure sensitive ion collection lead 128. This current is separated from the rest of the analyzer and supplies a zero volt bus so that ion current flow can be detected at the bus potential and diverted to the top device 162. The current source 170 of 100V supplies the current to operate the linear accelerator 129. This current source is regulated at an audible frequency by a sinusoidal wave of 1-2V amplitude. In the ion collecting plate, the final ion current is a phase detected as an audible signal as a reference. The output thus obtained is used to change the 100V potential of the correct value to maximize the ion current, i.e. to have the smallest first harmonic component in the phase detection ion signal. This modification keeps the analyzer 100 air-conditioned and, in addition, does not require possible routine adjustment of the structure due to order displacement and errors in the upper part of the analyzer.

Programmable direct current supply 171 has a 30V programmable current source or conductor 172 and is regulated by input from top device 162. The current source 172 is adjusted to an acceleration state necessary for being attached to the grounded ion collecting plate 135 according to the potential at which ions are generated. The potential of such a source is also sensed by the top device 162.

The base unit 161 includes a programmable high frequency generator 173 in which a high frequency signal is converted into an analysis system by two coaxial cables 174, each of which is terminated by a repetitive impedance. The high frequency generator, together with the harmonic multiplier, consists of a group of crystal controlled oscillators and a wide band power amplifier capable of transmitting a high frequency signal having an amplitude of 5-V peak to the analyzer. The output level is rectified and fed back to the power amplifier to preserve the magnitude of the high frequency amplitude constants. Switching of the oscillation period is controlled by the control means in the upper device 162 to select another ion species for analysis. In general, the conversion between ionic species will be determined by the settling time of the ion collection amplifier.

The base unit 161 also has an auxiliary heat regulator and a pressure transducer 175 having a current source conductor 176 and a current source conductor 177 electrically connected to a pair of auxiliary heat regulators, the function of which is described later. Will be more clearly described. The pair of current source conductors 178 also electrically connects the power source 175 with the differential pressure transducer 179. The output signal from the differential pressure converter 179 is transmitted to the multiplexer 180 via the conductor 81. Multiplexer 180 is part of a data acquisition device and also includes a control electronics for transmitting digital information to 10-bit analog-to-digital converter 182 and top device 162.

In addition to transmitting analyte ion current data, analyte pressure ion current data, and analytical parameters, the multiplexer 180 also transmits data obtained from a Zener reference source to test the continuous functionality of the multiplexer-analog digital converter.

Ion current amplifier 183 is installed as an upper amplifier in connection socket 184 of mass spectrometer header 106 and is followed by a second amplifier (not shown) at the module end of the connection cable for the connection socket. The use of an upper amplifier eliminates the problems associated with large cable capacitance otherwise associated with distant amplifiers.

The upper device 162 is composed of a system controller and is connected to the analyzer through the optical fiber cables 165 and 166. The system controller actually consists of a microcomputer 185 connected to a series of input and output terminals and can be assembled from any type of commercial central processing unit of the required capacity. In the presented embodiment, it will be appreciated that the microcomputer or CPU has been replicated for maximum reliability and for continued measurement even if run-wild or interruption occurs in the device. It also appears that each CPU is equipped with a set of monitors to detect errors.

The apparatus also includes a display and user interface 186 and may be a conventional screen-keyboard, conventional LCD panel, or contact input table. The upper device includes a digital-to-analog converter 187 and can be operated from a signal line input from the upper device 162. The digital to analog converter 187 is connected to the analog to digital converter 182 through any one channel of the multiplexer device. Therefore, the operation test advances the stepped wave formation on the digital analog computer together with the analog-to-digital converter 182 for converting each step. The fact is that in the absence of an error code, the forging can be checked by both the digital to analog converter 187 and the analog to digital converter 182. In operation, the digital-to-analog converter 187 generates the starting potential of the ions when set to the level of the power supply.

Although not shown in the drawings, it is a document that provides information about the patient's progress during surgery and is available for future use, such as future possible lawsuits, in a central recording area where analysis system data can be continuously recorded in an internal modulation environment. Output lines are provided.

During operation of the device, the manifold rotary valve 63 will be adjusted to a position for measuring sample gas from the engine at the bottom or from the engine fractionation cell 39. If the gas from the lung is fractionated, then the top device of the apparatus will indicate that this action is being performed and that the tracheal aliquot cell 39 is not used.

In a normal person, during quiescence, the distension of the lungs and the amount of cardiac output are necessarily the same. All CO ₂ recovered from respiratory air and all O ₂ consumed reflect blood flow to the right ventricle. Since the ejection volume of the left and right ventricles is substantially the same, the latter is the amount of cardiac blood ejection. The general expression for such a relationship is a well-known form of Fick.

Q = Vx / (Cax-Cvx)

In the above formula

Q = cardiac blood output

Arterial Concentration for Cax = x

Mixed Vein Concentration for CVx = x

Total amount for Vx = x

This indication is positive for inhalation state (X = O ₂ ) and negative for output state (X = CO ₂ ).

Cardiac blood ejection can be measured by a single breathing method or a CO ₂ respiration method. The single breathing method uses the respiratory exchange rate taken during a sustained expiration (10 seconds). A detailed discussion of the single breathing method and its calculations are given in the magazine Applied Physiology, 21 (4): 1338-1344; In 1966, TSKim et al., `` Estimation of True Venous and Arterial PCO ₂ by Gas Analysis of a Single Breath ''.

The rate of respiration exchange taken during continuous exhalation (10) is expressed by the following equation.

In operation of the test apparatus, mass spectrometer R yields data representing a curve calculated continuously during the continuous expiration. At various intervals the tangent slope (S) is used to derive the instantaneous R value from the following form of alveolar air.

About R

Various instantaneous values for R are then made for their corresponding measurement PCO ₂ (arterial-alveolar). This fact allows for the assessment of suitable arterial and mixed venous CO ₂ pressures that must be present. The PCO ₂ of the arteries is obtained from the averaged R values from various normal exhalations that are significantly ahead of the normal inspiration followed by the sustained exhalation (10 seconds).

In humans, time mixed vein PCO ₂ is obtained by intercepting R values at R = 0.32. At these values of R = 0.32, PCO ₂ in the arteries and veins are the same (no pressure gradient), but CO ₂ is still exchanged at one-third of its normal rate due to the Haldane effect. The unit volume of O ₂ taken by hemoglobin from the venous blood at R = 0.32 clearly replaces 0.32 volume of CO _{2 with} no change in PCO ₂ . Therefore, by precisely measuring the PCO ₂ of the alveolar-artery when the instantaneous exchange rate R is 0.32, a value which should be equal to the PCO ₂ of the mixed vein is obtained.

The point of this simple breathing method is the ability to measure PO ₂ and PCO ₂ at the same instantaneously over time enabled by a micromass spectrometer attached to the upper end of the endotracheal tube or mouthpiece device while removing the maximum amount of pores. . The heart rate and interrelationship of these data is important in the single breathing method.

When cardiac blood ejection is measured by CO ₂ respiration, this method is simple and is performed in less than 30 seconds. Specifically, this method is based on measuring the time taken for the rebreathered CO ₂ to reach the plateau. A detailed description of this method is described in a paper entitled "Cardiac Output Determination by Simple One-Step Rebreathing Technique" by LEFarhi et al. In Respiration Physiololgy (1976), 28, 141-159. However, the apparatus of the present invention shortens the time required to reach Plato because it obviously increases accuracy and reduces dead space.

The correlation between CO ₂ respiration and heart rate is important, but not as important as single breathing. During the use of single breathing and CO ₂ rebreathering, it is shown that the waste gas is refluxed through the endotracheal tube gas sample 20 and returned through the return passage 19. If the mouthpiece device 143 is used, the sample gas is directed upward through the sample gas passage 148 and returned through the return passage 149.

The spirometry or volume is measured by a differential pressure transducer and receives the sample gas from above and below the maternal restraint member 27 in the endotracheal tube or the maternal restraint member 154 in the disposable mouthpiece device. The location of the capillary restricting member 27 of the endotracheal tube or the capillary restricting member 154 in the mouthpiece device is selected such that the temperature of the capillary is close to body temperature, thus eliminating moisture accumulation in the capillary. The flow of gas through these capillaries represents the pressure difference through the associated passage to the differential pressure transducer for measuring the respiratory volume.

While both instrument sections 33 expand and act as retention members while collecting gas from the lungs by means of an endotracheal tube, these instrument sections also define a tracheal aliquot cell for use in analyzing gas from tissue cells. Aliquots from such tracheal spaces are performed at equilibrium with the tissue of the trachea and will measure tracheal O ₂ (and CO ₂ ) and will closely reflect the PO ₂ of the artery. This sample gas represents tissue PO ₂ in other parts of the body, and thus represents the accuracy of oxygenation. This specific method reduces or entirely eliminates the need for an arterial sample by performing an effective arterial PO ₂ measurement in a selective non-insertion method.

Argon gas is blown out from the engine fractionation cell (39) through an opening or terminal connecting the fractionation with the engine fractionation cell, and argon gas is passed through the mass spectrometer for analysis until the argon gas reaches an equilibrium state in the engine fractionation cell. It is carried out by reflux.

It also shows that a trace amount of gas, such as acetylene, can be introduced into the aerobic mixture to determine the lung reflux time with the organ. This is a useful physiological measurement of blood reflux efficiency. Moreover, inhalation kinetics of acetylene can be used to test local blood flow in organ tissues.

In addition to measuring the physiological parameters and properties described above, the instrument of the present invention may measure another aspect of respiratory function. In view of this, the device can measure the diffusion capacity of the lung and anatomical and physiological side flow to the anatomical respirator, physiological respirator, O ₂ and CO ₂ . Regardless of the sample gas source measured, it will be confirmed that these sample gases will go directly to the mass spectrometer via the motor pump apparatus 71. The use of an air drive gear pump ensures that the rectified flow of gas passes through the fractional opening of the mass spectrometer. Although fluctuations in the fill rate occur as a result of the meshing cycle of the gear teeth, such fluctuations in the flow rate are not significant for the breathing cycle.

In order to observe the flow of air, two electrothermal regulators are placed in the flow of preparative gas. One of the heat transfer regulators is positioned above the pump's rotor and the branches are positioned below the pump's rotary gear. The upper thermostat will be used to control the volume of the respiratory air to the standard temperature, while the lower thermostat supplies enough electrical energy to self-heat to a little higher than room temperature. Periodically, this lower electrothermal regulator interrupts the flow of electrical energy and the cooling rate is measured. The cooling rate will indicate the continuous flow of gas around the ring. If the sample gas passage or return passage is closed, or if the rotary gear does not rotate for some reason, the operator of the instrument realizes this error by an abnormal cooling rate of the lower electrothermal regulator. Positioning the thermostat on the opposite side of the pump gear provides thermal separation between them.

It will be confirmed that the major portion of the sample gas that goes directly to the motor pump will be returned via a specific return passage and only a small amount of sample gas will be released to the mass spectrometer. Return of sample gas for complete mixing of alveolar gas does not alter the ventilation of the measured lung. This return and remixing of the sample gas reduces the delay time that the gas reaches the mass spectrometer to a negligible value compared to the intake and discharge times.

In the foregoing, it will be seen that for perceptive and other anesthetized or unconscious operators, the new gas fractionator provides a non-insertable means for precisely and mechanically examining cardiac blood ejection and deep breathing function. Because the endotracheal tube and the mouthpiece are disposable, the motor pump and mass spectrometer module can be easily separated from them and reused after centrifugation. The gas fractionation efficiency of the device, in particular the endotracheal tube, is greatly enhanced by the removal of pores. The provision of a small motor pump mass spectrometer module allows this efficiency to be achieved. Micromass spectrometers with 1 / 2-2 cm free mean paths are simply unknown in the medical and related arts.

Accordingly, it will be appreciated that there is a desire to provide a non-insertable device for testing cardiac blood ejection and other respiratory functions in a more efficient manner than known comparators.

Claims (6)

A small mass spectrometer for use with a medical instrument, the mass spectrometer having an inlet through which a gas sample to be measured is introduced, the housing having an opening therein, and the internal pressure of the housing maintained at 10E ^-3 torr. Means for connecting an opening in the housing to a vacuum source, an ion generator disposed adjacent to the inlet in the housing and connected to an electrical energy source, the inside having a spiral grating defining an ionization zone; An electron-emitting filament disposed within the housing and connected to a current source, which, when excited, emits and accelerates electrons toward the helical lattice to segment and ionize gas sample molecules in the ionization zone, adjacent to the ion generator in the housing. Axially arranged, spaced apart and aligned with each other A linear accelerator comprising a plurality of acceleration electrode plates each having a central opening defining an acceleration path, an ion collecting plate disposed adjacent to a lower end of the acceleration electrode plate of the linear accelerator in the housing, and ions linearly accelerating Means for connecting the linear accelerator to a current and a high frequency source having a potential difference with respect to the potential of the ion generator such that the linear accelerator is deflected toward and gradually accelerated through an opening in the accelerating electrode plate and collected in the ion collecting plate to generate an ion current; It is composed of an electrical circuit connected to the mass spectrometer for analyzing the sample gas, the mass spectrometer characterized in that the length of the free path of the mass spectrometer from the inlet to the ion collecting plate is about 0.5 to 2 cm. 2. The pair of busses of claim 1 wherein the acceleration electrode plates of the linear accelerator have a triangular configuration and the means for connecting the acceleration electrode plates to a current source are each connected to alternating electrode plates to provide a deflection potential within the gap between adjacent plates. Mass spectrometer comprising a rail. 3. The mass spectrometer of claim 2, wherein the bus rail is electrically connected to a high frequency generator operative to superimpose a high frequency voltage on the rail at a peak value of about 5 volts. 2. The mass spectrometer of claim 1, wherein the mass spectrometer comprises an ion collecting trap disposed at a position in the housing opposite the electron-emitting filament, the ion collecting trap being connected to a current source and wherein the housing is in operation. Mass spectrometer characterized in that to observe the gas pressure inside. The extraction electrode plate of claim 1, wherein the ion generator includes an inflow electrode plate having an opening formed therein and disposed adjacent to the inlet of the housing, and an extraction electrode plate having an opening formed therein and disposed between the spiral lattice and the linear accelerator. Wherein the inflow electrode plate is connected to the helical grating and the extraction electrode plate is connected to a current source, and has a potential different from that of the helical grating and linear accelerator, for accelerating ions deflected from an ion region toward the ion collecting plate. Mass spectrometer, characterized in that. 2. The mass spectrometer of claim 1, wherein the mass spectrometer comprises a motor pump unit connected to the mass spectrometer housing, the motor pump unit having a motor pump housing having an outlet communicating with an inlet of the mass spectrometer, and the motor pump housing. A non-magnetic partition wall for dividing the interior into a motor chamber and a pump chamber, a pair of drive gears disposed in the motor chamber, and a pair of drive gears disposed coaxially with the pair of drive gears in the motor chamber in the pump chamber; And a magnetic element disposed on the drive gear in the motor chamber and a drive gear in the pump chamber coaxially disposed therewith, and connecting the motor chamber to a pressure air source to drive the drive gear in the motor chamber and the drive gear in the pump chamber. Means for guiding a sample gas into the mass spectrometer by driving a motor, the motor pump housing in communication with the pump chamber. Is a mass spectrometer comprising the separated gas passage.