U.S. patent application number 16/269418 was filed with the patent office on 2019-10-17 for spectroscopic analyser.
The applicant listed for this patent is Klein Medical Limited. Invention is credited to Donal Paul Krouse, Raymond Andrew Simpkin, Bryan James Smith.
Application Number | 20190317016 16/269418 |
Document ID | / |
Family ID | 46969417 |
Filed Date | 2019-10-17 |
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United States Patent
Application |
20190317016 |
Kind Code |
A1 |
Krouse; Donal Paul ; et
al. |
October 17, 2019 |
SPECTROSCOPIC ANALYSER
Abstract
An analyser 10 for identifying or verifying or otherwise
characterising a liquid based drug sample 16 comprising: an
electromagnetic radiation source 11 for emitting electromagnetic
radiation 14a in at least one beam at a sample 16, the
electromagnetic radiation comprising at least two different
wavelengths, a sample detector 17 that detects affected
electromagnetic radiation resulting from the emitted
electromagnetic radiation affected by the sample, and a processor
18 for identifying or verifying the sample from the detected
affected electromagnetic radiation, wherein each wavelength or at
least two of the wavelengths is between substantially 1300 nm and
2000 nm, and each wavelength or at least two of the wavelengths is
in the vicinity of the wavelength(s) of (or within a region
spanning) a spectral characteristic in the liquid spectrum between
substantially 1300 nm and 2000 nm.
Inventors: |
Krouse; Donal Paul;
(Wellington, NZ) ; Simpkin; Raymond Andrew;
(Auckland, NZ) ; Smith; Bryan James; (Auckland,
NZ) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
Klein Medical Limited |
Auckland |
|
NZ |
|
|
Family ID: |
46969417 |
Appl. No.: |
16/269418 |
Filed: |
February 6, 2019 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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15377914 |
Dec 13, 2016 |
10241039 |
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16269418 |
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14110134 |
May 19, 2014 |
9581552 |
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PCT/NZ12/00052 |
Apr 10, 2012 |
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15377914 |
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61472290 |
Apr 6, 2011 |
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Current U.S.
Class: |
1/1 |
Current CPC
Class: |
G01N 21/84 20130101;
G01J 3/28 20130101; G01N 2201/0612 20130101; G01N 21/359 20130101;
G01J 2003/1286 20130101; G01J 3/42 20130101; G01N 2201/0691
20130101; G01N 2021/3595 20130101; G01N 21/3577 20130101; G01J 3/10
20130101 |
International
Class: |
G01N 21/3577 20060101
G01N021/3577; G01J 3/28 20060101 G01J003/28; G01J 3/42 20060101
G01J003/42; G01J 3/10 20060101 G01J003/10; G01N 21/84 20060101
G01N021/84; G01N 21/359 20060101 G01N021/359 |
Claims
1. An analyser for identifying or verifying or otherwise
characterising a liquid based drug sample comprising: an
electromagnetic radiation source for emitting electromagnetic
radiation comprising at least two different wavelengths, a sample
detector that detects affected electromagnetic radiation resulting
from the emitted electromagnetic radiation affected by the sample,
and a processor for identifying or verifying the sample from the
detected affected electromagnetic radiation, wherein each
wavelength or at least two of the wavelengths is between
substantially 1300 nm and 2000 nm, and each wavelength or at least
two of the wavelengths is in the vicinity of the wavelength(s) of
(or within a region spanning) a spectral characteristic in the
liquid spectrum between substantially 1300 nm and 2000 nm.
Description
CROSS-REFERENCE TO RELATED APPLICATIONS
[0001] This application is a continuation of U.S. patent
application Ser. No. 15/377,914, filed Dec. 13, 2016, which is a
continuation of U.S. patent application Ser. No. 14/110,134, filed
May 19, 2014, which is a U.S. National Phase under 35 U.S.C. .sctn.
371 of Int'l Appl. No. PCT/NZ2012/000052, filed Apr. 10, 2012,
designating the United States and published in English on Oct. 11,
2012 as WO 2012/138236, which claims the benefit of priority to
U.S. Provisional Appl. No. 61/472,290 filed Apr. 6, 2011. Any and
all applications for which a foreign or domestic priority claim is
identified in the Application Data Sheet as filed with the present
application are hereby incorporated by reference under 37 C.F.R.
.sctn. 1.57.
BACKGROUND
Field
[0002] The present invention relates to a spectroscopic analyser,
such as a spectrophotometer, for verifying and/or identifying or
otherwise analysing drugs, blood or other substances.
Description of the Related Art
[0003] Spectroscopy, for example through the use of a spectroscopic
analyser such as a spectrophotometer, can be used to analyse
substances. For example, by directing incident radiation towards a
sample, and analysing the spectral nature of the affected
radiation, it can be possible to gain an indication of the nature
of the sample.
[0004] However, such analysers often provide inaccurate analysis.
Accurately discriminating between different substances can be
difficult.
SUMMARY
[0005] It is an object of the present invention to provide an
analyser and/or method for verifying or identifying or otherwise
characterising a drug or other substances using spectroscopy.
[0006] In one aspect the present invention may be said to consist
in an analyser for identifying or verifying a liquid based drug
sample comprising: an electromagnetic radiation source for emitting
electromagnetic radiation in at least one beam at a sample, the
electromagnetic radiation comprising at least two different
wavelengths, a sample detector that detects affected
electromagnetic radiation resulting from the emitted
electromagnetic radiation affected by the sample and provides
output representing the detected affected radiation, and a
processor for identifying or verifying the sample from the detector
output representing the detected affected electromagnetic
radiation, wherein each wavelength or at least two of the
wavelengths is between substantially 1300 nm and 2000 nm, and each
wavelength or at least two of the wavelengths is in the vicinity of
the wavelength(s) of (or within a region spanning) a spectral
characteristic in the liquid spectrum between substantially 1300 nm
and 2000 nm.
[0007] Preferably the electromagnetic radiation comprises a
plurality of electromagnetic radiation beams, each beam having a
different wavelength.
[0008] Described herein is verifying or identifying the drug sample
is against comparison data for one of a set of n drugs, and wherein
the electromagnetic radiation comprises at least log.sub.2 n
different wavelengths in one or more beams.
[0009] Preferably the different wavelengths span or capture a
plurality of at least some of the spectral characteristics in the
liquid spectrum between 1300 nm and 2000 nm.
[0010] Preferably the liquid spectrum comprises two or more
spectral characteristics, and wherein: each spectral characteristic
falls in or spans a region of the liquid spectrum, each wavelength
falls within one of the regions.
[0011] Described herein is each region is defined by a wavelength
range.
[0012] Preferably the spectral characteristics comprise peaks,
troughs, inflections, stable points or regions plateaus, knees
and/or slopes of the liquid spectrum.
[0013] Preferably the liquid is water and comprises spectral
characteristics falling in the following regions of the water
spectrum: a first region between 1300 nm and 1400 nm; a second
region between 1400 nm and 1500 nm, a third region between 1500 nm
and 1600 nm, a fourth region between 1600 nm and 1700 nm, a fifth
region between 1700 nm and 1800 nm, and a sixth region between 1800
nm and 200 nm.
[0014] Described herein is the electromagnetic radiation has an
anchor wavelength in the vicinity of the wavelength(s) of (or
within a region spanning) a stable region in the liquid
spectrum.
[0015] Described herein is each wavelength further corresponds to a
wavelength produced by a source that is readily/cheaply
obtainable.
[0016] Described herein is the source is a plurality of lasers,
each laser configured to emit an electromagnetic radiation beam at
a fixed or tuneable wavelength.
[0017] Preferably comprises a modulator for modulating the
electromagnetic radiation beam(s) emitted at the sample resulting
in detected affected radiation detected by the sample detector that
is modulated wherein the processor as part of identifying or
verifying the sample from the output from the detector removes the
dark current component from the output representing the detected
affected modulated electromagnetic radiation
[0018] Optionally the processor removes the dark current component
by multiplying the output representing the detected affected
modulated electromagnetic radiation by sine and cosine functions
and integrating over the period of modulation oscillation to remove
the dark current component.
[0019] Optionally the processor removes the dark current component
by conducting a Fourier Transform on the output representing the
modulated detected affected radiation and removing the dark current
component from the transformed.
[0020] Described herein is the processor identifies or verifies the
drug sample using reference information.
[0021] Described herein is the affected electromagnetic radiation
at or the electromagnetic radiation beam comprising the anchor
wavelength provides the reference information.
[0022] Described herein is the analyser further comprises: an
optical device for directing the plurality of electromagnetic
radiation beams to a reference sample, a reference detector that
detects affected electromagnetic radiation beams affected by the
reference sample to obtain the reference information and that
passes the reference information to the processor.
[0023] Described herein is the detector and/or source are
temperature compensated to provide temperature stability,
preferably using thermistors and peltier devices in a closed loop
system.
[0024] Described herein is each electromagnetic radiation beam is a
high intensity narrowband light beam.
[0025] Described herein is the detector is a broadband photodiode
that is biased to have a response corresponding to the wavelength/s
of the affected radiation.
[0026] Described herein is the emitted electromagnetic radiation
beams from the plurality of lasers are directed to a sample path by
one or more of: a carousel or carriage device to position the laser
beams in the sample path, or a prism, diffraction grating, beam
splitter or other optical device to redirect a radiation beam along
the sample path.
[0027] Described herein is the processor receives: output
representing the affected electromagnetic radiation from the drug
sample which provides drug sample information, and optionally
reference information for each wavelength, and the processor:
determines a representative value of the drug sample information
using that information and optionally reference information for
each wavelength.
[0028] Described herein is the sample information and reference
information correlate intensity and wavelength for each
electromagnetic radiation beam.
[0029] Described herein is the representative value corresponds to
a best fit between the sample information and optionally the
reference information.
[0030] Described herein is the representative value for the
electromagnetic radiation beam for each wavelength is compared to
stored values to verify or identify the drug sample.
[0031] Described herein is the liquid is water, there are six
electromagnetic radiation beams and the wavelengths are
substantially 1350 nm, 1450 nm, 1550, nm, 1650, nm, 1750 nm and
1850 nm, and optionally wherein 1450 nm is the anchor
wavelength.
[0032] Described herein is the sample is in an intravenous delivery
device such as an IV infusions set or syringe, or other receptacle
such as a test-cell, test-tube, flow cell or the like.
[0033] Preferably the source is a laser comprising a photodetector,
wherein the photodetector detects electromagnetic radiation from
the laser and outputs the reference information.
[0034] In another aspect the present invention may be said to
consist in a method for identifying or verifying or otherwise
characterising a liquid based drug sample comprising: emitting
electromagnetic radiation in at least one beam at a sample, the
electromagnetic radiation comprising at least two different
wavelengths, detecting affected electromagnetic radiation resulting
from the emitted electromagnetic radiation affected by the sample
and providing output representing the detected affected radiation,
and identifying or verifying the sample from the output
representing detected affected electromagnetic radiation, wherein
each wavelength or at least two of the wavelengths is between
substantially 1300 nm and 2000 nm, and each wavelength or at least
two of the wavelengths is in the vicinity of the wavelength(s) of
(or within a region spanning) a spectral characteristic in the
liquid spectrum between substantially 1300 nm and 2000 nm.
[0035] Preferably the electromagnetic radiation comprises a
plurality of electromagnetic radiation beams, each beam having a
different wavelength.
[0036] Described herein is verifying or identifying the drug sample
is against comparison data for one of a set of n drugs, and wherein
the electromagnetic radiation comprises at least log.sub.2 n
different wavelengths in one or more beams.
[0037] Preferably the different wavelengths span or capture a
plurality of at least some of the spectral characteristics in the
liquid spectrum between 1300 nm and 2000 nm.
[0038] Preferably the liquid spectrum comprises two or more
spectral characteristics, and wherein: each spectral characteristic
falls in or spans a region of the liquid spectrum, each wavelength
falls within one of the regions.
[0039] Described herein is each region is defined by a wavelength
range.
[0040] Preferably the spectral characteristics comprise peaks,
troughs, inflections, stable points or regions, plateaus, knees
and/or slopes of the liquid spectrum.
[0041] Preferably the liquid is water and comprises spectral
characteristics falling in the following regions of the water
spectrum: a first region between 1300 nm and 1400 nm, a second
region between 1400 nm and 1500 nm, a third region between 1500 nm
and 1600 nm, a fourth region between 1600 nm and 1700 nm, a fifth
region between 1700 nm and 1800 nm, and a sixth region between 1800
nm and 200 nm.
[0042] Described herein is the electromagnetic radiation has an
anchor wavelength in the vicinity of the wavelength(s) of (or
within a region spanning) a stable region in the liquid
spectrum.
[0043] Described herein is each wavelength further corresponds to a
wavelength produced by a source that is readily/cheaply
obtainable.
[0044] Described herein is the electromagnetic radiation is
generated using a source comprising a plurality of lasers, each
laser configured to emit an electromagnetic radiation beam at a
fixed or tuneable wavelength.
[0045] Described herein is wherein a modulator is used for
modulating the electromagnetic radiation beams emitted at the
sample resulting in detected affected radiation that is modulated,
and wherein identifying or verifying the sample from the output
from the output comprises removing the dark current component from
the output representing the detected affected modulated
electromagnetic radiation.
[0046] Described herein is removing the dark current component
comprises multiplying the output representing the detected affected
modulated electromagnetic radiation by sine and cosine functions
and integrating over the period of modulation oscillation to remove
the dark current component.
[0047] Described herein is removing the dark current component
comprises conducting a Fourier Transform on the output representing
the modulated detected affected radiation and removing the dark
current component from the transformed.
[0048] Described herein is the identifying or verifying is carried
out by a processor that identifies or verifies the drug sample
using reference information.
[0049] Described herein is the affected electromagnetic radiation
at or the electromagnetic radiation beam comprising the anchor
wavelength provides the reference information.
[0050] Described herein is the method further comprises: directing
the plurality of electromagnetic radiation beams to a reference
sample using an optical device, detecting using a reference
detector affected electromagnetic radiation beams affected by the
reference sample to obtain the reference information and that
passes the reference information to the processor.
[0051] Described herein is the method further comprises temperature
compensating the detector and/or source provide temperature
stability, preferably using thermistors and peltier devices in a
closed loop system.
[0052] Described herein is each electromagnetic radiation beam is a
high intensity narrowband light beam.
[0053] Described herein is the detector is a broadband photodiode
that is biased to have a response corresponding to the wavelength/s
of the affected radiation.
[0054] Described herein is the emitted electromagnetic radiation
beams from the plurality of lasers are directed to a sample path by
one or more of: a carousel or carriage device to position the laser
beams in the sample path, or a prism, diffraction grating, beam
splitter or other optical device to redirect a radiation beam along
the sample path.
[0055] Described herein is the processor receives: affected
electromagnetic radiation from the drug sample which provides drug
sample information, and optionally reference information for each
wavelength, and the processor: determines a representative value of
the drug sample information and optionally reference information
for each wavelength.
[0056] Described herein is the sample information and reference
information correlate intensity and wavelength for each
electromagnetic radiation beam.
[0057] Described herein is the representative value corresponds to
a best fit between the sample information and optionally the
reference information.
[0058] Described herein is the representative value for the
electromagnetic radiation beam for each wavelength is compared to
stored values to verify or identify the drug sample.
[0059] Described herein is the liquid is water, there are six
electromagnetic radiation beams and the wavelengths are
substantially 1350 nm, 1450 nm, 1550, nm, 1650, nm, 1750 nm and
1850 nm, wherein 1450 nm is the anchor wavelength.
[0060] Described herein is the sample is in an intravenous delivery
device such as an IV infusions, set or syringe, or other receptacle
such as a test-cell, test-tube, flow cell or the like.
[0061] Preferably each laser comprises a photodetector, wherein the
photodetector detects electromagnetic radiation from the laser and
outputs the reference information.
[0062] In another aspect the present invention may be said to
consist in an analyser for identifying or verifying or otherwise
characterising a drug sample (or other substance) in a liquid
carrier comprising: an electromagnetic radiation source for
emitting electromagnetic radiation in at least one beam at a
sample, the electromagnetic radiation comprising at least two
different selected wavelengths, a sample detector that detects
affected electromagnetic radiation resulting from the emitted
electromagnetic radiation affected by the sample, and a processor
for identifying or verifying the sample from the detected affected
electromagnetic radiation, wherein each wavelength is selected to
be in the vicinity of the wavelength(s) of (or within a region
spanning) a spectral characteristic in the spectrum of the liquid
carrier, each wavelength falling within an analysis range suitable
for the liquid carrier.
[0063] In another aspect the present invention may be said to
consist in a method for identifying or verifying or otherwise
characterising a drug sample (or other substance) in a liquid
carrier comprising: emitting electromagnetic radiation in at least
one beam at a sample, the electromagnetic radiation comprising at
least two different selected wavelengths, detecting affected
electromagnetic radiation resulting from the emitted
electromagnetic radiation affected by the sample, and identifying
or verifying the sample from the detected affected electromagnetic
radiation, wherein each wavelength is selected to be in the
vicinity of the wavelength(s) of (or within a region spanning) a
spectral characteristic in the spectrum of the liquid carrier, each
wavelength falling within an analysis range suitable for the liquid
carrier.
[0064] Described herein is an analyser for identifying or verifying
or otherwise characterising a liquid based drug sample (or other
substance) comprising: an electromagnetic radiation source for
emitting electromagnetic radiation in at least one beam at a
sample, the electromagnetic radiation comprising at least two
different wavelengths, a sample detector that detects affected
electromagnetic radiation resulting from the emitted
electromagnetic radiation affected by the sample, and a processor
for identifying or verifying the sample from the detected affected
electromagnetic radiation, wherein each wavelength is falls in an
analysis range that provides improved identification/verification
for drugs in the liquid carrier, and each wavelength is in the
vicinity of the wavelength(s) of (or within a region spanning) a
spectral characteristic in the liquid spectrum in the analysis
range.
[0065] Described herein is a method for identifying or verifying or
otherwise characterising a liquid based drug sample (or other
substance) comprising: emitting electromagnetic radiation in at
least one beam at a sample, the electromagnetic radiation
comprising at least two different wavelengths, detecting affected
electromagnetic radiation resulting from the emitted
electromagnetic radiation affected by the sample, and identifying
or verifying the sample from the detected affected electromagnetic
radiation, wherein each wavelength is falls in an analysis range
that provides improved identification/verification for drugs in the
liquid carrier, and each wavelength is in the vicinity of the
wavelength(s) of (or within a region spanning) a spectral
characteristic in the liquid spectrum in the analysis range.
[0066] In another aspect the present invention an analyser for
identifying or verifying or otherwise characterising a liquid based
drug sample comprising: an electromagnetic radiation source for
emitting modulated electromagnetic radiation in at least one beam
at a sample, the electromagnetic radiation comprising at least two
different wavelengths, a sample detector that detects affected
modulated electromagnetic radiation resulting from the emitted
electromagnetic radiation affected by the sample and provides
output representing the detected affected modulated radiation, and
a processor for identifying or verifying the sample from the output
representing detected affected modulated electromagnetic radiation
including removing dark current from the output, wherein each
wavelength or at least two of the wavelengths is between
substantially 1300 nm and 2000 nm.
[0067] In another aspect the present invention a method for
identifying or verifying or otherwise characterising a liquid based
drug sample comprising: emitting modulated electromagnetic
radiation in at least one beam at a sample, the electromagnetic
radiation comprising at least two different wavelengths, detecting
affected modulated electromagnetic radiation resulting from the
emitted electromagnetic radiation affected by the sample and
providing output representing the detected affected radiation, and
identifying or verifying the sample from the output representing
detected affected modulated electromagnetic radiation including
removing dart current from the output, wherein each wavelength or
at least two of the wavelengths is between substantially 1300 nm
and 2000 nm.
[0068] Described herein is an analyser for identifying or verifying
or otherwise characterising a liquid based drug sample comprising:
an electromagnetic radiation source for emitting electromagnetic
radiation in at least one beam at a sample, the electromagnetic
radiation comprising at least two different wavelengths and for
measuring the power of the emitted electromagnetic radiation, a
sample detector that detects affected electromagnetic radiation
resulting from the emitted electromagnetic radiation affected by
the sample and provides output representing the detected affected
radiation, and a processor for identifying or verifying the sample
from the detector output representing the detected affected
electromagnetic radiation including using the measured power of the
emitted electromagnetic radiation, wherein each wavelength or at
least two of the wavelengths is between substantially 1300 nm and
2000 nm, and each wavelength or at least two of the wavelengths is
in the vicinity of the wavelength(s) of (or within a region
spanning) a spectral characteristic in the liquid spectrum between
substantially 1300 nm and 2000 nm.
[0069] Described herein is a method for identifying or verifying or
otherwise characterising a liquid based drug sample comprising:
emitting electromagnetic radiation in at least one beam at a
sample, the electromagnetic radiation comprising at least two
different wavelengths and measuring the power of the emitted
electromagnetic radiation, detecting affected electromagnetic
radiation resulting from the emitted electromagnetic radiation
affected by the sample and providing output representing the
detected affected radiation, and identifying or verifying the
sample from the output representing detected affected
electromagnetic radiation including using the measured power of the
emitted electromagnetic radiation, wherein each wavelength or at
least two of the wavelengths is between substantially 1300 nm and
2000 nm.
[0070] Described herein is a analyser for identifying or verifying
or otherwise characterising a sample comprising: an electromagnetic
radiation source for emitting electromagnetic radiation in at least
one beam at a sample, the electromagnetic radiation comprising at
least two different wavelengths, a sample detector that detects
affected electromagnetic radiation resulting from the emitted
electromagnetic radiation affected by the sample, and a processor
for identifying or verifying the sample from the detected affected
electromagnetic radiation, wherein each wavelength or at least two
of the wavelengths is between substantially 1300 nm and 2000
nm.
[0071] Preferably the source is a plurality of lasers in a single
package, each laser configured to emit an electromagnetic radiation
beam at a fixed or tuneable wavelength.
[0072] It is intended that reference to a range of numbers
disclosed herein (for example, 1 to 10) also incorporates reference
to all rational numbers within that range (for example, 1, 1.1, 2,
3, 3.9, 4, 5, 6, 6.5, 7, 8, 9 and 10) and also any range of
rational numbers within that range (for example, 2 to 8, 1.5 to 5.5
and 3.1 to 4.7). The term "comprising" as used in this
specification means "consisting at least in part of". Related terms
such as "comprise" and "comprised" are to be interpreted in the
same manner.
[0073] This invention may also be said broadly to consist in the
parts, elements and features referred to or indicated in the
specification of the application, individually or collectively, and
any or all combinations of any two or more of said parts, elements
or features, and where specific integers are mentioned herein which
have known equivalents in the art to which this invention relates,
such known equivalents are deemed to be incorporated herein as if
individually set forth.
BRIEF DESCRIPTION OF THE DRAWINGS
[0074] Preferred embodiments of the invention will be described
with reference to the following drawings, of which:
[0075] FIG. 1 shows in schematic form a spectroscopic analyser
according to the present invention,
[0076] FIG. 2 shows in schematic form the hypothetical spectrum of
a hypothetical liquid base/carrier,
[0077] FIG. 3 is a graph showing the error vs. number of
wavelengths used in the spectroscopic analyser,
[0078] FIG. 4 is a flow diagram showing operation of the
spectroscopic analyser,
[0079] FIG. 5 shows the spectrum of a drug (gelofusine succinated
gelatine solution 4%) overlaid the spectrum of a liquid based,
being water,
[0080] FIG. 6 shows spectral characteristics of water between 1300
and 2000 nm,
[0081] FIG. 7 shows a schematic diagram of a first embodiment of
the spectroscopic analyser in which the sources are lasers on a
rotating carousel,
[0082] FIG. 8 shows a method of processing the output from the
detectors, including a pre-processing and a
verification/identification stage,
[0083] FIG. 9 shows a method of processing the output from the
detectors, including a pre-processing and comparison data
generation stage,
[0084] FIG. 10 shows a best fit line through data points obtained
from outputs from the sample and reference detectors,
[0085] FIG. 11 shows a separation line between pre-processed data
points for a training sample and a comparison sample,
[0086] FIG. 12 shows a second embodiment in which the source
comprises six lasers that are directed along the sample path 14a
using a diffraction grating,
[0087] FIG. 13 shows a third embodiment comprising a source of six
lasers the outputs of which are directed along a sample path using
beam splitters,
[0088] FIG. 14 shows in schematic form a fourth embodiment for the
source comprising six lasers the outputs of which are converged
onto a sample path using a prism,
[0089] FIG. 15 shows a matrix indicating verification for a set of
sample drugs,
[0090] FIG. 16 shows an analyser using source modulation to
eliminate a reference channel,
[0091] FIG. 17 shows laser output power where the source is
modulated,
[0092] FIG. 18 shows a schematic with a modulator,
[0093] FIG. 19 shows a flow diagram for extracting dark current
[0094] FIG. 20 shows in schematic form a fifth embodiment for the
source comprising six lasers the outputs of which are converged
onto a sample path using a planar lightwave circuit,
[0095] FIG. 21 shows in schematic form a sixth embodiment for the
source comprising a single package source and collimated lens.
DETAILED DESCRIPTION
Overview
[0096] FIG. 1 shows an overview of a spectroscopic analyser 10 (for
example, a spectrophotometer) according to the present invention
for verifying or identifying (that is, analyse/characterise) drugs
or other samples (e.g. blood, biological samples etc.). The term
"drug" should be interpreted broadly to cover any pharmaceutical or
other medicament or substance for treating patients, which is
clinician controlled 9 (e.g. through a hospital, prescription or
pharmacy) or freely available. The analyser (apparatus) 10
comprises a controller 12 that controls both physical control and
processing aspects of operation. The analyser 10 comprises an
electromagnetic radiation source 11 for generating and emitting
electromagnetic radiation 22 with/at a plurality of wavelengths
within a wavelength range. The source might also have a
photodetector 4 or similar for control purposes. The
electromagnetic radiation could take the form of a plurality of
electromagnetic radiation beams at different wavelengths, or a
single electromagnetic radiation beam comprising a plurality of
wavelength components.
[0097] The term "wavelength" used for electromagnetic radiation
output refers to a particular wavelength, such as 1300 nm. As will
be appreciated, in practice, a source will not provide
electromagnetic radiation output with a pure single wavelength--the
output could contain components either side of the centre
wavelength/peak. In this case, the term "wavelength" refers to the
centre wavelength/peak of the electromagnetic radiation output,
where the radiation output might also have a wavelength components
either side of the centre wavelength, e.g. +/-30 nm, or +/-12 nm or
even just a few nm (e.g. 2 nm for lasers) either side. Each such
wavelength could be termed a "discrete" wavelength, as for
practical purposes it is discrete, even if other components
exist.
[0098] The electromagnetic radiation beams 22 could be visible
light beams emitted from one or more lasers, for example. In one
example, the electromagnetic radiation source ("source") 11 could
be a single device that can be configured to generate and emit a
plurality of electromagnetic radiation beams with different
wavelengths in sequence or simultaneously, or that emits a single
electromagnetic radiation beam with multiple wavelength components.
In another example, the source 11 could be a set of individual
sources, each configured to generate and emit electromagnetic
radiation beams 22 with a desired wavelength. The term "source" can
refer to a single source or multiple sources making up a source. In
each case, the source 11 might generate a fixed wavelength
electromagnetic radiation beam(s), or it might be tuneable to emit
an electromagnetic radiation beam(s) at one of a range of
wavelengths. Other examples could be envisaged by those skilled in
the art also.
[0099] Preferably, the source 11 is configured so that each
electromagnetic radiation beam 22 with a corresponding
wavelength(s) can be independently emitted in sequence. This might
be achieved through using a single source that is tuned to emit
electromagnetic radiation beams that sweep through a range of
wavelengths. Alternatively, where a source comprises multiple
electromagnetic radiation sources, each of which can be operated in
turn, it might be achieved by each source becoming the "active"
source. So that the electromagnetic radiation beam of the active
source is directed along the desired sample path 14a, each
electromagnetic radiation beam output from the source can be
arranged to hit a grating, mirror, prism or other optical apparatus
13 that redirects the beam from that source along the desired
sample path 14a. In such arrangement, each electromagnetic
radiation beam can be directed in sequence along the desired path
as it is generated/activated. Alternatively, multiple
electromagnetic radiation beams could be simultaneously directed
along a beam path 14a, resulting in a single beam of
electromagnetic radiation comprising a plurality of wavelength
components. Alternatively, the sources could be arranged on a
carousel or linear carriage (also represented by 13) that can be
mechanically controlled to physically position each source to emit
a radiation beam along the path 14a. These alternatives will be
described further later. Other arrangements for redirecting a
plurality of electromagnetic radiation beams from a source 11 along
a desired path 14a could also be envisaged. The electromagnetic
radiation beam directed along the path 14a can be termed the sample
electromagnetic radiation beam.
[0100] The apparatus 10 comprises a sample/sample retainer 16 for
holding a sample in the path 14a of the sample electromagnetic
radiation beam. The sample retainer 16 could be a
test-tube/test-tube holder, other type of test cell, part of an
infusion pump/IV set, flow-cell, or any other type of device for
holding any of these or holding a sample/substance in any manner.
The sample could alternatively simply be placed in the path 14a.
Any sample retainer allows for transmission of the electromagnetic
radiation 22 to and through the sample. The sample is preferably a
liquid based drug. The liquid based sample could, for example be a
water based drug, but it could also be another type of
sample/substance in water or other liquid carrier. The term
"sample" is used generally to indicate a substance for analysis
(e.g. verification/identification) and is not necessarily
restricted to a test sample/small portion of a larger amount of
substance. For example, the sample could be an actual drug to be
administered--not simply a (sample) portion of that drug to be
administered. The apparatus 10 can be used in a clinical or other
environment to verify/identify a drug prior to admission. In this
case, the sample put in the apparatus 10 will be the actual drug
being administered.
[0101] An electromagnetic radiation beam emitted along the path 14a
provides incident electromagnetic radiation on a sample (substance)
16 placed in the path (e.g. in the sample retainer.) Any incident
electromagnetic radiation beam 14a that reaches the sample 16 is
affected by the sample (e.g. either by transmission through and/or
reflection by the sample.) The affected (sample) electromagnetic
radiation 14b that exits the sample 16 is affected electromagnetic
radiation and contains spectral information regarding the sample.
For example, the affected electromagnetic radiation 14b comprises
information about the intensity of the affected electromagnetic
radiation at one wavelength of the incident radiation.
[0102] A sample detector 17 is placed in the affected
electromagnetic radiation path 14b such that affected
electromagnetic radiation 14b exiting the sample can be detected.
The detector 17 can comprise, for example, one or more
photodetectors. The detector 17 outputs information 14c in the form
of data/a signal that represents or indicates spectral information
of the sample 16--that is, the output represents the detected
affected electromagnetic radiation. The detector 17 output is
passed through to a processor 18 that carries out optionally a
pre-processing and a verification/identification algorithm in order
to verify or identify or otherwise analyse the sample in the
retainer. The processor 18 can form part of the controller 12, or
can be separate thereto. The processor 18 comprises or has access
to a database 23 with reference/comparison data for verifying or
identifying or otherwise analysing the sample. The path 14a, 14b,
emitted and affected radiation and/or the sample/sample holder 16
can be termed the "sample channel." The sample detector 16 and
inputs to the processor 18 (and optionally the processor itself)
can also form part of the sample channel.
[0103] Optionally there might also be a reference channel, in which
the emitted electromagnetic radiation beam 14a incident on the
sample 16 is split 21 or otherwise redirected along a reference
path 15a towards another retainer 19 containing a reference
sample/substance (or simply "reference") 19. A beam splitter 21
could be used to achieve this. The reference could be saline, for
example. The reference sample retainer 19 could be any one of those
retainers 16 mentioned with respect to the sample channel. The
reference electromagnetic radiation beam along the reference path
15a is incident on and affected by the reference sample 19 to
produce affected (reference) electromagnetic radiation 15b which is
incident on and detected by a reference detector 20. The reference
detector 20 could be the same or different detector to that of the
sample channel. In FIG. 1, the reference detector 20 is shown as an
independent detector by way of example.
[0104] The reference detector 20 outputs information 15c in the
form of data/a signal that represents or indicates spectral
information 15c of the reference--that is, the output represents
the detected affected electromagnetic radiation. The detector
output 15c is passed through to the processor 18 that carries out
pre-processing and a verification/identification algorithm in order
to verify or identify the sample 16 in the retainer. The detector
output 15c from the reference channel provides data from which to
normalise and/or correct the sample channel data 14c. The reference
channel might also comprises a neutral density filter prior to the
sample. This attenuates the incident electromagnetic radiation in a
manner to normalise the detected affected electromagnetic
radiation, or otherwise modify it so that the output of the
detector is at a suitable level to enable processing/comparison
with the output of the detector on the sample channel.
[0105] Each electromagnetic radiation beam 22 has a wavelength (or
has a plurality of wavelength components) that falls in the
analysis range ("analysis region"), preferably of 1300-2000
nanometres (nm). This region can nominally be termed "near
infrared" or "NIR". This region provides useful spectral
information for verifying or identifying drugs. The wavelength of
each electromagnetic radiation beam 22 (or the wavelengths making
up an electromagnetic beam) is selected based on spectral
characteristics(features) of the base liquid of the drug sample
that fall within the analysis range. Such characteristics could be,
for example, peaks, troughs, points of inflection, stable point or
regions, plateaus, knees and/or slopes of that base liquid
spectrum. Each wavelength selected is in the vicinity of (or within
a region spanning) such a spectral characteristic. The position of
a spectral characteristic could be defined by a nominal wavelength
(of for example the centre wavelength of the characteristic) or a
range of wavelengths defining a region spanning the
characteristic.
[0106] Selection of each wavelength can be demonstrated with
reference to the spectrum of a hypothetical base liquid as shown in
FIG. 2. The hypothetical spectrum comprises the following spectral
characteristics A-E in the analysis range. [0107] A peak between
1300 nm and 1400 nm (centre wavelength of 1350 nm of actual peak)
(A). [0108] A trough between 1400 nm and 1500 nm (centre wavelength
of 1450 nm of actual trough) (B). [0109] An inflection between 1500
nm and 1600 nm (centre wavelength of 1550 of actual inflection)
(C). [0110] A slope between 1600 nm and 1800 nm (D). [0111] A
plateau between 1800 nm and 2000 nm (E). [0112] A knee is also
shown around 1800 nm between characteristics D and E.
[0113] For analysis of drugs with this hypothetical liquid as a
base, wavelengths could be chosen that are within the vicinity of
the wavelength ranges (or centre wavelength) for one or more of the
spectral features A-E above, or that fall within in a region
spanning (defining/delimiting) the wavelength ranges for one or
more of the spectral features A-E above. A wavelength in the
"vicinity" of a spectral characteristic also can mean a wavelength
at the spectral characteristic centre wavelength. For example,
three different wavelengths could be chosen as follows. [0114]
Wavelength #1 1310 nm--within the region 1300-1400 nm for feature
A. [0115] Wavelength #2 1450 nm, roughly at or within the vicinity
of the centre wavelength of feature B. [0116] Wavelength #3 1800
nm, at the edge/knee (i.e. within the region) of feature E.
[0117] The chosen discrete wavelengths that relate to spectral
characteristics of the liquid spectrum can be termed "selected
wavelengths" or "chosen wavelengths". In general terms, the
selected or chosen wavelengths "correspond" to or "capture" a
spectral characteristic.
[0118] It will be appreciated that FIG. 2 shows just some
hypothetical examples of spectral characteristics (features)--many
more are possible for a spectrum. Further, the wavelength ranges
for spectral characteristics could overlap or even coincide.
Further, a separate wavelength need not be chosen for each spectral
characteristic in the analysis range--just a selection of
wavelengths relating to a selection of spectral characteristics
might be chosen. It might not be possible to define a spectral
characteristic by a wavelength range, or any such range might vary
depending on interpretation. A wavelength in the vicinity of a
spectral characteristic might instead be chosen. This could be a
wavelength that is near or within a certain tolerance (e.g. +/-30
nm) of the centre point wavelength of a spectral characteristic,
for example.
[0119] In addition, the selected wavelength might be influenced by
sources 11 that are readily obtainable or configurable to a
wavelength that is in the vicinity of or falls within in a region
spanning such a spectral characteristic. The selection of suitable
wavelengths for the emitted radiation will provide better
information for accurate verification or identification by the
processor.
[0120] In addition, preferably, the selected wavelengths can be
selected independently from the drug(s) being tested.
[0121] Any suitable number of wavelengths can be used. Optionally,
although not essentially, the number of different wavelengths
constituting the electromagnetic radiation (either in one or
multiple beams 22) provided by the source 11 is at least log.sub.2
n, where n is the number of samples that are tested for. The more
wavelengths that are used, the better the accuracy, but this is
optimised against costs and convenience. As seen in FIG. 3, as the
number of electromagnetic radiation beams/wavelengths increases,
the error of detection decreases. A selection of two wavelengths
provides an error of 0.14 for a set of 30 drugs, whereas five
wavelengths provide an error of just 0.02.
[0122] One of the electromagnetic radiation wavelengths 22 can be
selected to have a wavelength at an anchor point, which can be used
to eliminate the need for a reference channel. The anchor point is
chosen to have a wavelength in a stable or other suitable portion
of the spectrum of the underlying base liquid. The anchor
wavelength is described further later.
[0123] Upon receiving output from a sample detector 17 and
optionally a reference detector 20, the processor 18 executes an
algorithm that accesses a database 23 comprising comparison data,
and uses that output to verify or identify the sample 16 based on
the affected electromagnetic radiation 14b detected from the sample
16, and optionally where a reference channel is used, the detected
affected radiation 15b from that reference sample using the
comparison data. The processor 18 can operate with or independently
from the controller 12. Processing will be described further
later.
[0124] A user interface 24 allows a user to operate the apparatus
10, including setting parameters, inputting anticipated drugs and
receiving the results of analysis (via a screen, display, audio
alarm, indicator or similar). The results might indicate whether
the drug is as anticipated (verification/confirmation), or might
advise of the drug (identification).
[0125] Preferably, the apparatus 10 also comprises a feedback
system to stabilise the temperature of the electromagnetic
radiation source 11 and/or the detectors(s) 17, 20. In one example,
thermistors detect the temperature of the electromagnetic radiation
source and/or detector(s). Peltier cooling devices can be operated
to cool and stabilise the temperate of the source 11 and detectors
17, 20. The output of the thermistor(s) is sent to the controller
12, which controls the peltier cooling devices to cool the source
and/or detectors. Preferably the thermistor is the built-in
photodetector thermistor 5a, 5b. And the peltier thermo-electric
cooler is built-in to the photodetector 5a, 5b.
[0126] The apparatus 10 works generally as follows, with reference
to the flow diagram in FIG. 4. The controller 12 is used to operate
the source 11 to emit one or more electromagnetic radiation beams
22 (preferably individually and in sequence) with/at the selected
wavelengths towards the sample 16, step 40. The electromagnetic
radiation incident 14a on a sample 16 is transmitted or reflected
through the sample and becomes affected electromagnetic radiation
14b which is detected by the detector 17, step 41. Optionally, the
emitted radiation maybe diverted by a beam splitter 21 also to a
reference sample 19, which is detected by the same or a different
detector 20, step 42. The outputs 14c, 15c from the sample detector
17 and optionally the reference detector 20 are passed to the
processor 18, step 42. Here pre-processing takes place to normalise
and/or correct the detector output 14c, 15c, step 42. Then the
identification/verification algorithm is executed, step 43, which
includes querying the database 23 of reference drugs, the
information from which being utilised to identify or verify the
sample from the normalised detector output. The result of the
verification or identification of the sample is communicated by the
user interface 24, step 44.
[0127] Other options will become apparent as a more detailed
description of the invention is provided.
First Embodiment
[0128] One possible embodiment of the invention will now be
described in detail by way of example. This should not be
considered limiting but illustrative. The embodiment is described
in relation to an apparatus for providing verification or
identification of water based drugs from e.g. a set of 30
drugs.
[0129] Six wavelengths of electromagnetic radiation are chosen for
this example, six being greater than log.sub.2 n of 30. The
wavelengths are chosen in the analysis range and are based on the
spectral characteristics of water, being the base liquid, falling
in that range. The spectrum of a water based drug (or other liquid
based drug or aqueous solution) will be heavily dominated by the
base liquid spectrum. For example referring to FIG. 5, the spectrum
(dotted line) of drug W (gelofusine succinated gelatine solution
4%) is very similar to the spectrum of water (solid line). This is
because the spectrum of water dominates. However, the differences
in transmission coefficient between different water based drugs can
be measured. Focussing on areas/wavelengths of spectral
characteristics of the water spectrum, by using electromagnetic
radiation beams at those wavelengths, the difference between the
water spectrum and the water based drug spectrum at those
wavelengths can be utilised to provide drug discrimination for drug
identification or verification.
[0130] FIG. 6 shows a spectrum of water with some possible spectral
characteristics (features) in the analysis range identified, and
explained further below. [0131] Spectral characteristic A
(slope)--in a first region between 1300 nm and 1400 nm. [0132]
Spectral characteristic B (plateau/trough)--in a second region
between 1400 nm and 1500 nm. [0133] Spectral characteristic C
(slope)--in a third region between 1500 nm and 1600 nm. [0134]
Spectral characteristic D (peak)--in a fourth region between 1600
nm and 1700 nm. [0135] Spectral characteristic E (inflection)--in a
fifth region between 1700 nm and 1800 nm. [0136] Spectral
characteristic F (knee) a sixth region between 1800 nm and 2000 nm.
This is not an exhaustive list of possible spectral features.
[0137] The selection of a wavelength for an electromagnetic
radiation beam is not strictly fixed, and not necessarily solely
based on spectral characteristics of the base liquid. It is
influenced by the wavelength of spectral characteristics in
spectrum of the base water of the drug sample, but in addition the
selected wavelength can be based on other factors also. For
example, in interest of cost effectiveness and a regularly
obtainable supply chain, it might be preferable to use or select an
alternative wavelength that is close to the spectral characteristic
but not quite the same, if that alternative wavelength is easily
obtainable by an off-the-shelf laser or other optical
component.
[0138] For example, it is possible to use 1310 and 1550 nm as
selected wavelengths for water based drugs as there are many
devices configured for these wavelengths as they have wide spread
use within the communications industry. Laser diodes nominally have
centred wavelengths at 1650 nanometres, 1750 nanometres and 1850
nanometres, although these can be varied by up to plus or minus 30
nanometres. So wavelengths in these ranges can also be selected.
Therefore by looking at the availability of these components, and
the spectral characteristics of the base liquid, suitable
wavelengths for the emitted radiation can be determined.
[0139] Therefore, based on the above explanation, each of the six
wavelengths can be chosen to be within the vicinity or within the
region spanning one of each of the spectral features, but also
influenced by the availability of hardware. The six wavelengths for
water could therefore be (by way of example): 1350 nanometres
corresponding to feature A, 1450 nanometres corresponding to
feature B, 1550 nanometres corresponding to feature C, 1650
nanometres corresponding to feature D, 1750 nanometres
corresponding to feature E and 1850 nanometres corresponding to
feature F, all which fall within the 1300-2000 nanometres. As can
be seen the 1350 nm to 1850 nm wavelength selections do not match
exactly to peaks and troughs and other spectral characteristics in
the water spectrum, although are close. The selections also relate
to operating wavelengths of available hardware. These are of course
nominal wavelengths and the actual wavelength might vary in
practice due to source 11 characteristics.
[0140] FIG. 7 shows in schematic form one possible form of the
apparatus 10 as generally described in FIG. 1. The spectroscopic
analyser 10 has a controller 12 and a carousel 50 that supports six
lasers 51a-51f, which together form the source 11 to output
electromagnetic radiation 22 at a plurality of wavelengths in the
form of light. Each laser is tuned or tuneable to emit
electromagnetic radiation 22 at one of the six wavelengths defined
above. Each laser can comprise or be formed from laser diodes
providing a stable, high intensity, narrow band collimated
electromagnetic radiation output that is readily controlled
electronically via driver circuitry. Each laser comprises a lens
that can collimate the emitted electromagnetic radiation 14a into a
beam using appropriate lenses. Each laser 51a-51f can have one or
more photodiodes 4a-4f for detecting output electromagnetic
radiation for feedback control of that radiation. Lasers have fewer
heat emission problems than other sources, thus reducing the
detrimental effects of heat on the measurements. The output power
of each laser preferably is nominally the same (typically 30 mW) in
the interests of having a balanced apparatus. Preferably, this also
enables a common diode driver circuit to be used for the laser
diodes.
[0141] The controller 12 can control the carousel 50 to rotate
about an axis to activate any one of the lasers 51a-51f in turn and
align the activated laser (e.g. 51f as shown) to emit a beam 22
along the sample path/beam path 14a. The lasers 51a-51f can also be
turned off completely to facilitate the measurement of dark current
signals if required. The use of mechanically activated optical
chopper can thereby be eliminated (although one can be included if
desired.) Once activated, the laser emits electromagnetic radiation
22 towards the sample along the path 14a. The path 14a from the
source to the detector is preferably predominantly via free-space
preferably with minimal if any optical fibre components. This
reduces optical attenuation and hardware. The apparatus also
comprises a sample retainer 16a, which is aligned with the beam
path 14a. The emitted electromagnetic radiation from an active
laser 51a-51f is incident on and transmits or reflects through the
sample 16 in the sample retainer.
[0142] The detector 16 is placed in the affected radiation path 14b
that exits the sample 16a. Preferably the detector 16 is a single
photodetector/photodiode biased to have a suitable response to
detect electromagnetic radiation of wavelengths that will be in the
affected radiation. A single detector reduces the errors due to
variability introduced by components--it removes the relative
differences between multiple photodetectors enabling a more stable
response to the output of the emitted electromagnetic radiation
thus enhancing sensitivity. An InGaAs photodiode could be used, for
example. The detector 17 detects the affected radiation 14b and the
output 14c of the detector 17 is passed to a processor 18 that
verifies or identifies the sample as described above.
[0143] The apparatus also has a beam splitter 21 to redirect the
incident electromagnetic radiation beam 22/14a towards a reference
sample retainer along a reference path 15a, which passes through to
a reference detector 20. The output of the reference detector 20 is
also passed to the processor 18. The reference could be saline, for
example.
[0144] Preferably, the apparatus also comprises a feedback system
to stabilise the temperature of the electromagnetic radiation
source 11 and the detectors(s). In one example, thermistors detect
the temperature of the electromagnetic radiation source and/or
detector(s). Peltier cooling devices can be operated to cool and
stabilise the temperate of the source and detectors. The output of
the thermistor(s) is sent to the controller, which controls the
peltier cooling devices to cool the source and/or detectors.
Preferably the thermistor is the built-in photodetector thermistor
5a, 5b. And the peltier thermo-electric cooler is built-in to the
photodetector 5a, 5b.
[0145] Referring to FIG. 4, operation of the apparatus 10 will now
be described. The controller 12 operates the carousel 50 to rotate
each laser 51a-51f in turn to the activate position. When in the
activate position, the laser 51a-51f is operated by the controller
12 to emit an electromagnetic radiation beam at one of the selected
wavelengths to the sample 16 (and optionally to reference sample
19.) In this manner, six electromagnetic radiation beams with
different selected wavelengths are emitted, step 40, in sequence
from each of the six lasers 51a-51f, each tuned to a different
selected wavelength. Each laser 51a-51f in turn emits an
electromagnetic beam 22 along the path 14a towards the sample. The
affected radiation coming from the sample is detected, step 41, for
each electromagnetic radiation beam emitted 14a towards the sample
16. The electromagnetic radiation beam could be switched on and off
to get a reading/measurement made by the detector during the off
phase also--this can give a dark signal/current for reference
purposes. The emitted electromagnetic radiation is also directed
along the reference path 15a, through the reference sample 19 using
the beam splitter 21, and detected by the reference detector 20.
The outputs from the sample detector 17 and the reference detector
20 are passed to the processor 18, step 42. The processor
(optionally) carries out pre-processing on the output from the
detectors, and then verifies or identifies the drug based on the
pre-processed outputs, step 43. It outputs the results via the user
interface 24, step 44.
[0146] In one possible embodiment, the processor 18 comprises or
implements a pre-processing method and then a
verification/identification method as shown in FIG. 8. In this
embodiment a reference channel is used and also dark current
readings. Dark current is the output provided by the detectors 17,
20 when no electromagnetic radiation (e.g. light) is incident on
them. This dark current reading from the detector can be subtracted
from the actual reading from the detectors for calibration
purposes. Having a dark reading is not essential for the invention
and is described here as one possible option--the remaining
description of the processing method would work also without dark
readings being taken or by.
[0147] Prior to carrying out the verification or identification in
FIG. 8, a training process is carried out to produce a comparison
data from which samples can be verified/identified as shown in
FIGS. 9-11. In the training process, an algorithm is used to
generate the comparison data, which determines the particular
linear combination of data values from each of the sample data that
optimises the separation between different drugs. The resulting
mathematical rule is then applied to the data acquired for the drug
under test to verify that it is the intended drug. In the
embodiment described, dark current readings are used. The training
process preferably comprises a pre-processing stage, and a
comparison data generation stage. Pre-processing is not essential,
but improves performance.
[0148] Referring to FIG. 9, for the training process, a number of
training samples are tested in the analyser in turn. Each training
sample relates to a sample that will be test for during actual use
of the analyser. For each training sample, output from both sample
and reference channels is received at the processor, step 90. If
dark current is being used, the output from each detector for the
dark reading is subtracted from the output of the actual reading.
The output 14c received at the processor 18 from the sample
detector 17 indicates the intensity of the affected electromagnetic
radiation 14b for each emitted electromagnetic radiation beam at
the sample 16. It may, for example, comprise data which directly or
indirectly indicates photocurrent of the detector and/or intensity
of the detected electromagnetic radiation. Likewise, the output.
15c received at the processor 18 from the reference detector 20
indicates the intensity of the affected electromagnetic radiation
15b for each emitted electromagnetic radiation beam at the
reference sample. Preferably, the apparatus carries out multiple
measurements for each wavelength. For example, at each wavelength,
the apparatus detects affected electromagnetic radiation affected
by the sample at 15 different times and passes this output to the
processor, step 94. Similarly, at each wavelength, the apparatus
detects affected electromagnetic radiation affected by the
reference at 15 different times and passes this output to the
processor, step 94.
[0149] Next, for each wavelength, the processor 18 generates from
the output of the reference and sample detectors a range of sample
data points for the sample that correlate an intensity of affected
electromagnetic radiation 14b affected by the sample at a
particular selected wavelength, step 91. These data points 100
could be plotted, as shown for example in FIG. 10--although it will
be appreciated that the processor does not necessarily actually
plot the data. The x axis shows intensity indicative values
corresponding to detector output for the sample detector 17, and
the y axis shows intensity indicative values correlating to
detector output for the reference detector 20. The values indicate
directly or indirectly the intensity of detected affected
electromagnetic radiation. Where a reference channel is used,
output on the reference detector is paired with output from the
sample detector taken at the same time. Each sample/reference
channel detector output value pair is plotted on the graph. Such
measurements can be taken for several times for each wavelength.
Therefore, the plot in FIG. 10 shows the values indicative of
intensity 103 measured at several times (e.g. 15) for a particular
selected wavelength (e.g. nominally 1350 nm) of electromagnetic
radiation incident 14a on the training sample 16 and on the
reference 19.
[0150] For each training sample, the process is then repeated to
get similar data points for a second (comparison) sample 101 and a
control (e.g. saline) 102. The sample/reference channel detector
output value pairs for the second (comparison) 101 sample and
control sample 102 could also plotted on the graph, as shown in
FIG. 9, step 91.
[0151] A best fit straight line can then be calculated using a
suitable statistical technique, step 92, and the intercept value of
the x axis is found, step 92, for each of the: [0152] training
sample set, 103 [0153] second (comparison) sample 101, and the
[0154] control sample 102 set of data points for the particular
wavelength (1350 nm), as shown in FIG. 10.
[0155] From this a normalised pre-processed value is found. For
example, the x-axis intercept values (e.g. 842500 and 850500) for
the training sample 103 and control 102 respectively can be found,
and then can be subtracted from each other to obtain normalised
pre-processed values (e.g. 8000), step 93. Similarly, the x-axis
intercept values (e.g. 86000 and 850500) for the second
(comparison) sample 101 and control 102 respectively can be found
also, and then subtracted from each other to obtain normalised
pre-processed values (e.g. 95000), step 93. This process can be
carried out for each of the other selected wavelengths (e.g. five
others in this case), step 94 and steps 90-93, resulting in a set
of six normalised pre-processed values (--one for each wavelength)
for the training sample. The process can also be carried out for
each of the other selected wavelengths for the second (comparison)
sample, resulting in a set of six normalised pre-processed values
for the second (comparison) drug for each wavelength. These sets of
normalised pre-processed values for the training sample and second
(comparison) for each wavelength sample can be correlated/plotted
in a multidimensional space, each axis corresponding to a
wavelength and the pre-processed value for that wavelength being
plotted relative to that axis.
[0156] In practice, this process, steps 90-94, can then be carried
out numerous times for each wavelength, so that for each training
sample and second (comparison) sample, there are a plurality of
sets of six normalised pre-processed values. Each set can be
plotted/correlated as one point in a multidimensional (six
dimensions in this case) space. An example of such a plot is shown
in FIG. 11. Here, for simplicity, only a two dimensional space is
shown, each axis relating to the results from two wavelengths--in
reality it would need to be a six-dimensional graph to cover all
six wavelengths. For each set for each of the training sample and
second (comparison) sample, a pair of two normalised pre-processed
value (i.e. one value for each wavelength) is plotted as a single
point on the two dimensional graph, e.g. 110, resulting in a
normalised pre-processed value data set for the training sample 111
and the second (comparison) sample 112.
[0157] The pre-processing stage described above reduces the
detrimental effects of systematic errors in the system and drift in
the measured data. Note, the reference channel/value is optional.
In an alternative, x-axis intercept values are found for the sample
data only.
[0158] In an alternative embodiment, the pre-processing steps
previously described can be omitted on the grounds that system
drift and systematic errors can be virtually eliminated with the
use of highly stable laser diode sources and a reference signal
derived from the laser's own monitor diode output. This facilitates
the use of a single channel with a single photo-detector
eliminating the need for separate optical reference channel and/or
control sample to be used. To this end, the data base of measured
transmission spectra for a range of intravenous drugs can be built
up in a more straightforward manner by sequentially measuring
samples of each drug in a single channel using multiple test
tubes.
[0159] After the data has been pre-processed for the training
sample and second (comparison) sample and correlated as shown in
FIG. 11, a representative value can be obtained for the training
sample. If no pre-processing is carried out, the process proceeds
to finding the representative value on non-pre-processed (raw)
data. First a line 113 that separates the training sample data set
111 from the second (comparison) sample data set 112 is determined,
step 95. Then the normal direction of the line is used as a
weighting in a score to separate the training sample from the
comparison sample. Also, a threshold is determined below which the
training sample falls, step 96. The threshold and weighting score
provide a representative value for comparison data to assist in
verification/identification for that training sample. The
representative value is stored as comparison data in a database 23
for the training sample, step 98.
[0160] The entire process is the repeated (step 99, and steps
90-98) for the same training sample against a third (comparison)
sample to get a second representative value for storing as
comparison data in the database 23 for the training sample. Then
the process is repeated again (step 99, and steps 90-98) against a
fourth and subsequent comparison samples to generated a third and
subsequent representative values for storing as comparison data for
the training sample. Together these form the representative values
in the comparison database to identify/verify the training
sample.
[0161] The entire process (step 100, step 90-99) is the repeated
for each other training sample (in the set of n drugs) against
multiple comparison samples, in order to obtain representative
values for each additional training sample also.
[0162] It will be appreciated that in describing the training
process steps 90-100, there has been reference to graphs and
techniques. These are described for illustrative purposes. Any
processor carrying out the training process to determine
representative values might not actually produce such graphs or
utilise such techniques to obtain the end result, but rather use
other processing techniques that achieve the same result.
[0163] The above training process will generate comparison data for
each training sample (in the set of n drugs) that can stored in the
database 23 and can be used to identify or verify actual samples
from the set under test. The comparison database 23 can be
generated well in advance of actual sample testing, or can be
generated soon before or even on-the-fly. The comparison data can
be considered as a multidimensional verification/identification
matrix based on the acquired multidimensional spectral data from
the detectors. The comparison data can be used to verify or
identify any of the drugs from any of the other drugs in the set of
n drugs.
[0164] Referring back to FIG. 8, once a comparison database is
produced and stored in the database 23, verification/identification
of actual samples occurs as follows. Output from both sample and
reference channels is received at the processor, step 80. If dark
current is being used, the output from each detector for the dark
reading is subtracted from the output of the actual reading. The
output 14c received at the processor 18 from the sample detector 17
indicates the intensity of the affected electromagnetic radiation
14b for each emitted electromagnetic radiation beam at the sample
16. It may, for example, comprise data which directly or indirectly
indicates photocurrent of the detector and/or intensity of the
detected electromagnetic radiation. Likewise, the output 15c
received at the processor 18 from the reference detector 20
indicates the intensity of the affected electromagnetic radiation
15b for each emitted electromagnetic radiation beam at the
reference sample. Preferably, the apparatus carries out multiple
measurements for each wavelength. For example, at each wavelength,
the apparatus detects affected electromagnetic radiation affected
by the sample at 15 different times and passes this output to the
processor, step 80. Similarly, at each wavelength, the apparatus
detects affected electromagnetic radiation affected by the
reference at 15 different times and passes this output to the
processor, step 80.
[0165] This output is then preferably pre-processed, steps 81-84,
in the same manner as described above for the training process and
with reference to FIGS. 9 to 11. That description need not be
repeated here, but in summary, data points are generated, step 81,
best fit lines found, step 82, and x-axis values are obtained which
provide normalised pre-processed values, step 83. This is done for
all wavelengths, step 84. Pre-processing is not essential, but can
improve performance.
[0166] After this pre-processing is carried out for the affected
radiation of each wavelength, steps 81-84, the
identification/verification algorithm can then be invoked, step 85.
Verification involves confirming that a sample drug is the drug
that is expected. For example, a clinician can specify what they
think the drug is (e.g. from the set of n drugs) through the user
interface 24, e.g. step 80, then use the apparatus to confirm
whether the drug in the retainer is actually that drug which is
specified by the clinician. Identification involves determining
what a drug actually is, without any suggestion from the clinician
as to what the drug is. For verification/identification, the
spectral data (that is, the pre-processed values) are compared
against the comparison data in the database 23, step 85, to
identify the drug, or verify whether it is the anticipated drug as
specified by the clinician. Output is then provided to the user
interface, step 86.
[0167] In one possible identification/verification algorithm, once
the sample data is obtained and pre-processed, representative
values are found for the sample, in the same manner that they were
found during the training process as explained with reference to
FIGS. 9 to 11. The representative values are found for the sample
at each selected wavelength and with respect to each other
comparison sample. The representative values are compared to the
representative values in the comparison data. If there is
sufficient similarity between the representative values found for
the sample and the representative values in the comparison data
corresponding to the same sample, then verification or
identification is made. Sufficient similarity can be determined
using any suitable statistical or other technique. For example,
sufficient similarity might occur when some or all of the
representative values match those in the verification matrix. In
another example, this might occur when the sample falls below the
threshold for each comparison sample. An alarm or output might be
made via a user interface to advise the user of the result of the
verification/identification.
[0168] FIG. 15 shows test data for a set of 30 drugs verified using
the analyser. In the test, each drug was inserted in the analyser,
and then systematically the analyser was configured to check if it
was one of the 30 drugs. If an alarm was raised, this indicated the
drug was not the one that was anticipated, and the alarm noted.
Each drug was tested 15 times, in relation to each of the other
drugs. So, for example, Metaraminol was put into the analyser and
then the analyser was configured to check for Metaraminol. After 15
tests, the analyser did not once raise an alarm, indicating that
the analyser did not detect Metaraminol as another drug. Keeping
Metaraminol in the sample retainer, the analyser was then
configured to check for Heparin. For each of 15 independent tests,
the analyser raised an alarm, indicating it detected each time that
the drug in the analyser (Metaraminol) was not the drug it was
expecting (Heparin). The analyser was then reconfigured for each of
the other drugs, and the test done 15 times for each, while
Metaraminol was in the sample retainer. The same process was then
repeated for every other drug being used as a sample, with the
analyser systematically being re-configured to check for every
other drug. Each time an alarm was raised (indicating the analyser
did not consider the drug in the retainer was that being checked
form), the alarm was noted. The table in FIG. 15 reflects the
number of times an alarm was raised of each drug detection
combination. The error rates are shown. The low error rates
demonstrate a significant improvement in verification accuracy.
Second Embodiment
[0169] FIG. 12 shows an alternative embodiment of the apparatus 10.
In this embodiment rather than using a carousel 50, the six lasers
51a-51f forming the source 11 are arranged to emit their
electromagnetic radiation beam 22 towards a diffraction grating 120
of the reflection type. Each laser 51a-51f is operable to emit a
tuned or tuneable wavelength of a collimated electromagnetic beam
22 towards the diffraction grating. The angle of incidence X on the
grating surface for each laser 51a-51f is chosen that their first
order diffracted beam emerges at the same angle Y thereby producing
a common optical path 14a for each laser. The controller 12
activates each laser 51a-51f sequentially to emit a beam of a
single wavelength towards the sample. Alternatively, multiple
lasers 51a-51f could be operated at once such that an
electromagnetic beam 22 comprising multiple wavelength components
could be emitted towards the sample 16. A separate grating or beam
splitter 21 could be used for example as shown in FIG. 1 to direct
the beam towards a reference channel sample 19, if there is one.
All other aspects of the embodiment can be as shown and described
in FIGS. 1, 2, 16 and/or 18.
Third Embodiment
[0170] FIG. 13 shows another alternative embodiment of the
apparatus 10. In this embodiment rather than using a carousel 50,
the six lasers 51a-51f forming the source 11 are arranged to emit
their electromagnetic radiation beam 14a towards respective beam
splitters 130a-130f that redirect the emitted electromagnetic
radiation beam 22 along the sample path 14a. The controller 12 can
control each electromagnetic radiation source 11 in turn to emit a
tune or tuneable wavelength of electromagnetic radiation towards
the sample via the respective beam splitter 130a-130f.
Alternatively, two or more of the lasers 51a-51f could be activated
at once to provide an electromagnetic beam 22 with multiple
wavelength components towards 14a the sample 16. An absorber 135 is
provided behind the beam splitter array to mop up transmitted
energy from the beam splitters. A separate grating or beam splitter
21 could be used for example as shown in FIG. 1 to direct the beam
towards a reference channel sample 19, if there is one. All other
aspects of the embodiment can be as shown and described in FIGS. 1,
2, 16 and/or 18.
Fourth Embodiment
[0171] FIG. 14 shows an alternative embodiment of the apparatus 10.
In this embodiment rather than using a carousel 50, the six lasers
51a-51f forming the source 11 are arranged to emit their
electromagnetic radiation beam 22 towards a prism 140. Each laser
51a-51f is operable to emit a tuned or tuneable wavelength of a
collimated electromagnetic beam 14a towards the prism. The angle of
incidence X on the grating surface for each laser 51a-51f is chosen
that their first order refracted beam 22 emerges 14a at the same
angle Y thereby producing a common optical path 14a for each laser
51a-51f. The controller 12 activates each laser 51a-51f
sequentially to emit a beam of a single wavelength towards the
sample. Alternatively, multiple lasers 51a-51f could be operated at
once such that an electromagnetic beam 22 comprising multiple
wavelength components could be emitted towards 14a the sample 16. A
separate grating or beam splitter 21 could be used for example as
shown in FIG. 1 to direct the beam towards a reference channel
sample 19, if there is one. All other aspects of the embodiment can
be as shown and described in FIGS. 1, 2, 16 and/or 18.
Fifth Embodiment
[0172] FIG. 20 shows an alternative embodiment of the apparatus 10.
In this embodiment rather than using a carousel 50, the six lasers
51a-51f forming the source 11 are arranged to emit their
electromagnetic radiation beam 22 through separate fibre optic
cables 201a-201f towards a planar lightwave circuit (PLC) (fibre
optic combiner) 200. Each laser 51a-51f is operable to emit a tuned
or tuneable wavelength of a collimated electromagnetic beam 14a
towards the PLC 200 via the fibre optic cables 201a-201f. The
controller 12 activates each laser 51a-51f sequentially to emit a
beam of a single wavelength towards the sample. Alternatively,
multiple lasers 51a-51f could be operated at once such that an
electromagnetic beam 22 comprising multiple wavelength components
could be emitted towards 14a the sample 16. A separate grating or
beam splitter 21 could be used for example as shown in FIG. 1 to
direct the beam towards a reference channel sample 19, if there is
one. All other aspects of the embodiment can be as shown and
described in FIGS. 1, 2, 16 and/or 18.
Sixth Embodiment
[0173] FIG. 21 shows an alternative embodiment of the apparatus 10.
In this embodiment rather than using a carousel 50, a single
package 211 comprising 6 lasers forming the source 11 are arranged
to emit their electromagnetic radiation beam 201a-201f towards an
integrated collimating lens 210. The laser is operable to emit a
tuned or tuneable wavelength at each of 6 wavelengths towards the
lens 210. The controller 12 activates the laser to sequentially to
emit a beam 212a-212f of a single wavelength towards the sample.
Alternatively, multiple beams 51a-51f could be operated at once
such that an electromagnetic beam 22 comprising multiple wavelength
components could be emitted towards 14a the sample 16 via the lens
210. A separate grating or beam splitter 21 could be used for
example as shown in FIG. 1 to direct the beam towards a reference
channel sample 19, if there is one. All other aspects of the
embodiment can be as shown and described in FIGS. 1, 2, 16 and/or
18.
Alternative Embodiments
[0174] The nominal analysis range of 1300-2000 nm for selected
wavelengths is chosen as it provides advantages for improved drug
verification or identification. However, it will be appreciated
that the reference to 1300-2000 nm should not be considered
limiting, and wavelengths could be chosen that relate spectral
characteristics in slightly different ranges or other ranges
entirely. The selected wavelengths (and therefore the spectral
characteristics) fall within any analysis range provide for
improved identification/verification for drugs in the liquid
carrier. For example, the analysis range could be a subset of 1300
nm-2000 nm, such as 1300 nm-1900 nm; 1350 nm-1950 nm; 1400 nm-1900
nm; 1500 nm-1800 nm or some other subset. The range could also be
larger, such as 1250-2050 nm; 1200 nm-2100 nm; or 1150 nm-2150 nm
or the like. The analysis range might even be offset from the
nominal range, such as 1200 nm-1900 nm, or 1300 nm-1900 nm. These
are non-limiting examples. In general, the analysis range could
start, for example, anywhere from 1100 nm-1500 nm and end anywhere
from 1800 nm-2150 nm. Even that is non-limiting and the range could
be something different entirely that provides for improved
verification/identification. Further, wavelengths falling outside
these analysis ranges and corresponding to spectral features lying
outside these analysis ranges above could also be used in
combination with wavelengths falling in the analysis ranges
mentioned. Using a plurality of wavelengths corresponding to
spectral characteristics falling within the analysis range provides
improved performance. Preferably any and all wavelengths are
selected within the analysis range, but that does not preclude
using wavelengths falling in other ranges also where that might be
useful.
[0175] The range could be at least partially influenced by
component selection. For example, silicon photodiodes have a
response down to at least 1100 nm, so if used this wavelength might
be used as the bottom end of the range. Preferably, the invention
uses only one detector, so the range might be defined by what a
single detector can cover--for example 1300 nm-2000 nm in the case
of an InGaAs detector.
[0176] Other liquids to water might have other analysis ranges that
provide improved identification/verification.
[0177] In an embodiment described above, a dark current was used to
calibrate/normalise the output data from the detectors 17, 20. The
dark current is subtracted from the detector reading. In another
embodiment, obtaining dark current readings using a chopper wheel
(or turning off of the source 11) is not required. Rather, laser
driver current modulation is used to eliminate the need for dark
current readings. Referring to the simplified schematic of the
analyser in FIG. 16, the laser is driven by a driver
current/modulator 160. The driver current/modulator may form part
of the source or be separate to it. The source 11 is a laser diode
with built-in photodetector 4 (to provide control feedback). A
sample cell 16 and photodetector 17 are provided. The laser driver
current modulator 160 is also shown in FIG. 18 incorporated into
the more detailed block diagram of the overall analyser in FIG.
1.
[0178] The sample channel output current is the sum of two
components--a dark current term that is present even in the absence
of any illumination, and a term proportional to the intensity of
light incident on the detector. Therefore, we can write the sample
channel output current, I.sub.S as follows:
I.sub.S=I.sub.S.sup.Dark+SP (1)
where in (1): I.sub.S.sup.Dark is the dark current signal of the
sample channel detector S is a constant representing the
attenuation in the optical path including the sample cell. P is the
incident power illuminating the sample cell.
[0179] A similar expression can be written for the reference
channel output current, I.sub.R, generated from the built-in
photo-detector of the laser diode source, namely:
I.sub.R=I.sub.R.sup.Dark+RP (2)
where in (2): I.sub.R.sup.Dark is the dark current signal of the
reference photo-detector in the laser diode package. R is a
constant representing the fraction of incident power delivered to
the reference.
[0180] We now excite the laser source by modulating the driver
current with a known waveform. Typically, a sinusoidal modulation
with angular frequency co is used to vary the current about a mean
value. This has the effect of modulating the output power of the
laser diode source in a similar sinusoidal manner illustrated in
FIG. 17.
[0181] Mathematically, the time-dependent laser output power, P(t),
can be written as follows:
P(t)=P.sub.0+.DELTA.Psin(.omega.t+.PHI.) (3)
where in (3): P.sub.0 is the mean output power from the laser
.DELTA.P is the modulation amplitude in the output power waveform
(depth of modulation) .PHI. is the phase of the modulation waveform
at tine, t=0.
[0182] If we now substitute for the incident power in equations (1)
and (2) using (3), we obtain the following expressions for the
output currents from sample and reference channels:
I.sub.S=I.sub.S.sup.Dark+SP.sub.0+S.DELTA.Psin(.omega.t+.PHI.)
I.sub.R=I.sub.R.sup.Dark+RP.sub.0+R.DELTA.Psin(.omega.t+.PHI.)
[0183] The parameters of interest with respect to characterising
the sample under test are the constants S and R. The ratio of these
two constants represents a normalised coefficient characteristic of
the liquid in the sample cell.
[0184] Expanding the sinusoidal term in the above equations,
gives:
sin(.omega.t+.PHI.)=sin(.omega.t)cos .PHI.+cos(.omega.t)sin
.PHI.
which gives the following:
I S = I S Dark + S P 0 + S .DELTA. P sin ( .omega. t ) cos .phi. +
S .DELTA. P cos ( .omega. t ) sin .phi. .ident. A 0 S + A 1 S cos (
.omega. t ) + B 1 S sin ( .omega. t ) ( 4 ) I R = I R Dark + R P 0
+ R .DELTA. P sin ( .omega. t ) cos .phi. + R .DELTA. P cos (
.omega. t ) sin .phi. .ident. A 0 R + A 1 R cos ( .omega. t ) + B 1
R sin ( .omega. t ) ( 5 ) ##EQU00001##
So that: A.sub.OS=I.sub.S.sup.Dark+SP.sub.0
A.sub.0R=I.sub.R.sup.Dark+RP.sub.0
A.sub.1S=S.DELTA.Psin .PHI.
B.sub.1S=S.DELTA.Pcos .PHI.
A.sub.1R=R.DELTA.Psin .PHI.
B.sub.1R=R.DELTA.Pcos .PHI.
[0185] Inspection of equations (4) and (5) shows the output
currents have the form of a simple Fourier series consisting of
constant DC terms, A.sub.0S and A.sub.0R, plus sine and cosine
terms that oscillate with the modulation frequency, .omega., with
amplitudes A.sub.1S, A.sub.1R, B.sub.1S and B.sub.1R.
[0186] The dark current terms contribute only to the DC term of the
Fourier series in (4) and (5). The dark current terms are contained
within the DC components of equations (4) and (5). Therefore, a
simple Fourier analysis of the modulated output waveform gives the
Fourier coefficients of the sin(.omega.t) and cos(.omega.t)
terms--which are independent of the dark current.
[0187] By measuring the sinusoidally varying component of each
output current, the constants, S and R, can be determined without
the need to measure the dark current of each detector diode. These
latter terms can be eliminated from the measurement by DC blocking
components or by performing a Fourier analysis of the output
currents and discarding all but the sinusoidal terms.
[0188] In conventional spectrometer systems, the dark current would
be measured by blocking off the illumination to the detector diode
using a rotating mechanical chopper that periodically blocks then
re-instates the optical illumination. Using the laser-current
modulation described above eliminates the need for mechanical
components such as rotating choppers which simplifies the
spectrometer design, reduces cost and improves reliability by not
using any moving parts. Electrical interference from the electric
motors used to drive mechanical choppers is also eliminated.
[0189] The method Would work as follows with reference to FIG. 19
which is the same as the method shown in FIG. 4 with the additional
dark current method added. The output source electromagnetic
radiation would be modulated using the apparatus in FIG. 16/18 and
emitted towards the sample step 190. The affected detected
radiation would be received by the sample and reference detectors
17 and 20 (where used), step 191 and passed to the processor 18,
step 192 for processing. The received output can be processed by
the processor step 192 to remove the dark current (DC) component
A.sub.0S and A.sub.0R of the received output (as per equations (4),
(5) above) and any other unwanted components. The desired
components sin(.omega.t) and cos(.omega.t) are obtained and
represent the intensity measurement without dark current. This
processing can be done using any suitable signal processing know to
those in the art. The remaining steps 193 and 194 are as previously
described.
[0190] For example, in one possibility for extracting dark
currently step 192, Fourier analysis of the output currents could
be performed by multiplying the outputs by sin(.omega.t) and
cos(.omega.t) respectively, and integrating over a period of the
oscillation. This can be used where the modulation is a single
frequency, e.g. sine wave modulation at a single frequency. This
procedure provides a form of averaging which is beneficial in
reducing measurement noise.
[0191] Alternatively, a Fast Fourier Transform (FFT) algorithm can
be applied to a digitised output waveform and the relevant Fourier
components extracted. From the Fourier coefficients we therefore
obtain: S.DELTA.P= {square root over
(A.sub.1S.sup.2+B.sub.1S.sup.2)} for the sample channel and
R.DELTA.P= {square root over (A.sub.1R.sup.2+B.sub.1R.sup.2)} for
the reference channel.
[0192] Taking the ratio of these Fourier amplitudes eliminates the
dependence on the modulation depth .DELTA.P to give a normalised
output, N, given by:
N = S R ( 6 ) ##EQU00002##
Values of N are determined at each wavelength of interest and form
the output data set for the liquid under test.
[0193] Other methods for extracting the information could be known
and used by the skilled in the art.
[0194] In an alternative analysis process, a reference channel is
not used. Rather, the detector output 14c from affected
electromagnetic radiation (from the sample) acquired at an anchor
wavelength is used, rather than the detector output 15c from
affected electromagnetic radiation from the reference in the
reference channel. All other detector output 14c from affected
electromagnetic radiation received relating to other wavelengths is
normalised/corrected using the detector output of affected
electromagnetic radiation at the anchor wavelength. The anchor
wavelength can be one of the wavelengths already selected, although
preferably will be selected to be in the vicinity or within a
region spanning a suitable spectral feature/point in the base
liquid spectrum. For example, the anchor wavelength could be in the
vicinity of or fall within a region spanning a stable region of the
base liquid spectrum. Elimination of the reference channel/detector
output removes variation between the sample and reference channels
that can mask sample differences, thus removal creates a more
sensitive and stable apparatus. The output at the anchor wavelength
can be used to normalise, calibrate or otherwise adjust the output
for the other wavelengths. The output from the anchor wavelength
could be processed in the same manner as the output from the
reference channel as describe previously in order to verify/analyse
the sample. That is, the anchor output can become the reference
information.
[0195] In one possibility, where water is the base liquid, 1450
nanometres is chosen as the anchor point as there is particular
stability in the spectrum of water around this wavelength. This
wavelength corresponds to the maximum optical absorption aqueous
solutions due to the presence of OH bonds. It is a common
transmission medium for sample drugs tested. Data acquired at this
wavelength shows minimum thermal sensitivity and is therefore
provides a highly stable and predictable reference. This is just
one example for water based drug, and is indicative only and should
not be considered limiting as to the wavelengths and anchor points
that might be chosen based on other considerations.
[0196] Each of the previous embodiments describe the optional use
of a reference channel to obtain reference measurements for use in
processing data. In an alternative, the reference channel is not
used. Rather, a photodiode 4 (see FIG. 20) in the laser diode 11
(which is used for power monitoring and control of the laser diode)
can be utilised to obtain reference information. Laser diodes are
often fitted with built-in photo-detector diodes 4 that are used to
monitor the output power of the laser. This is done to stabilise
the laser by allowing the laser driver current to be controlled via
a feedback circuit incorporating the integrated photo-diode
signal.
[0197] This alternative for obtaining reference information can be
substituted in place of the reference channel for any of the
embodiments described. The reference measurements obtained using
the alternative can be utilised in the same manner as described any
previous embodiment.
[0198] The output of the laser diode photodetector 4 which detects
the output power of the source electromagnetic radiation is passed
to the processor 18 and used instead of reference readings obtained
by the reference detector 20 to normalise and/or correct the output
from the detector 17 in the sample channel. This output signal from
the photodetector 4 performs the same function as a reference
channel that would otherwise have been produced more conventionally
by using a beam splitter arrangement involving two separate
measurement channels. Using the photo-diode output from the laser
as a reference signal thereby eliminates the need for
beam-splitting optics and an additional reference sample and
detector.
[0199] In an alternative embodiment, the electromagnetic source 11
is a broadband source with multiple filters 13 at different
wavelengths that can be arranged in between the broadband source
and the sample. The output from each filter provides an
electromagnetic beam 22 with one of the selected wavelengths. The
broadband source could be, for example, a broadband filament
blackbody source and filters. The source 11 could alternatively
take the form of one or more LEDs with or without filters. Any of
the alternative sources could be mounted on a carousel 50 and
operated as described for the first embodiment, or operated in
conjunction with an optical device such as described in embodiments
two to four.
[0200] Any of the sources could be temperature stabilised with a
feedback system, for example by using thermistors and peltier
cooling devices as previously described.
[0201] The detectors could be in the form of one or more InGaAs
photodiodes or other light sensors.
[0202] A separate photodiode or similar or other detector could be
used for each of the reference and sample channels. Alternatively,
a single photodiode or similar or other detector could be used for
both the sample and reference channels, utilising optical devices
to merge the affected radiation beams of both channels, or
otherwise direct them to the detector.
[0203] Random errors in measurements can be reduced by averaging
detector readings over many measurements (e.g. 500). Dark
measurements (source off) can be used to correct measured data.
[0204] For dark current readings, a chopper wheel can optionally be
used that blacks out/blocks the electromagnetic radiation 22
incident on the sample 16 and the reference 20. The chopper could
form part of the optical device 13. For each electromagnetic
reading, the detector 17/20 also takes a "dark" reading when the
chopper blocks the electromagnetic radiation 22. Having a chopper
wheel and dark reading is not essential for the invention and is
described here as one possible option.
[0205] Over the band 1300 nm to 2000 nm, it is also possible to use
a single type of photo-diode detector based on indium gallium
arsenide (InGaAs) technology which further simplifies the detector
system.
[0206] The present invention preferably uses wavelengths in the
analysis region of 1300 nm to 2000 nm or variations thereof. This
region has previously been ignored for drug analysis due to the
perceived disadvantage of broad spectral peaks and troughs that
appear in the absorbance spectrum. Infra-red (IR) spectroscopy
previously has exploited the numerous narrow-band spectral
absorption characteristics that exist for wavelengths longer than
2000 nm. This so-called `finger-print` region exhibits spectral
lines that are characteristic of certain chemical bonds present in
the material under test and offers a highly sensitive technique to
identifying the material. The present inventors have determined
that the 1300 nm-2000 nm analysis range (or portions thereof)
provides an advantage for drug verification or identification or
other analysis. Further, the inventors have established that the
spectral location of salient spectral features in this analysis
region is less affected by temperature variations. The numerous
narrow spectral bands that appear in the region above 2000 nm
exhibit large temperature sensitivity. If this region above 2000 nm
is used for verification or identification, the analysis apparatus
requires very precise wavelength resolution. This resolution can
only be achieved using high-cost sophisticated spectrometers
[0207] More particularly, this type of IR spectroscopic measurement
(above 2000 nm) requires very fine wavelength resolution (typically
a few nanometres) maintained over a wide spectral band in order to
resolve the numerous individual spectral features. The fine
wavelength resolution is especially required to account for any
shift in the narrow spectral lines with respect to temperature
variations.
[0208] The measurement of such highly resolved spectral lines
requires the use of a spectrometer fitted with a sophisticated
monochromator based either on a mechanically rotated diffraction
grating and single detector, or a fixed grating with a linear array
of detector elements. Both options are found in existing
spectrometers and both are expensive to implement.
[0209] As a cost-effective alternative, aimed for example at
water-based intravenous drug verification/identification or other
analysis, it has been determined by the present inventors that it
is advantageous to make measurements within the shorter wavelength
region between 1300 nm and 2000 nm. Whilst the spectral
characteristics/features in this, wavelength region are much fewer
in number and much broader spectrally (differing little from those
of water), the inventors have found that there remain sufficient
spectral differences between drugs (or other liquid based samples)
to facilitate verification/identification. The have also found,
that, in the 1300 nm to 2000 nm region, the wavelengths at which
the peaks and troughs (and other spectral characteristics) of each
drug's IR transmission spectrum occur remain highly stable with
respect to temperature for all water-based drugs (or other
samples).
[0210] Importantly, due to the absence of temperature-sensitive
narrow spectral absorption features, they have established there is
no requirement for highly resolved spectral lines to be measured
thereby eliminating the need for an expensive monochromator. A
small number of measurements (5, or 6 typically) made at discrete
wavelengths over the range 1300 nm to 2000 nm is sufficient to
characterise each drug (or other sample). Typically, each
measurement is made over a bandwidth of 12 nm (as determined by a
band-pass filter, illuminated by a broad-band source, for example)
or over a few nanometres for laser-based illumination.
* * * * *