Positron emission tomography (PET) offers the study of biochemical,
physiological, and pharmacological functions at a cellular and molecular level.
The performance of a PET study mostly depends on the used radiotracer of
interest. However, the development of a novel PET tracer is very difficult, as
it is required to fulfill a lot of important criteria. PET radiotracers usually
encounter different chemical modifications including redox reaction, hydrolysis,
decarboxylation, and various conjugation processes within living organisms. Due
to this biotransformation, different chemical entities are produced, and the
amount of the parent radiotracer is declined. Consequently, the signal measured
by the PET scanner indicates the entire amount of radioactivity deposited in the
tissue; however, it does not offer any indication about the chemical disposition
of the parent radiotracer itself. From a radiopharmaceutical perspective, it is
necessary to quantify the parent radiotracer’s fraction present in the tissue.
Hence, the identification of radiometabolites of the radiotracers is vital for
PET imaging. There are mainly two reasons for the chemical identification of PET
radiometabolites: firstly, to determine the amount of parent radiotracers in
plasma, and secondly, to rule out (if a radiometabolite enters the brain) or
correct any radiometabolite accumulation in peripheral tissue. Besides,
radiometabolite formations of the tracer might be of concern for the PET study,
as the radiometabolic products may display considerably contrasting distribution
patterns inside the body when compared with the radiotracer itself. Therefore,
necessary information is needed about these biochemical transformations to
understand the distribution of radioactivity throughout the body. Various
published review articles on PET radiometabolites mainly focus on the sample
preparation techniques and recently available technology to improve the
radiometabolite analysis process. This article essentially summarizes the
chemical and structural identity of the radiometabolites of various radiotracers
including [11C]PBB3,
[11C]flumazenil,
[18F]FEPE2I, [11C]PBR28,
[11C]MADAM, and
(+)[18F]flubatine. Besides, the importance of
radiometabolite analysis in PET imaging is also briefly summarized. Moreover,
this review also highlights how a slight chemical modification could reduce the
formation of radiometabolites, which could interfere with the results of PET
imaging.
Graphical abstract
×
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Ultra high-performance liquid
chromatography/quadrupole-time of flight-mass spectrometry
Background
Positron emission tomography (PET) is one of the most rapidly
progressing imaging modalities, which offers understanding about the biochemical,
physiological, and pharmacological functions at a molecular and cellular level
[1, 2]. To date, PET has been applied in several areas including
cardiology, neurology, and oncology particularly in tumor targeting and diagnosis
[3, 4]. Numerous PET radiotracers have been studied and developed for
imaging cancerous lesions, brain receptors, transporters, and enzyme systems, but
only a few of them are currently in use as imaging agents in clinical practice. The
PET imaging technique includes the acquirement of physiological images that
constitute the distribution of radioactivity associated with positron-emitting
radionuclides in the volume of examination [5]. Compared to other imaging tools like the X-ray, magnetic
resonance imaging (MRI), and computed tomography (CT) which offer structural
information, PET imaging is advantageous as it shows numerous functional and
biochemical characteristics of organs and tissues of interest. PET combines several
crucial features like absolute quantitation, allows repetitive and longitudinal
examination before/after interventions with the help of short-lived PET
radionuclides. Very high resolution (< 2.5 mm) can be achieved at any part of the
body with a dedicated PET scanner [6,
7]. Most importantly, procedures
developed in preclinical research can be applied to clinical studies. The PET
imaging technique is currently the only non-invasive imaging tool to measure in vivo
tissue pharmacokinetics quantitatively.
The process involved in developing new PET radiopharmaceuticals begins
with compound selection, through in vitro and in vivo efficacy evaluation,
ultimately leading to clinical investigation. Hence, the performance of a PET study
mostly depends on the used radiotracer of interest. However, developing PET imaging
tracers is difficult as various critical criteria need to be fulfilled such as
optimum molecular weight and lipophilicity. Besides, the radiotracer should have a
high affinity for the target receptor, and it should show a fast washout after
reaching the saturation binding. For imaging the central nervous system (CNS), the
radiotracer should not be a subject for P-glycoprotein (P-gp) [8‐10]. On the other hand, the non-brain tissue
radiotracer development process also faces some serious challenges as low peripheral
radiometabolism is necessary to compensate for the lack of BBB. In the case of the
CNS radiotracer development, most of the compounds failed to show promising results
in preclinical and clinical studies. Some of the most common causes for the failure
of radiotracers appear when non-displaceable binding surpasses target binding, i.e.,
when signals from the background exceed the signals coming from the target. One of
the serious problems with PET is that it offers information about the total
radioactivity deposited in the tissue of interest but does not reflect any evidence
of its chemical identity. The existence of radiometabolites in the tissue of
interest would affect how precise the quantitative analysis of the PET examination
is [11, 12].
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In living organisms, PET radiotracers usually encounter different types
of chemical modifications including oxidation, reduction, hydrolysis,
decarboxylation, and various conjugation processes. Due to these biotransformations,
diverse chemical entities are generated while the concentration of the original
radiotracer decreases [13‐18]. Therefore, the signal measured by the PET scanner replicates
the entire amount of radioactivity deposited in the tissue of choice, but it does
not offer any indication about the chemical identity of the pharmacophore itself.
From a radiopharmaceutical perspective, the quantification of only the parent
radiotracer fraction present in tissues is a requirement [19]. Almost all the PET radiotracers are
metabolized within the body. Among these metabolized products, some may carry the
radioactivity tag. There are some reactions that are planned, such as the
phosphorylation of [18F]FDG and its resulting trapping
into the cell. However, the PET radiotracers are mostly metabolized to form unwanted
radiometabolites which create serious problems in quantification. Although
radiometabolites present in plasma can be rectified, the radiometabolites deposited
into tissues should be considered during image analysis. Radiotracers for brain
imaging are designed in such a way that they do not produce any radiometabolites
that can pass through the blood–brain barrier [20]. However, there are some exemptions to this guideline, as in
the case of [18F]FDOPA. In the preclinical evaluation of
a new PET radiotracer, it is important to take into consideration that the
radiometabolites may display a significant difference in distribution patterns and
activity in the body in comparison to the parent radiotracer. Enough information on
biochemical transformations is crucial to have a more detailed knowledge of
radioactive distribution in the whole body. For example, substantial inter-tissue
variances in the further radiometabolism of FDG, i.e., away from FDG-6-phosphate,
have been demonstrated ex vivo in different rat organs [21]. Moreover, a relative tissue-dependent
distribution of individual radiometabolites replicating the physiological features
of the respective organs has also been established [21]. Therefore, by understanding the occurrence and biochemical
nature of different radiometabolic compounds, it is possible to gain extensive
insight into the pathological and physiological processes by PET. To calculate
physiological parameters such as receptor density and metabolic rates, it is
necessary to know the concentration of the tracer and its radiometabolites in the
blood and tissues over time. Hence, it is vital to establish methods by which
radiometabolites, especially those having the potential to cross the BBB, can be
identified and measured over time. Identification of radiometabolites during the
evolution of a new radiotracer is also important as it offers information about the
most suitable position to radiolabel a compound to escape any production of
inquisitive radiometabolites [22,
23]. There are some reviews already
published on PET radiometabolites [24,
25]. However, those reviews mainly
focus on the sample preparation techniques and recently available technology to
improve the radiometabolite analysis process. Our review mainly summarizes the
chemical and structural identities of radiometabolites of different radiotracers.
Moreover, this review also highlights how a slight chemical modification could
reduce the formation of radiometabolites, which could interfere with the results of
PET imaging.
Importance of PET radiometabolite analysis
Radiometabolite adjusted arterial input function is crucial for the
exact quantification of the PET radiotracers that do not possess any appropriate
reference region in the brain. There are two main reasons for the chemical
identification of radiometabolites: firstly, to determine the amount of parent
radiotracers in plasma, and secondly, to rule out or correct any radiometabolite
accumulation in peripheral tissue. Radiometabolite formations of the tracer might be
a concern for the PET study, as radiometabolic products may display considerably
contrasting administration patterns into the body, as compared to the tracer itself.
An understanding of radiometabolite formation and its chemical nature may provide
important information on physiological, biochemical, and pathological processes by
PET. To fulfill this requirement, data analysis models were established to evaluate
the correlation between the acquired data and the biophysical factors influencing
radiotracer accumulation and biotransformation [26, 27]. Moreover,
radiotracer metabolism can significantly influence the arterial input function,
which is a factor applied for analyzing PET images quantitatively. Radiometabolite
examinations in the plasma are a crucial requirement for the precise assessment and
revelation of PET imaging and the determination of pathological changes in metabolic
pathways [28]. After estimating the
radioisotopic decay and restructuring it into an image, the exact biodistribution of
the compound is accessible. Hence, radiometabolite analysis is an extremely
important topic in PET imaging. In some cases, it was noticed that a radiometabolite
can show a better affinity for the target than its parent radiotracer. For example,
[11C]Loperamide and its putative radiometabolite
[N-methyl-11C]N-desmethyl-loperamide both behave as the avid substrate for P-gp
[29, 30]. Actually, [N-methyl-11C]N-desmethyl-loperamide could be superior to
[11C]Loperamide in determining P-gp function at the
blood–brain barrier because further demethylation of [N-methyl-11C]N-desmethyl-loperamide will generate a more polar radiometabolites
that have negligible access into the brain [31]. There are some instances where the parent radiotracer and
its radiometabolites both have the affinity for the same targets. In this case, the
cold compound of the radiotracer can be injected for checking their competition for
the target. For example, both [18F]LBT-999 and its
radiometabolite (2β-carbomethoxy-3b-(4′-tolyl) nortropane) have the binding affinity
for dopamine transporter (DAT) [32]. In
a PET experiment, Saba et al. have shown that after intravenous injection of cold
metabolite, it induced a strong displacement of
[18F]LBT-999 in the striata, suggesting that the
radiometabolite can cross the BBB and competing with the radiotracer
[18F]LBT-999 for the target [33].
Radiotracer metabolism
Most of the drug/tracer metabolism takes place in the liver. However,
it may also take place in the kidney or intestine. Usually, metabolism occurs to
transform the radiotracer into a compound that is more water-soluble and easily
excreted. Similar to the drug, the radiotracer metabolism also takes place in two
phases. In phase I, the radiotracers are chemically changed by enzymes through
oxidation, reduction, and hydrolysis. Hence, in phase I, a new functional group is
generated which can be used in the next phase. In phase II, some hydrophilic moiety
is attached to that functional group to form readily water-soluble conjugates that
can be easily excreted through urine [34, 35]. Table
1 summarizes the different processes,
substrates, and products of phase I and phase II.
Table 1
Phase I and phase II metabolism of the
radiotracer
Phase I metabolism
Phase II metabolism
Process
Substrate
Product
Process
Substrate
Product
Oxidation
Aromatic compounds
Aliphatic compounds
Aromatic ethers
Aromatic amine
Tertiary Amine
Hydroxylated compound
Alcohol, aldehyde, ketones, acids
Phenols and Aliphatic aldehydes
Hydroxyamino compound
N-Oxide
Glucuronidation
Alcohol or phenol derivatives of the radiotracers
and glucuronic acid
Conjugated Ester
Reduction
Aldehydes, ketones
Carbon–carbon double bond
Nitro group
Alcohols
Corresponding saturated compounds
Corresponding amine
Sulphonation
Alcohol and phenol derivatives of the radiotracers
and its metabolites
Conjugated product
Hydrolysis
Ester, amide
Acid
Acetylation
Aliphatic or aromatic amine
Amides
Methods of radiometabolite analysis
Several chromatographic techniques including thin-layer chromatography
(TLC) [36], high-performance liquid
chromatography (HPLC) [37], micellar
chromatography [38], and overpressure
thin-layer chromatography (OPTLC) [39]
were commonly used for the examination of radiometabolites. Among these techniques,
TLC was the earliest known chromatographic tool applied in radiochemistry to
separate radioactive compounds. To date, TLC is an important technique and is
regularly used in radiopharmacy departments, to determine the radiochemical purity
of radiopharmaceuticals. This technique is very easy to apply, fast, inexpensive,
and most importantly it can detect all deposited radioactivity without losing any
information [40]. However, TLC,
generally a qualitative technique, suffers from several limitations including
resolution, accuracy, and reproducibility [41]. Therefore, TLC is not a suitable tool for radiometabolite
analysis. In comparison to TLC, the OPTLC comes with superior resolution and rapid
analysis. Until recently, the most widely used technique for the analysis of
radiometabolites of a radiotracer is the HPLC, combined with radioactivity
detectors. HPLC analysis is reproducible, and it allows to quantify narrow, rider,
and shoulder peaks precisely which is not possible for TLC. A multistep sample
extraction process is required before it could be injected into the HPLC system
[42]. However, due to the
reasonably lengthy preparation procedure in combination with the very short
half-lives of the radiotracers, loss of information may occur particularly at the
later stages of the PET imaging experiments. Additionally, multi-stage blood
extraction may lead to a decrease or alteration of information. This may induce bias
and hamper the repeatability of the analysis. To get rid of this time-consuming
sample preparation technique, solid phase extraction (SPE) of the radiometabolite
can serve as a suitable choice. In SPE, first, the plasma sample is loaded into an
SPE cartridge directly or after the precipitation of protein. Then the radiotracer
and its metabolites are extracted from SPE depending on their polarity. Although
direct blood sampling could largely reduce the sample preparation time, it is still
a challenging issue in radiometabolite analysis. Another important and well-known
approach for radiometabolite analysis is column-switching HPLC. Here, the plasma
sample is directly loaded into a capture column which is a kind of short SPE
cartridge. Following this, the radiotracer and its metabolites are eluted into a
reverse-phase column of a radio-HPLC [43‐45]. This semi-automated method effectively reduces
time-consuming sample preparation steps and exposure to the radioactivity with
better reproducibility. However, this method suffers from high back pressure as it
is required a large plasma volume for radiometabolite analysis. Nakao et al. have
developed an alternative rapid and efficient method based on micellar liquid
chromatography for the direct analysis of plasma radiometabolites [24, 38, 46]. This method
uses micellar/high submicellar liquid chromatography along with semi-preparative
alkyl-bonded silica column for the analysis of radiometabolites. The steep gradient
and high flow rate are used for the rapid removal of the macromolecule from plasma.
Compared to the particle-based column, the monolithic column provides high
resolution and better sensitivity. The main advantage of this approach is that it
reduces time-consuming sample preparation steps. Besides, it also allows the
analysis of a large number of samples with appropriate sensitivity. Currently,
protein precipitation and SPE of radiometabolites are the two most encouraging
sample preparation procedures designed for radioactive metabolite analysis. Table
2 summarizes the various advantages and
limitations of different analytical techniques applied to radiometabolite analysis.
Table 2
Advantages and limitations of different analytical
techniques applied to radiometabolite analysis
Analytical techniques
Sensitivity
Resolution
Measurement speed
Required pre-treatment
Cost
Radio-TLC
High
Low
Slow
Yes
Low
OPTLC
High
Moderate
Fast
Yes
Moderate
Radio-HPLC
High
High
Fast
Yes
High
Column-switching HPLC
High
High
Fast
No
High
SPE
Moderate
Low
Fast
Usually no
Low
Micellar chromatography
High
Low
Fast
No
Low
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Sample preparation
The most commonly used biological samples for the radiometabolite
analysis are blood, plasma, and tissue. The direct analysis of these samples has
several limitations. Hence, most of the time, it is essential to separate the
radiotracer and its metabolites from the biological matrix.
It is well known that the ease of sample analysis increases with
the degree of fluidity. Hence, all the tissue samples are usually required to go
through some mechanical procedures before the sample is analyzed [19]. There are some common techniques used
for the disruption of tissue samples including “motor and pastel” technique,
blades technique, and sonication techniques. One of the disadvantages of these
procedures is that during this procedure the radiotracers or its metabolites may
change the chemical structure. Sometimes these samples produce emulsion, and
because of it, subsequent sample analysis may be difficult.
Protein elimination
The biological samples or disrupted tissue samples usually have a
large amount of protein. Sometimes these proteins bind very strongly to the
radiotracers or its radiometabolites. To examine the radiometabolites, it is
required to separate the radiotracers and its radiometabolites from the protein
[25]. Besides, multistep manual
extraction of blood samples is necessary to remove the biological matrix before
injection of the sample into the HPLC system, and in this way, the risk of HPLC
column blockage can also be minimized. Hence, the blood sample is required to be
centrifuged. The plasma attained from this is then mixed with an organic solvent
such as acetonitrile to precipitate plasma proteins. This mixture is then
centrifuged again to collect the organic fraction as the supernatant
[42]. The collected
supernatant, which contains the desired compound is then injected into the HPLC
instrument. The protein precipitation techniques from the blood sample can be
described by the schematic diagram shown in Fig. 1.
×
Importance of plasma protein binding analysis
One of the most important aspects of PET study is to find out the
amount of free fraction of an injected radiotracer in plasma. After the injection of
the radiotracer into the body, a fraction of it binds to the plasma protein. The
remaining fraction (free radiotracer) is then making an equilibrium with its plasma
protein bounded fraction [42]. It is
worth mentioning that only the free fraction of the radiotracer is available to bind
the target of interest and the efficacy of a drug depends on the free fraction
present in plasma [47]. When the two
drugs were administrated into the body at the same time, it is particularly
important to know their plasma protein binding affinity as one drug can replace a
proportion of other drugs from being bound to the plasma protein, enabling a greater
proportion of free drug fraction. The methods to measure the amount of plasma
protein binding and the free fraction of radiotracer were discussed in detail by
Moein et al [25].
Case studies
Radiometabolite analysis of [11C]PBB3
In 2015, Kazunori Kawamura et al. revealed the structure of the key
radiometabolites of [11C]PBB3 by high-performance
liquid chromatography-mass spectrometry (HPLC-MS) and suggested that its
possible metabolic route is through in vitro, in vivo, and in silico
investigations [48]. PBBs, a family
of pyridyl and phenyl-butadienyl-benzothiazoles compounds, were initially
examined by Makoto Higuchi et al. for the applications of prospective imaging
radiotracers of tau deposition in the brain [49, 50].
[11C]PBB3 appeared as the most promising
candidate among all the PBB compounds. It has a large affinity for tau protein
aggregates with a Kd value of 2.55 nM and the selectivity of PBB3 for tau is
around 50 times higher in comparison to Aβ deposits [49]. In another study, the group also
revealed that [11C] PBB3 readily degraded to form a
polar radiometabolite [49,
51] and thus potentially
impeding a simplified PET image analysis. An identical radiometabolite was also
obtained from the mouse brain after the administration of
[11C]PBB3 as the PET radiotracer.
In vivo radiometabolite examination demonstrates that the fraction
of parent [11C]PBB3 is around 30%, 5 min after the
administration of [11C]PBB3 (carrier-added) in mouse
plasma was relatively larger than the results obtained (1.9%) after
administration of [11C]PBB3 alone [51]. The results ascertained that extra
amounts of carrier PBB3 reduce the metabolic rate of
[11C]PBB3. Analytical radio-HPLC offers two peaks
corresponding to the two radiometabolites and parent
[11C]PBB3 peaks in the in vivo metabolite
examination of [11C]PBB3 (carrier-added) mouse
plasma. A small radioactive metabolite peak ([11C]M1)
at 0.6 min was assumed to have formed due to the demethylation of the
radiotracer in the presence of cytochrome P450 enzymes (CYPs) (Fig. 2) [48]. The mass of the main metabolite
([11C]M2) which appears at 1.6 min was obtained
as 390 [M+H+] from LC–MS (Fig. 3b)
[48]. Hence, the main
metabolite with m/z 390 was non-identical from the one formed in the phase I
radiometabolism facilitated by CYPs [52, 53]. The in
vitro radiometabolite examination of [11C]PBB3 by
incubating with a mouse as well as a human liver S9 fraction followed by the
evaluation of this result with the in vivo radiometabolite analysis of mouse
plasma shows that the main radioactivity peak was equivalent to
[11C]M2 with m/z 390, produced due to the
sulfate conjugation of [11C]PBB3 facilitated by a
sulfotransferase enzyme. The incubation of [11C]PBB3
with mouse liver microsomes (MLM) and human liver microsomes (HLM) having a CYP
activator confirms that the minor radiometabolite is
[11C]M1, which was produced by the CYP
facilitated demethylation.
×
×
Only a small variation between mouse and human samples were
detected for the radiometabolism of [11C]PBB3 (in
vitro) by cytochrome P450 and sulfotransferase enzymes. Therefore,
[11C]PBB3 metabolism in mice may offer a
substantial understanding of the pharmacokinetic behavior of the radiotracer
with PET imaging in humans. These results have established that the radiotracer
[11C]PBB3 mostly metabolized to produce
[11C]M2 a sulfate conjugation reaction
facilitated by sulfotransferases enzymes and a negligible radiometabolite,
[11C]M1, was produced due to oxidation being
interposed by the CYPs (Fig. 2). Hence,
it is extremely important to determine the metabolic pathway and radiometabolite
structure for assessing the clinical usage of
[11C]PBB3. Besides, the information also could be
used in designing new PBB analogs which are more efficient and biostable than
the parent compound.
Radiometabolite analysis of
[11C]flumazenil
In 2013, Amini et al. presented a strategy to find out radioactive
metabolites in monkey plasma after the injection of
[11C] flumazenil, a PET radiotracer—for GABAA
receptor [54]. Utilizing this
procedure, radiometabolites formed in vivo could be acknowledged and studied by
the support of fast radio-LC, ultra high-performance liquid
chromatography/quadrupole-time of flight-mass spectrometry (UHPLC/Q-ToF-MS), and
hepatic microsomes. According to this strategy, the radiometabolites were first
formed in vitro by liver microsomes as radiotracers are mostly metabolized in
the liver. All the radiometabolite peaks were successively separated and
collected independently by fast radio-LC and identified by UHPLC/Q-ToF-mass
spectrometry. The in vivo metabolic profiles are then related to and recognized
by the help of the in vitro results. When the in vitro radiometabolism of
[11C]flumazenil was analyzed by fast radio-LC, it
offered three peaks corresponding to [11C]flumazenil
and its two radiometabolites, -[11C]flumazenil-M1 and
[11C]flumazenil-M2. Mass spectrometry analysis
offers monoisotopic masses of [11C]flumazenil, its
radiometabolites, and their fragmented ions. In mass spectrometry, the
flumazenil fragmentation pattern gives an acylium ion peak corresponding to
m/z
258.0691. This result is compared to the one reported previously [55]. The two radiometabolites of flumazenil
were identified—one is a hydroxyl-ethyl ester (flumazenil-M1) and the other one
is an acid (flumazenil-M2). These results demonstrate that the identical
fragmentation of flumazenil occurs due to radiometabolism. To identify the in
vivo metabolism of [11C]flumazenil, after
administration of the radiotracer, samples from the rhesus monkey plasma were
collected at intervals and examined by fast radio-LC (Fig. 4) [54]. When the metabolic stability of
[11C] flumazenil in vitro (no carrier-added) as
well as in vivo was examined, the radiotracer metabolism rate was found to be
faster in in vivo than in in vitro. Nevertheless, both in vitro and in vivo
experiments produce an equal number of radiometabolites and in both cases,
[11C]flumazenil-M2 appears to be the major
radiometabolite. A similar metabolic profile was reported in primates and human
plasma [56‐59]. There
were no metabolites detected in the absence of any microsomes in in vitro. These
results demonstrate the microsome dependency of radiometabolite formation of
[11C]flumazenil. The most important metabolite of
[11C]flumazenil is an acid, and it does not
penetrate the blood–brain barrier in normal human subjects [60]. Besides, it has negligible in vitro
human benzodiazepine receptors binding affinity. Hence, the radioactive
metabolite could only marginally impact the estimation of free ligand
concentration in the brain and the interpretation of the PET data.
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Radiometabolite analysis of [11C]PBR28
[11C]PBR28, a PET radiotracer for
an18-kDa translocator protein is widely used in brain imaging [61]. Carrier-added solutions of
[11C]PBR28 were incubated with human liver
microsomes to find out its phase I radiometabolism [54]. The metabolism reaction was paused at
different intervals and the progress of radiometabolite formation was examined
using fast radio-LC. The radiotracer peak and the produced radiometabolite peaks
were isolated and recognized by mass spectrometry. The mass spectrometry data
suggested that the PBR28-M1 was produced by two-step biotransformation of PBR28.
Initially, N-debenzylation of PBR28 following the oxidation of
[11C]2-methoxybenzaldehyde produces
[11C]2-methoxybenzoicacid (PBR28-M1). The identity of the radiometabolite was
additionally established by matching its retention time with the reference
standard of PBR28-M1. PBR28-M1 was also documented earlier in vivo rats’ studies
[61]. The in vivo metabolite
identification was demonstrated by comparing the retention times of its in vitro
metabolite peaks. In the case of the in vivo radiometabolism study, after the
injection of [11C]PBR28 in a human, the plasma
samples were acquired at multiple time intervals and examined with standard
radio-LC and fast radio-LC (Fig. 5)
[54]. The examination of the
metabolic stability of the [11C]PBR28 radiotracers
confirmed that they are metabolized faster in in vitro than in in vivo.
Interestingly enough, four additional radiometabolite peaks were observed when
[11C]PBR28 was incubated with the human liver
microsome. However, these peaks are missing in human plasma. Although the above
strategy can be successfully applied to identify the chemical form of several
radiometabolites, it is quite difficult to foresee the comparative quantity of
radiometabolites formed in in vivo with the help of the in vitro route.
×
Radiometabolite analysis of
[18F]FEPE2I
[18F]FEPE2I which targets the DAT is a
PET radiotracer used in neuroimaging [62]. Phase I radiometabolites of the PET radiotracer
[18F]FE-PE2I was investigated by the incubation
of carrier-added solutions of the radiotracer with microsomes from a monkey
liver. Five major radiometabolites were identified due to the different kinds of
in vitro enzymatic biotransformations, including N-dealkylation and benzylic
hydroxylation followed by additional oxidation of benzyl alcohol, the primary
metabolite. The study also demonstrates the in vivo radiometabolism by analyzing
the plasma samples from a rhesus monkey at different time points after the
administration of [18F]FE-PE2I by using conventional
radio-LC and fast radio-LC. Seven different radiometabolite peaks were separated
with the help of a fast radio-LC and among them, five were recognized. However,
only two radiometabolite peaks were witnessed by the conventional radio-HPLC as
reported elsewhere [63,
64]. When examining the
metabolic stability of [18F]FE-PE2I, it was observed
that the rate of radiometabolism is faster in the case of in vitro than in vivo.
Although equal numbers of radioactive metabolites were identified both in in
vitro as well as in in vivo analysis, the major radiometabolite amount
significantly varies between the two studies. In the case of in vivo, the major
radiometabolite was demonstrated as [18F]FE-PE2I-M2
(Fig. 6) [54], whereas the combined peak of
[18F]FE-PE2I-M4 and
[18F]FE-PE2I-M5 is appeared to be the predominant
fraction in in vitro analysis. Similar kinds of variations between in vivo and
in vitro radiometabolites formed are also observed in other studies
[65, 66].
×
Radiometabolite of [11C]MADAM
Diphenyl sulfide derivatives have proven to be potential PET/SPECT
radiotracers for serotonin transporter (SERT) study in vivo and are thus
extremely crucial to examine their radioactive metabolism [67, 68]. Christer et al. had explored the metabolic portfolio of
[11C]MADAM, a widely used diphenyl sulfide-based
radiotracer for PET-SERT examination in vivo [69]. [11C]MADAM/MADAM metabolism
was demonstrated with liver microcosm from a rat (RLM) and a human (HLM) in
association with radio-HPLC or UHPLC/Q-ToF-MS. The study examined the influence
of the carrier on the rate of metabolism of
[11C]MADAM both in in vitro as well as in vivo with
the help of radio-HPLC. To identify the carrier concentration dependency of
metabolite formation in vitro, two different concentrations of RLM and HLM were
incubated with [11C]MADAM. The urine samples were
also examined with radio-HPLC (Fig. 7)
[69]. The results suggest that
the metabolites were produced in in vitro because of the following
biotransformation: N-benzylic hydroxylation, S-oxidation, and demethylation
(Fig. 7) [69]. Their study also revealed that the carrier presence
significantly enhanced the [11C]MADAM metabolism rate
in RLM/HLM in in vitro experiments as well as in in vivo rat studies. The decent
commonality of the outcomes anticipated by RLM/HLM experiments with the data
acquired from the rat studies in vivo designates that
[11C]MADAM metabolism rate is dose dependent.
Therefore, this matter requires to be examined when the diarylsulfide compounds
are applied for the quantifications of SERT by PET.
×
Radiometabolite analysis of
(+)-[18F]flubatine
In the PET study, both the enantiomers of
[18F]flubatine are applied as a neuroimaging
agent for α4β2nicotinic
acetylcholine receptors (nAChRs) [70]. In 2018, Peter Brust et al. demonstrated a general
strategy for identifying radiometabolites of
(+)-[18F] flubatine formed in humans by studying the
radiometabolism in pigs (in vivo) and incubations with liver microsomes (in
vitro) assisted with radio-HPLC and LC-MS/MS [71]. Chromatographic investigations of both urine and plasma
samples from humans displayed the presence of very high fractions of
(+)-[18F]flubatine. Almost 96% of
(+)-[18F]flubatine stayed unaffected after 30 min
of injection. The enantiomer of the
(+)-[18F]flubatine (i.e.,
(−)-[18F]flubatine) also showed a large fraction
of the unaffected radiotracer, which was around 91% [72] and 93% [73] at the time of the investigation. The
(+)-[18F]flubatine undertook a biochemical
transformation via C-hydroxylation within the
azabicyclic ring to produce h-M1, which is equivalent to
[18F]M4 produced in vitro (Fig. 8) [71]. The bridgehead nitrogen (N8) hydroxylation (N8)
followed by a conjugation reaction by glucuronic acid leads to the formation of
a phase II radiometabolite h-M2, which is the same as
[18F]M7a, produced in vitro. Hence, the
radioactive metabolites spotted in humans was in decent accordance with those
produced by the human liver microsomes (Fig. 9) [71]. The
structures of h-M1 as well as also h-M2 are highly lipophobic and hence have a
lesser chance to pass through the blood–brain barrier. Thus, the result was in
agreement with the metabolic examination done with the mice where an extremely
small amount of radioactive metabolites (< 7%) were spotted in the brain,
after 30 min of administration [74]. The radiometabolism of the
(−)-[18F]flubatine was also examined in the in
vivo preclinical studies [75‐77] as well as in humans [72, 73,
78]. However, no structural
information about the radiometabolites of
(−)-[18F]flubatine has been reported yet. In a
clinical study, a radiometabolite was noticed in very small amounts by the
radio-HPLC, but no characterization study was performed [76]. This metabolic product is mostly formed
due to the N-hydroxylation of the
(−)-[18F]flubatine, followed by a glucuronidation
as identified for the (+)-[18F]flubatine. As the
amount of radiometabolite formed is too little, the radiometabolism of the
(+)-[18F]flubatine does not need to be considered
in the narrative of the arterial input function for the analysis of PET data
through kinetic modeling. Because of the little formation of these
radiometabolites in humans, the (+)-[18F]flubatine
displays a great metabolic stability in the clinical study. Thus, the
(+)-[18F]flubatine has been accepted as a highly
suitable radiotracer for the PET imaging of
α4β2 nAChRs.
×
×
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Improvement of metabolic stability
Improvement of the metabolic stability of the radiotracer is as
important as the analysis and identification of its radiometabolites. An increase in
metabolic stability could improve the quality of PET imaging results. There are two
major ways to improve the metabolic stability of the radiotracer. The first approach
is to substitute the hydrogen present in the reactive site by deuterium. The
deuterium substitution of the methyl or ethyl group will usually reduce the rate of
metabolism as it requires higher energy to cleave a carbon–deuterium covalent bond
other than the carbon–hydrogen bond simply due to a higher mass effect of deuterium.
The second approach is to change the labeling position without altering any of the
structural or chemical changes of the parent radiotracer. In this section, we will
look into the case study for the above two approaches using
[18F]Fluorocholine and
[11C]WAY-100635, respectively.
Stability of [18F]fluorocholine vs
[18F]fluoro-[1,2-2H4]choline
Choline radiotracers are commonly applied for clinical PET imaging
in oncology [79, 80]. In 2011, Smith et al. reported a unique
di-deuterated choline radiotracer,
[18F]fluoro-[1,2-2H4]choline, and assessed its in
vitro and in vivo stability as well as its potential use as a PET imaging
radiotracer [81]. Chemical
oxidation of these radiotracers by the chemical potassium permanganate shows
that [18F]fluoro-[1,2-2H4]choline has relatively
higher stability to oxidation when compared to
[18F]fluorocholine, which was expected from the
isotope effect (Fig. 10a) [81]. Radio-HPLC profiles indicate the
presence of almost similar amounts of the original radiotracers and the major
radiometabolite, betaine for [18F]fluorocholine after
incubation with potassium permanganate for 20 min. However, only a trace amount
of betaine was observed for
[18F]fluoro-[1,2-2H4]choline in the same conditions.
Oxidative stability of these radiotracers was also examined against the enzyme
choline oxidase (Fig. 10b)
[81], and this indicates a
greater degree of oxidation compared to the potassium permanganate system.
However, both enzymatic oxidation and in vitro chemical examination of
[18F]fluorocholine and its di-deuterated analog
directed that the later have higher oxidative resistance than
[18F]fluorocholine. This in vitro result is also
supported by the in vivo radiometabolite profile. The radio-HPLC exploration of
plasma samples provided some additional indication for an increase in the
resistance of the [18F]fluoro-[1,2-2H4]choline
against oxidation relative to the [18F]fluorocholine.
In the case of [18F]fluorocholine, simply a little
portion of the original radiotracer was detected in the radio-HPLC profile.
However, a considerable peak in the original radiotracer was still spotted in
the plasma sample for [18F]fluoro-[1,2-2H4]choline. A
biodistribution study in mice with the HCT-116 tumors also confirmed the better
in vivo stability and higher uptake of
[18F]fluoro-[1,2-2H4]choline in different tissues,
including tumor. Importantly,
[18F]fluoro-[1,2-2H4]choline shows a considerably
higher tumor uptake than [18F]fluorocholine at later
time intervals.
×
Stability of [O-methyl-11C]WAY-100635 vs
[carbonyl-11C]WAY-100635
[Carbonyl-11C]WAY-100635 is one of the
most promising PET radiotracers to assess 5-HT1A receptors in the brain. To
study the influence of the label position on radiotracer characteristics,
[carbonyl-11C]WAY-100635 and [O-methyl-11C]WAY-100635 were examined in a human
and a healthy monkey by PET [23].
[Carbonyl-11C]WAY-100635 radioactivity was
retained in regions including the occipital cortex, temporal cortex, and raphe
nuclei, which are known to be affluent with 5-HT1A receptors. However, it
rapidly cleared from the region that was almost devoid of 5-HT1A receptors such
as the cerebellum. Compared to
[O-methyl-11C]WAY-100635,
[carbonyl-11C]WAY-100635 offers about 10 and 3
times superior signal contrast in receptor-affluent regions of the human and
monkey brain, respectively. The HPLC analysis of plasma samples at various time
periods helps detect the amount of parent radiotracers,
[carbonyl-11C]WAY-100635, and its
radiometabolites (Fig. 11)
[23]. The original radiotracer
constitutes 19% of the total radioactivity at 47 min in the monkey plasma, and
in the human plasma, it constitutes around 8% of the overall radioactivity,
after 40 min. In the human plasma, a negligible radiometabolite was detected as
[carbonyl-11C]desmethyl-WAY-100635 but it was
almost undetectable in the monkey plasma.
[11C]Cyclohexanecarboxylicacid has been detected as
the major radioactive metabolite, and it contributes to around 21% of the total
radioactivity in the human plasma at 10 min after injection. In order to
identify its effects in PET imaging,
[carbonyl-11C]cyclohexanecarboxylic acid was
administrated into the cynomolgus monkeys and the PET study was then performed.
The PET examination concludes that the
[11C]cyclohexanecarboxylicacid uptake was extremely
low in the brain tissue and that it does not affect the PET study.
×
Stability of [18F]FMeNER vs
[18F]FMeNER-D2
(S,S)-[11C] MeNER displays high
selective affinity to norepinephrine transporter (NET) [82]. However, there is an inherent problem
of using (S,S)-[11C] MeNER in PET study of NET as the
specific binding did not attain its maximum within the stipulated PET scanning
period (93 min). Besides, the radiotracer also shows the significant noisy
signal at later time point [82]. To
avoid this problem, radiofluorinated analogs of
(S,S)-[11C]MeNER were investigated. In 2004,
Magnus et al. examined the PET study of NET using two fluorinated analog of
(S,S)-[11C] MeNER—(S,S)-[18F]FMeNER and also
(S,S)-[18F]FMeNER-D2 [83]. In the
case of (S,S)-[18F]FMeNER, it was noticed that
there was significant contamination in PET images due to the skull-bound
radioactivity. This observation indicates the rapid defluorination of
[18F]FMeNER. However, a significant decrease in
defluorination occurs for the di-deuterated analog
[18F]FMeNER-D2. These results prove that the
defluorination rate of the radiotracer can be minimized by the deuterium isotope
effect.
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Stability of [18F]FEPEP,
[18F]FMPEP vs
[18F]FMPEP-d2
11C-MePPEP, a PET radiotracer, has been used to
quantify cannabinoid CB1 receptors in the brain [84]. However, the application of
the11C-MePPEP was challenging due to the short
half-life of the carbon-11 radioisotope (20.4 min). To overcome this limitation,
18F-labeled analogs of the MePPEP were developed
(18F-FEPEP, 18F-FMPEP,
and 18F-FMPEP-d2). Terry et al. examined the brain
uptake of these three fluorinated tracers and identified that
18F-FMPEP-d2 is the best tracer due to its high
brain uptake [85]. Besides,
18F-FMPEP-d2 displays a significantly lower
radioactivity uptake in the skull compared to
18F-FMPEP. These results reveal that the accumulation
of the 18F-fluoride ion in the bone occurs due to the in vivo defluorination of
18F-FMPEP.
Stability of verapamil analog radiotracers
(R)-[11C] Verapamil is a widely used PET
radiotracer for P-gp research. Two other analogs of verapamil, labeled with
fluorine-18, were also reported [86] ([18F]1 and
[18F]2, Fig. 12) to assess the P-gp function in the brain. However, all
these three radiotracers suffer from complicated image interpretation due to
their poor metabolic stability [86,
88]. Hence, to develop a stable
radiotracer for P-gp, Raaphorst et al. have synthesized six new deuterium
substituted analogs of verapamil and evaluated their metabolic stability
[87]. They also aimed to
evaluate their metabolic pathway. It was discovered that the metabolic stability
of [18F]1 and [18F]2 could
be enhanced by the addition of deuterium in the parent radiotracer. They also
observed that the deuterium substituted methyl containing analogs
([18F]3-d3 and
[18F]3-d7) showed better metabolic stability compared
to their corresponding unsubstituted analogs. This increased metabolic stability
could be due to enhanced steric hindrance which eventually slows down the
enzymatic metabolism. In PET imaging, [18F]3-d7 and
(R)-[11C] verapamil both have shown similar kind
of in vivo characteristics. Therefore, [18F]3-d7
could be a potential metabolically stable radiotracer for the clinical
evaluation of P-gp.
×
Conclusion
PET is presently one of the most beneficial imaging tools for measuring
drug pharmacokinetics non-invasively in the tissue of interest. Since the last
decade, PET studies have offered a lot of important information regarding the tissue
accumulation of numerous types of drugs. However, for the analysis and
interpretation of the images, it is required to keep in mind that the collected
signals from the PET scanner alone do not permit any conclusion to be drawn about
the compound’s chemical identity that contributes to the radioactivity during the
scan. The identification of radiometabolites is extremely important as they could
offer some important information about the appropriate part of the compound to
attach the radioactive label. From the image analysis point of view, detailed
knowledge of the radiometabolite formation is required to get the maximum
information from a PET scan. However, the identification of the radiometabolites is
quite difficult because of its very short-lived radioisotope and the low dosage of
the radiopharmaceutical and its metabolites. The tedious sample preparation
procedure makes it even more complicated to analyze the radiometabolite in in vivo.
Here, in this review, we have given important information and updates regarding the
radiometabolite analysis of several carbon-11- and fluorine-18-based radiotracers
from in vitro, preclinical and clinical aspects.
Acknowledgements
The authors acknowledge the support from Lee Kong Chian School of Medicine,
Nanyang Technological University, Singapore, Austrian Institute of Technology and
Medical University of Vienna internal Grant (NAM/15006) and LKCMedicine Imaging
Probe Dev. Platform, Singapore.
Ethics approval and consent to participate
Not applicable
Consent for publication
Not applicable
Competing interests
The authors declare that they have no competing interests.
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